CA2970214A1 - System for pumping a biological fluid - Google Patents
System for pumping a biological fluid Download PDFInfo
- Publication number
- CA2970214A1 CA2970214A1 CA2970214A CA2970214A CA2970214A1 CA 2970214 A1 CA2970214 A1 CA 2970214A1 CA 2970214 A CA2970214 A CA 2970214A CA 2970214 A CA2970214 A CA 2970214A CA 2970214 A1 CA2970214 A1 CA 2970214A1
- Authority
- CA
- Canada
- Prior art keywords
- chamber
- actuation
- pressure
- pump
- fluid
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
- 238000005086 pumping Methods 0.000 title claims abstract 129
- 239000013060 biological fluid Substances 0.000 title claims 12
- 239000012530 fluid Substances 0.000 claims abstract description 123
- 238000005259 measurement Methods 0.000 claims abstract 3
- 210000001124 body fluid Anatomy 0.000 claims abstract 2
- 239000000523 sample Substances 0.000 claims description 71
- 239000008280 blood Substances 0.000 claims description 54
- 210000004369 blood Anatomy 0.000 claims description 54
- 238000010438 heat treatment Methods 0.000 claims description 47
- 238000010926 purge Methods 0.000 claims description 3
- 238000002560 therapeutic procedure Methods 0.000 claims description 3
- 238000006073 displacement reaction Methods 0.000 claims 74
- 239000012528 membrane Substances 0.000 claims 73
- 238000000034 method Methods 0.000 claims 45
- 238000004891 communication Methods 0.000 claims 31
- 206010020843 Hyperthermia Diseases 0.000 claims 8
- 230000001594 aberrant effect Effects 0.000 claims 8
- 230000036031 hyperthermia Effects 0.000 claims 8
- 238000012544 monitoring process Methods 0.000 claims 7
- 230000008878 coupling Effects 0.000 claims 5
- 238000010168 coupling process Methods 0.000 claims 5
- 238000005859 coupling reaction Methods 0.000 claims 5
- 229920001296 polysiloxane Polymers 0.000 claims 5
- 230000013011 mating Effects 0.000 claims 4
- 239000002184 metal Substances 0.000 claims 4
- 229910052751 metal Inorganic materials 0.000 claims 4
- 238000010521 absorption reaction Methods 0.000 claims 3
- 238000001816 cooling Methods 0.000 claims 3
- 239000007788 liquid Substances 0.000 claims 3
- 239000000463 material Substances 0.000 claims 3
- 239000004033 plastic Substances 0.000 claims 3
- 229920003023 plastic Polymers 0.000 claims 3
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 claims 2
- 229910000831 Steel Inorganic materials 0.000 claims 2
- WYTGDNHDOZPMIW-RCBQFDQVSA-N alstonine Natural products C1=CC2=C3C=CC=CC3=NC2=C2N1C[C@H]1[C@H](C)OC=C(C(=O)OC)[C@H]1C2 WYTGDNHDOZPMIW-RCBQFDQVSA-N 0.000 claims 2
- 239000004020 conductor Substances 0.000 claims 2
- 229910052802 copper Inorganic materials 0.000 claims 2
- 239000010949 copper Substances 0.000 claims 2
- 238000013016 damping Methods 0.000 claims 2
- 238000001914 filtration Methods 0.000 claims 2
- 239000010959 steel Substances 0.000 claims 2
- 239000012815 thermoplastic material Substances 0.000 claims 2
- 238000012546 transfer Methods 0.000 claims 2
- 238000011144 upstream manufacturing Methods 0.000 claims 2
- 238000003466 welding Methods 0.000 claims 2
- 239000004593 Epoxy Substances 0.000 claims 1
- 239000000853 adhesive Substances 0.000 claims 1
- 230000001070 adhesive effect Effects 0.000 claims 1
- 239000003146 anticoagulant agent Substances 0.000 claims 1
- 229940127219 anticoagulant drug Drugs 0.000 claims 1
- 239000004519 grease Substances 0.000 claims 1
- 230000002977 hyperthermial effect Effects 0.000 claims 1
- 238000007726 management method Methods 0.000 claims 1
- 239000008155 medical solution Substances 0.000 claims 1
- 230000001681 protective effect Effects 0.000 claims 1
- 229910052709 silver Inorganic materials 0.000 claims 1
- 239000004332 silver Substances 0.000 claims 1
- 239000000243 solution Substances 0.000 claims 1
- 229910001220 stainless steel Inorganic materials 0.000 claims 1
- 239000010935 stainless steel Substances 0.000 claims 1
- 239000000126 substance Substances 0.000 claims 1
- 229920002803 thermoplastic polyurethane Polymers 0.000 claims 1
- 102100033121 Transcription factor 21 Human genes 0.000 description 13
- 101710119687 Transcription factor 21 Proteins 0.000 description 12
- 241000251468 Actinopterygii Species 0.000 description 1
- 101000941356 Nostoc ellipsosporum Cyanovirin-N Proteins 0.000 description 1
- FBJUTZMAUXJMMH-UHFFFAOYSA-N azane;5-methyl-2-(4-methyl-5-oxo-4-propan-2-yl-1h-imidazol-2-yl)pyridine-3-carboxylic acid Chemical compound [NH4+].N1C(=O)C(C(C)C)(C)N=C1C1=NC=C(C)C=C1C([O-])=O FBJUTZMAUXJMMH-UHFFFAOYSA-N 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- VIKNJXKGJWUCNN-XGXHKTLJSA-N norethisterone Chemical compound O=C1CC[C@@H]2[C@H]3CC[C@](C)([C@](CC4)(O)C#C)[C@@H]4[C@@H]3CCC2=C1 VIKNJXKGJWUCNN-XGXHKTLJSA-N 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 101150109289 tcf21 gene Proteins 0.000 description 1
Classifications
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
- F04B43/06—Pumps having fluid drive
- F04B43/073—Pumps having fluid drive the actuating fluid being controlled by at least one valve
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
- A61M1/1601—Control or regulation
- A61M1/1603—Regulation parameters
- A61M1/1605—Physical characteristics of the dialysate fluid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
- A61M1/1654—Dialysates therefor
- A61M1/1656—Apparatus for preparing dialysates
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/28—Peritoneal dialysis ; Other peritoneal treatment, e.g. oxygenation
- A61M1/287—Dialysates therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3622—Extra-corporeal blood circuits with a cassette forming partially or totally the blood circuit
- A61M1/36222—Details related to the interface between cassette and machine
- A61M1/362227—Details related to the interface between cassette and machine the interface providing means for actuating on functional elements of the cassette, e.g. plungers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3622—Extra-corporeal blood circuits with a cassette forming partially or totally the blood circuit
- A61M1/36225—Extra-corporeal blood circuits with a cassette forming partially or totally the blood circuit with blood pumping means or components thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3622—Extra-corporeal blood circuits with a cassette forming partially or totally the blood circuit
- A61M1/36226—Constructional details of cassettes, e.g. specific details on material or shape
- A61M1/362265—Details of valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/369—Temperature treatment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/104—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body
- A61M60/109—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems
- A61M60/113—Extracorporeal pumps, i.e. the blood being pumped outside the patient's body incorporated within extracorporeal blood circuits or systems in other functional devices, e.g. dialysers or heart-lung machines
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
- A61M60/36—Medical purposes thereof other than the enhancement of the cardiac output for specific blood treatment; for specific therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/424—Details relating to driving for positive displacement blood pumps
- A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
- A61M60/43—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic using vacuum at the blood pump, e.g. to accelerate filling
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
- A61M60/554—Regulation using real-time blood pump operational parameter data, e.g. motor current of blood pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/835—Constructional details other than related to driving of positive displacement blood pumps
- A61M60/837—Aspects of flexible displacement members, e.g. shapes or materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/845—Constructional details other than related to driving of extracorporeal blood pumps
- A61M60/847—Constructional details other than related to driving of extracorporeal blood pumps arranged in a cassette
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/845—Constructional details other than related to driving of extracorporeal blood pumps
- A61M60/849—Disposable parts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/845—Constructional details other than related to driving of extracorporeal blood pumps
- A61M60/851—Valves
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B23/00—Pumping installations or systems
- F04B23/04—Combinations of two or more pumps
- F04B23/06—Combinations of two or more pumps the pumps being all of reciprocating positive-displacement type
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B39/00—Component parts, details, or accessories, of pumps or pumping systems specially adapted for elastic fluids, not otherwise provided for in, or of interest apart from, groups F04B25/00 - F04B37/00
- F04B39/12—Casings; Cylinders; Cylinder heads; Fluid connections
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B39/00—Component parts, details, or accessories, of pumps or pumping systems specially adapted for elastic fluids, not otherwise provided for in, or of interest apart from, groups F04B25/00 - F04B37/00
- F04B39/12—Casings; Cylinders; Cylinder heads; Fluid connections
- F04B39/123—Fluid connections
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B39/00—Component parts, details, or accessories, of pumps or pumping systems specially adapted for elastic fluids, not otherwise provided for in, or of interest apart from, groups F04B25/00 - F04B37/00
- F04B39/14—Provisions for readily assembling or disassembling
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/0009—Special features
- F04B43/0081—Special features systems, control, safety measures
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
- F04B43/06—Pumps having fluid drive
- F04B43/073—Pumps having fluid drive the actuating fluid being controlled by at least one valve
- F04B43/0736—Pumps having fluid drive the actuating fluid being controlled by at least one valve with two or more pumping chambers in parallel
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B53/00—Component parts, details or accessories not provided for in, or of interest apart from, groups F04B1/00 - F04B23/00 or F04B39/00 - F04B47/00
- F04B53/16—Casings; Cylinders; Cylinder liners or heads; Fluid connections
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B53/00—Component parts, details or accessories not provided for in, or of interest apart from, groups F04B1/00 - F04B23/00 or F04B39/00 - F04B47/00
- F04B53/22—Arrangements for enabling ready assembly or disassembly
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B7/00—Piston machines or pumps characterised by having positively-driven valving
- F04B7/02—Piston machines or pumps characterised by having positively-driven valving the valving being fluid-actuated
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K1/00—Details of thermometers not specially adapted for particular types of thermometer
- G01K1/08—Protective devices, e.g. casings
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K1/00—Details of thermometers not specially adapted for particular types of thermometer
- G01K1/16—Special arrangements for conducting heat from the object to the sensitive element
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01M—TESTING STATIC OR DYNAMIC BALANCE OF MACHINES OR STRUCTURES; TESTING OF STRUCTURES OR APPARATUS, NOT OTHERWISE PROVIDED FOR
- G01M3/00—Investigating fluid-tightness of structures
- G01M3/02—Investigating fluid-tightness of structures by using fluid or vacuum
- G01M3/04—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point
- G01M3/16—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point using electric detection means
- G01M3/18—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point using electric detection means for pipes, cables or tubes; for pipe joints or seals; for valves; for welds; for containers, e.g. radiators
- G01M3/186—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point using electric detection means for pipes, cables or tubes; for pipe joints or seals; for valves; for welds; for containers, e.g. radiators for containers, e.g. radiators
- G01M3/188—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point using electric detection means for pipes, cables or tubes; for pipe joints or seals; for valves; for welds; for containers, e.g. radiators for containers, e.g. radiators for radiators
-
- G—PHYSICS
- G05—CONTROLLING; REGULATING
- G05D—SYSTEMS FOR CONTROLLING OR REGULATING NON-ELECTRIC VARIABLES
- G05D7/00—Control of flow
- G05D7/06—Control of flow characterised by the use of electric means
- G05D7/0617—Control of flow characterised by the use of electric means specially adapted for fluid materials
- G05D7/0629—Control of flow characterised by the use of electric means specially adapted for fluid materials characterised by the type of regulator means
- G05D7/0676—Control of flow characterised by the use of electric means specially adapted for fluid materials characterised by the type of regulator means by action on flow sources
- G05D7/0682—Control of flow characterised by the use of electric means specially adapted for fluid materials characterised by the type of regulator means by action on flow sources using a plurality of flow sources
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
- A61F7/12—Devices for heating or cooling internal body cavities
- A61F2007/126—Devices for heating or cooling internal body cavities for invasive application, e.g. for introducing into blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3622—Extra-corporeal blood circuits with a cassette forming partially or totally the blood circuit
- A61M1/36226—Constructional details of cassettes, e.g. specific details on material or shape
- A61M1/362263—Details of incorporated filters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3626—Gas bubble detectors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/12—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/12—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
- A61M2205/127—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit with provisions for heating or cooling
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/12—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
- A61M2205/128—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit with incorporated valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3317—Electromagnetic, inductive or dielectric measuring means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3324—PH measuring means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
- A61M2205/3334—Measuring or controlling the flow rate
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3368—Temperature
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/36—General characteristics of the apparatus related to heating or cooling
- A61M2205/3606—General characteristics of the apparatus related to heating or cooling cooled
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/36—General characteristics of the apparatus related to heating or cooling
- A61M2205/3653—General characteristics of the apparatus related to heating or cooling by Joule effect, i.e. electric resistance
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/50—General characteristics of the apparatus with microprocessors or computers
- A61M2205/502—User interfaces, e.g. screens or keyboards
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/89—Valves
- A61M60/892—Active valves, i.e. actuated by an external force
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/89—Valves
- A61M60/894—Passive valves, i.e. valves actuated by the blood
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
- Y02A90/00—Technologies having an indirect contribution to adaptation to climate change
- Y02A90/10—Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation
Abstract
Various types and configurations of pump pods, heat-exchanger systems, and thermal/conductivity sensors are described above. Pump pods can be used in a wide variety of applications including but not limited to heat-exchanger systems and for pumping of bodily fluids or medical fluids. Thermal/conductivity sensors can be used in a wide variety of applications including but not limited to thermal/conductivity measurements of fluids and thermal/conductivity measurements in the context of heat-exchanger systems. Heat-exchanger systems may be used in a wide variety of applications to heat or cool fluids and are not limited to use with pump pods and thermal/conductivity sensors.
Description
IQ
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t11:- 410w-'----1:4 -I l ---1.-- itillo- 12 .--460.-i:4).:ir _________________________________________________________ 16 kik4 1114..4 i 41 g ----___ :
'-i if-0,11.. tH11:1 It FIG. 1
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..._,_ ..... - .1.)) griii/>........- -4----------- ___------ =
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c,)``) 7-) cno \
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c,)``) 7-) cno \
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4 .,=o 0 0 V"on ,00 (300 61) -C,7 LCC1I co C.) o o o o o Fluid side V
Pneumatic side 33 32 r--44 Pod I Pressure _____________________________________________________________________ ' Sensor r"--45 r-46 Tank Tank pressure Positive 48 Vacuqm pressure sensor supply 47 supply sensor 1-r valve valve =
Positive Pressure 7-51 Vacuum Pressure Reservior Reservoir Controller FIG. 4 8r-/ry " = 4t,µ =
0 ' I %.
c., <
LI
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Will Ln Lg IllgtFl*
R.
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tili 1 K__ . 11-1111HT CD
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AP ro FIG. 5B
.
, .
, .
.
.
, 721 tE ----- .
, 66¨'\
-, , HEAT
co( 1-1.13 1.13-1 ii..0 . HEAT HEAT u) to EXCHANGER BAG 4 Ill A> i5 Z.5 ,--, (----, m RI m m z z z z r- , A 'a 'c 1' lit la', I7.i 0 (I) (43 OgK M
1 ilg- ,ris, -o 13 Z 6 F4 )i CI)q r= FILTER m ......, 0 I ______________ z AIR PURGE/
PATIENT TEMPERATURE
SENS-OR61 62ENSO TRAP R --If--2019 PROBES
-\ _________ RT BLOOD OUT
RETURN CATHETER
,-29 66 - .5: : ' 35 36 2022 __ M
mg =IT
_____________________ BLOOD IN
INLET CATHETER
IS shiemill, 35 STERILE FIELD =
=
_______________________________________________________________ 25b 2020 1111111v POD 1 w-0 POD 2 -o DATA
PRIME
x 2:1 m m KEY
25a m cnco co\.....-- 2021 C ) C c c7 `---2018' m ,,, 38 ----\ -C3 ''v.---"011 9, 0 n.) 1 , f t Disposable Module Connection Diagram FIG. 6 . \--.-- 16 Pressure Pulses for low command (approx 15) .....Pod_l_Pressure (PSI) Podl desPos Cmd End of stroke period -= - =- = -2_0 _initial 1 , pumpinqil 1 1 , 1 1 k IMilkil Pod1 PosValve 1.8 -Period i'l 5 il II F, A, ii rl 11 t., il q A 1,, II
1.6 - "d µ.5 il ill 1111,ft 1!1 il it IIIV. a_ E-1--T--1Ø1171trcr."-TrillitirttAt-----= =o-1.4 - ' I \11! µ1 ki µi II .1.: If , t: li : 11 ,1 ; Q
- = T.:1 . .0 li ,' , t! g µ1 :.= : 1: v 1 1 i 1 1 1 .11 ril ' i 1 ! i=-;
1.2 - i ; ...1, L.¨ ____________________________________________________ Command 1.0- 1 - , , =I 1 ti , .-0.8 - .
k. = . ; i-=,____t-- in Valve , 0.6 - -.== - i co Open = = cn 0.4 - l 8 . .
, 0.2- , , . = .., = . = co 0 ---- _______________________________________ .___J 0 6.4 6.45 6.5 6.55 Time in seconds x10' FIG. 7 Command \ Pressure Pulse for a large command ______________________________________________________________ =
_y_odl_Pressure (PSI) i=-= \- -- = =
;
8 -1 Pod1 desPos Cmd --=-=-;
7 - i ______________________________________________ Pod1 PosValve Pressure __ 6 - -____ . _____________ i /v.-- - VVVAAJNA../VVNI-1 2 I
i 1 4 - = I
!Initial Pumpin End of stroke i --1 Period period 3 E
3 - i=
, ____________________________________________________ Valve 2 - I li to Open f ilg- O:
1 rl: milli 8.43 8A4 8.45 8.46 8.47 8.48 .
Time (cycles) x101 FIG. 8 =
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.,....: I 0 6 7.-1 -,......1.., I I = IT - = I I I T 1 I
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--....._._.
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III _l_ I I 771.1.rf."=.-- --,-,..r, Frequency (Hz)101 FIG. 9 =
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=
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CL N.
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---____ -180 ---,---- ' ' ' ' ' ' ' r 1 1 1 1 1 --1-11.------Frequency (Hz) , FIG. 10 , , _______________________________________ - Pod1 Pressure 700 - il P../. S Pod2 Pressure 600 - isr !-.
lir¨ Pod1 Filtered :4'-'; ------- Pod2 Ripple Filter2 500 -l I !,, I :II _ __ _.Podl Ripple Filter2 -II _________________________________________ Pod1 300 k 1s lv p aMCID NJ.
200 41 ; \I 4 1 i :I i Pod2 Filtered 100-. ,µ ,...--., c.-:.: f 1::___ =-z.\ ,) ,t " i1 !
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:
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c) _ to -300 - ca . , 7.66 7.68 7.7 7.72 7.74 7.76 Time (cycles) . FIG. 11 .
o o o o Pod Pressure Is Averaged Between the 5th and 10th Pressure Pulse 11 _________________________________________________________________ Pod1 Pulse Cnt.
_____________________________________________________________________ Pod1 Pressure (mmHG) Pulse Count _....pod1 Avg Pressure (mmHG) 9 __________________________________________________________________ ______________________________________________________________________________ t=J
______________________________________________________________________________ ______________________________________________________________________________ o_ ________________________________________________________________ Pressure C=4
Pneumatic side 33 32 r--44 Pod I Pressure _____________________________________________________________________ ' Sensor r"--45 r-46 Tank Tank pressure Positive 48 Vacuqm pressure sensor supply 47 supply sensor 1-r valve valve =
Positive Pressure 7-51 Vacuum Pressure Reservior Reservoir Controller FIG. 4 8r-/ry " = 4t,µ =
0 ' I %.
c., <
LI
ftV410 /
Will Ln Lg IllgtFl*
R.
. c71 c C>
tili 1 K__ . 11-1111HT CD
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AP ro FIG. 5B
.
, .
, .
.
.
, 721 tE ----- .
, 66¨'\
-, , HEAT
co( 1-1.13 1.13-1 ii..0 . HEAT HEAT u) to EXCHANGER BAG 4 Ill A> i5 Z.5 ,--, (----, m RI m m z z z z r- , A 'a 'c 1' lit la', I7.i 0 (I) (43 OgK M
1 ilg- ,ris, -o 13 Z 6 F4 )i CI)q r= FILTER m ......, 0 I ______________ z AIR PURGE/
PATIENT TEMPERATURE
SENS-OR61 62ENSO TRAP R --If--2019 PROBES
-\ _________ RT BLOOD OUT
RETURN CATHETER
,-29 66 - .5: : ' 35 36 2022 __ M
mg =IT
_____________________ BLOOD IN
INLET CATHETER
IS shiemill, 35 STERILE FIELD =
=
_______________________________________________________________ 25b 2020 1111111v POD 1 w-0 POD 2 -o DATA
PRIME
x 2:1 m m KEY
25a m cnco co\.....-- 2021 C ) C c c7 `---2018' m ,,, 38 ----\ -C3 ''v.---"011 9, 0 n.) 1 , f t Disposable Module Connection Diagram FIG. 6 . \--.-- 16 Pressure Pulses for low command (approx 15) .....Pod_l_Pressure (PSI) Podl desPos Cmd End of stroke period -= - =- = -2_0 _initial 1 , pumpinqil 1 1 , 1 1 k IMilkil Pod1 PosValve 1.8 -Period i'l 5 il II F, A, ii rl 11 t., il q A 1,, II
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- = T.:1 . .0 li ,' , t! g µ1 :.= : 1: v 1 1 i 1 1 1 .11 ril ' i 1 ! i=-;
1.2 - i ; ...1, L.¨ ____________________________________________________ Command 1.0- 1 - , , =I 1 ti , .-0.8 - .
k. = . ; i-=,____t-- in Valve , 0.6 - -.== - i co Open = = cn 0.4 - l 8 . .
, 0.2- , , . = .., = . = co 0 ---- _______________________________________ .___J 0 6.4 6.45 6.5 6.55 Time in seconds x10' FIG. 7 Command \ Pressure Pulse for a large command ______________________________________________________________ =
_y_odl_Pressure (PSI) i=-= \- -- = =
;
8 -1 Pod1 desPos Cmd --=-=-;
7 - i ______________________________________________ Pod1 PosValve Pressure __ 6 - -____ . _____________ i /v.-- - VVVAAJNA../VVNI-1 2 I
i 1 4 - = I
!Initial Pumpin End of stroke i --1 Period period 3 E
3 - i=
, ____________________________________________________ Valve 2 - I li to Open f ilg- O:
1 rl: milli 8.43 8A4 8.45 8.46 8.47 8.48 .
Time (cycles) x101 FIG. 8 =
Bandpass filters 0 , , .....,,, , I 11114/1!..!...... i .,..
.,....: I 0 6 7.-1 -,......1.., I I = IT - = I I I T 1 I
.....' .
. 16Hz..
.--*".=
.
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.-- .
co .
-0 ...---" 16Hz ...
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, , ,,,,,, ..._._.............. 16Hz ....
45 - _ ..
CD 2Hz¨N___.."-, .
cu=
.
2:--I o- ,.. 16Hz _ co ..
co .
co .
.c a_ -45 - _ .........
--....._._.
-30 . . , , ¨.1 . , , ,,õ,, I I I I I I
III _l_ I I 771.1.rf."=.-- --,-,..r, Frequency (Hz)101 FIG. 9 =
________________________________ ..........._.õ
0 - ....._..._ 6.15Hz ....,õ............ .
...-.. -a:. -.,..
........
CDN.
0.55Hz--.,),.. --, -0 -20 - =
....., _E
rn -...
co .=..=..
.
-.., ---..-.
-----..
-80 , . . . 1_1111 1 1 J I 11111 1 1 1 111111 0 ....
=
--------..._ 6.15 Hz --__,, - *---... 6.15-----,Fiz 0.55Hz _ -di T
- 0.55Hz--=\_>õ..
a) -1, ....
\ NNNN<
co .c ....
CL N.
-135 - N...., .....õ.....
---____ -180 ---,---- ' ' ' ' ' ' ' r 1 1 1 1 1 --1-11.------Frequency (Hz) , FIG. 10 , , _______________________________________ - Pod1 Pressure 700 - il P../. S Pod2 Pressure 600 - isr !-.
lir¨ Pod1 Filtered :4'-'; ------- Pod2 Ripple Filter2 500 -l I !,, I :II _ __ _.Podl Ripple Filter2 -II _________________________________________ Pod1 300 k 1s lv p aMCID NJ.
200 41 ; \I 4 1 i :I i Pod2 Filtered 100-. ,µ ,...--., c.-:.: f 1::___ =-z.\ ,) ,t " i1 !
-- -..,----- - -- - - -0 A5-Pod2 Filtered :.
:
"\--_,--Pod1 Filtered Ix>
c) _ to -300 - ca . , 7.66 7.68 7.7 7.72 7.74 7.76 Time (cycles) . FIG. 11 .
o o o o Pod Pressure Is Averaged Between the 5th and 10th Pressure Pulse 11 _________________________________________________________________ Pod1 Pulse Cnt.
_____________________________________________________________________ Pod1 Pressure (mmHG) Pulse Count _....pod1 Avg Pressure (mmHG) 9 __________________________________________________________________ ______________________________________________________________________________ t=J
______________________________________________________________________________ ______________________________________________________________________________ o_ ________________________________________________________________ Pressure C=4
5 r-4 ¨
4,) /.%je\ /4 I
,/ µ\ / \I µ
1=
3 ¨_1-51 .1 =
;
(c) , Average P'essure---N
, 2 ;
II
;
= t ;
:
t 5.46 5.47 5.48 5.49 5.5 5.51 5.52 Time (cycles) x1 o4 FIG. 12 Cover A 18 Door Afairallillpftrimmoongw_ \
N ''''- ebk lib& vik.Lc.o.iing I11111111311111.
111.14%.-12111" Numma111116 .iii '', i\. F na .
Pneumatic Sealing -1"-klitka µ1~111011111allIMIKinalak lb 4 ,.õ.õ, ____ 12 Tracks 11011hft112111\1111111.111k111111Mik \ 1 NIII.b,..7111101110111116.111111m1.1.111wli. \
Heat Exchanger Disposable 21 yArb..
Heating 141""=^^ftimilimilae---",------------ _ _ k .14 JLV.
27 AIN%
23a-231b--FIG. 13A
o o o o o 13.4 23a 23b 138b =
Men-=wrfir " a 7;
400., ln 133a 139b 133b 139a FIG. 13B
FIG. 13C
A
141}
142 ll94 = 4 ' Ailk P11 141'41'4%. 143 FIG. 14 lie 121 FIG. 15 FIG. 16 Mal =
FIG. 17 =
,-182 1837--- 184 ' I
I I
t -I-7:LN1 I ' =
=
FIG. 18 =
Measure temperature at first and second points.
Compare temperature readings from first and second points. and __________________________ First alarm if readings are deterrnine if readings are inconsistent.
consistent.
Determine if temperature, Second alarm if readings fall readings fall within safe range. outside of safe range.
FIG. 19 . 20/107 in co cs) css ci oi 0 co CNI
CO
/ CV
/
/
/
/
/
/ \ 4\
=43 t.,,,.. \ \ (r) c) / ..,-.= ' i/'%. I-=
9.
/ .
l.. .
1 C) .1µ4&. ..*.M 04 = A a) c) ........ .
c7i . 0 v.
...;
, . \
/...,:
s's=-.-..
0.1 .s. .x.
. /
/f /
r--------------"--i t.'N's': 03 CO
CV
CD Z71)-Cs1 pr., --) "
. 0 CNI "
a) .
CNI
zif¨ 2098 2090 2096- ______________________________ 2091 m iIIINiaiftj 411.11 4\
/111111111115116, _____________________________________________________________ 2092 2088 _______________________________________________ 2095 FIG. 21 2015 .
. __ 2005 I
._,..,, -2008 === \
.._, _.,--'- 0 -`-,-____,,\.
4 __tHi\
(5(6-0,,,,):
.,\
,,.... .
/
OD 2025b 2025a 0 6 _ )2011 .:
. , - di FIG. 22A .
_ 2096a I _______________ 2000b //I III
2000a --=--wit 2096b - /
0 rya,-
4,) /.%je\ /4 I
,/ µ\ / \I µ
1=
3 ¨_1-51 .1 =
;
(c) , Average P'essure---N
, 2 ;
II
;
= t ;
:
t 5.46 5.47 5.48 5.49 5.5 5.51 5.52 Time (cycles) x1 o4 FIG. 12 Cover A 18 Door Afairallillpftrimmoongw_ \
N ''''- ebk lib& vik.Lc.o.iing I11111111311111.
111.14%.-12111" Numma111116 .iii '', i\. F na .
Pneumatic Sealing -1"-klitka µ1~111011111allIMIKinalak lb 4 ,.õ.õ, ____ 12 Tracks 11011hft112111\1111111.111k111111Mik \ 1 NIII.b,..7111101110111116.111111m1.1.111wli. \
Heat Exchanger Disposable 21 yArb..
Heating 141""=^^ftimilimilae---",------------ _ _ k .14 JLV.
27 AIN%
23a-231b--FIG. 13A
o o o o o 13.4 23a 23b 138b =
Men-=wrfir " a 7;
400., ln 133a 139b 133b 139a FIG. 13B
FIG. 13C
A
141}
142 ll94 = 4 ' Ailk P11 141'41'4%. 143 FIG. 14 lie 121 FIG. 15 FIG. 16 Mal =
FIG. 17 =
,-182 1837--- 184 ' I
I I
t -I-7:LN1 I ' =
=
FIG. 18 =
Measure temperature at first and second points.
Compare temperature readings from first and second points. and __________________________ First alarm if readings are deterrnine if readings are inconsistent.
consistent.
Determine if temperature, Second alarm if readings fall readings fall within safe range. outside of safe range.
FIG. 19 . 20/107 in co cs) css ci oi 0 co CNI
CO
/ CV
/
/
/
/
/
/ \ 4\
=43 t.,,,.. \ \ (r) c) / ..,-.= ' i/'%. I-=
9.
/ .
l.. .
1 C) .1µ4&. ..*.M 04 = A a) c) ........ .
c7i . 0 v.
...;
, . \
/...,:
s's=-.-..
0.1 .s. .x.
. /
/f /
r--------------"--i t.'N's': 03 CO
CV
CD Z71)-Cs1 pr., --) "
. 0 CNI "
a) .
CNI
zif¨ 2098 2090 2096- ______________________________ 2091 m iIIINiaiftj 411.11 4\
/111111111115116, _____________________________________________________________ 2092 2088 _______________________________________________ 2095 FIG. 21 2015 .
. __ 2005 I
._,..,, -2008 === \
.._, _.,--'- 0 -`-,-____,,\.
4 __tHi\
(5(6-0,,,,):
.,\
,,.... .
/
OD 2025b 2025a 0 6 _ )2011 .:
. , - di FIG. 22A .
_ 2096a I _______________ 2000b //I III
2000a --=--wit 2096b - /
0 rya,-
6-;
,=
I le - ,, (0,, =
c , 2025a 2106a ,e) --t \_. to 411111111 2106b 2025b Ire #, 1;ro -, -'11\ if 2096c 2000d W 2000c 2096d _ 2006 FIG. 22B
? j-20432 2045---Tht 0 D
......,,,,,...:
, P rr-----A-, =
"
Ali Am /
r.-I I I 1 I III = 2041 2047-I=2016 FIG. 23 LL
14.
l*k _________________________________ 1 4 = gra ____________________________ 1 411141WMWm %NO
= 0 0 '11)I
-.. d ,ii<....___ ...."11.11...
-.-----....- -----,.---7-- -- 1 - - ....==---"--- ok ' 11--- c---..,._.
10-__õ,1 g,,,w, ,_____ 2500 MOP III
_-----------l, FIG. 25 u, , .Fr:
.
,-.
, o ,I, u, 2539b ----\\
-IIIIP = ' 61 m AV
c ) A
lir 00 0 2539a I
-=::....
%IIill,. c .
-AL. ONO
II qt.
410 . 2500 k.) -.1 6"
..1 SP, 1.
FIG. 26 o o Model #
Status Temp Graphs Flow Graphs Logs \ Therapy Controls PATIENT BODY TEMPERATURES
44 C ___________________________________________________________________ 44 C
SYSTEM IDLE
= 40 C
mom PRIME
32 C '¨'1 ______________________________________________________________ 32 C
WARM-UP
0 5 10 15 20 25 30 minutes Core (Bladder) on= Reference Probe #1 c=
oe Monitor (Nasophng) =no Reference Probe #2 =
PLATEAU
Target Temperature ezszz 44 C = BLOOD CIRCUIT TEMPERATURES
COOL-DOWN
END-THERAPY
36 C Enl- 36 C
Phase Progress:
0 min 302gutes I I U 1[W]
Entrance MN Exit =a DATE TIME ENTER COMMENT LOG OUT
FIG. 27 Pressure PR+
-End of stroke Pc, Time Pc_ __________________________________________________________ End of PR- stroke FIG. 28 OUTLET INLET
= AS.
FIG. 29 Gill beg/ill/W.0d FIG. 30A
3006 eifigswillrar/W4 Allikejr=Arri t r 3020 3018 "NW 3018 Amu 3020 -.01101111.
FIG. 30B 3004 3100 ---,\
BB
st:\
mum MINI 41=
j-- 111111111111111.1.
3114 ____________________________________________________________ 3114 1\-4211Mit0 CI" 3112 FIG. 31A
"7////11/Dio1r/11//W....._ _ tor -/Aimeavoimmon
,=
I le - ,, (0,, =
c , 2025a 2106a ,e) --t \_. to 411111111 2106b 2025b Ire #, 1;ro -, -'11\ if 2096c 2000d W 2000c 2096d _ 2006 FIG. 22B
? j-20432 2045---Tht 0 D
......,,,,,...:
, P rr-----A-, =
"
Ali Am /
r.-I I I 1 I III = 2041 2047-I=2016 FIG. 23 LL
14.
l*k _________________________________ 1 4 = gra ____________________________ 1 411141WMWm %NO
= 0 0 '11)I
-.. d ,ii<....___ ...."11.11...
-.-----....- -----,.---7-- -- 1 - - ....==---"--- ok ' 11--- c---..,._.
10-__õ,1 g,,,w, ,_____ 2500 MOP III
_-----------l, FIG. 25 u, , .Fr:
.
,-.
, o ,I, u, 2539b ----\\
-IIIIP = ' 61 m AV
c ) A
lir 00 0 2539a I
-=::....
%IIill,. c .
-AL. ONO
II qt.
410 . 2500 k.) -.1 6"
..1 SP, 1.
FIG. 26 o o Model #
Status Temp Graphs Flow Graphs Logs \ Therapy Controls PATIENT BODY TEMPERATURES
44 C ___________________________________________________________________ 44 C
SYSTEM IDLE
= 40 C
mom PRIME
32 C '¨'1 ______________________________________________________________ 32 C
WARM-UP
0 5 10 15 20 25 30 minutes Core (Bladder) on= Reference Probe #1 c=
oe Monitor (Nasophng) =no Reference Probe #2 =
PLATEAU
Target Temperature ezszz 44 C = BLOOD CIRCUIT TEMPERATURES
COOL-DOWN
END-THERAPY
36 C Enl- 36 C
Phase Progress:
0 min 302gutes I I U 1[W]
Entrance MN Exit =a DATE TIME ENTER COMMENT LOG OUT
FIG. 27 Pressure PR+
-End of stroke Pc, Time Pc_ __________________________________________________________ End of PR- stroke FIG. 28 OUTLET INLET
= AS.
FIG. 29 Gill beg/ill/W.0d FIG. 30A
3006 eifigswillrar/W4 Allikejr=Arri t r 3020 3018 "NW 3018 Amu 3020 -.01101111.
FIG. 30B 3004 3100 ---,\
BB
st:\
mum MINI 41=
j-- 111111111111111.1.
3114 ____________________________________________________________ 3114 1\-4211Mit0 CI" 3112 FIG. 31A
"7////11/Dio1r/11//W....._ _ tor -/Aimeavoimmon
7 kiek-w------hia #11 3106 \4, 3100y 3108 3112 =
FIG. 31B
---0)111111111(0/11 ji .16 B
MI .140111,1111 0 ___________________________________ 0 FIG. 32A
001!nrillellIMPAILTA
111111111eawrArri p 3108 , Alhasu FIG. 32B
______________________________________________ 3302 A /MI
Alai\
= ________________________________________ Za1111111111 _____ D t õ .71111P> _______ FIG. 33A
Adimh=-7, 3302 -1,11111AIMEL = .
odiar MI IF
FIG. 33B
Bt t ________________________________________________________ I
FIG. 34A
3408 ____________________________ - ____________________ -7111 3410 ____________________________ FIG. 34B
3500¨ 3518 ------ .".=
111 =
--.______ __i `l , A t/ ill .1V---1-1-1111-1411 s ''--- .T--------------- --__N.õ......,_______________..õ,.._ _ :-- '--- -=
\.._/,'' 401110.=,....._...s' ' 3520 - ---- e- .- *- ' 3524 9 ,(000+0======....-_% ' --, ':iIMIIIIIMMI11.101 1 NowyrMOP
-,-,-:.=
. 3508 FIG. 35A
3408 ____________________________________________________________ 3408 tt)-, % 4Pc) ocPc i 0-00o00 / 00 _O 0000000 0 0 ¨00s"
¨ _______________________________________________________ FIG. 35B FIG. 35C
r_ ___________________________________________________________ 3408 FIG. 35D FIG. 35E
o o llIL
o 3, 500 Ir3502k õmg -_ 11111.
3610 11110r 4 oo -Immr jikli 3606 FIG. 36A 3504 FIG. 36B
41ifiNkx 3608 Silt_ 3602 ilk _ FIG. 36C
=
=s, \
\.,., d, =--N
. ., 3712 N\
Aiiimor = k AIR ., -\ 19 '(-44*
........................) .' 'S----------------7--=_-_--,----- _LL.L17-: .
----7 6--7-_-- -?fl \II'lft......... 3706 - ---:----- ---I
4111'.1. -----------_______--5"-- =
....
FIG. 37 =
-mei\B3814 dalitt'amtv -.mom _ Of I a it *amt.." Mr gaff" 'µ,4111. 1.11111.1.
FIG. 38A
r¨ 3800 frikT. t- ;1%6 3816 "'*111kir A N 38183816 , ji" NMI _ FIG. 38B
390O--. \ 3904 3902\A.. ' - ' --\ --,'"--/--::---t--- .- 1-4p, 3904 411.11W-\
it \\,.....
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eMIK--- 3914 ________________________________________________ 3908 ..----(C4104,/
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,1?.
tl I
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---------46 s, 0.16' /0321rAT
, s'N..."--.....' 3906 = --I
µ..N....
ilk FIG. 40A 4006 I
A
ir 41140, er#
OP' 01.11 FIG. 40B
u, , .
,-.
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IV
I-I
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I
' ' ' = ' `..
, _______________________________________________________________________________ ____________ 4100 3916 ........, _-_---...õ,, , s B
\
MAO, 'IN
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)11L
I
( I
a , , I
I co CN
=:r.
i i r lip \,,ii LW
sz . 45/107 1.1..
(If-o .
CV @)) vs-' a CV
µ3.
411) 0 =
cµi C
C
(.6 .11.41.1 A4320 _ 4334 fish -%.'== =
¨ '<_,111/01., 4330 =
=
1-11-11¨"---"-!.
FIG. 43A
o o o o o fr ;Firail-17-11111-1' ?IN \
\ 4h ilk 8 ) 04' -A !.j.irs.
1A.04.-1?-411110e =
4342 4- ,==r510.
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FIG. 43E3 cp I() st t\i, c=I
4=111/ 'fft4 in c=I
Alf / All .
=
r,..., A.
.6,...
,...., , .. ...%_, L, ..,t.
d -.........õ,,,/
il i v, '-o t;
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=
0.-44 rik i \ 11---7 I-0) µ
L
is=
wram ......=
FIG. 44A
, 11701 . c:41 if _Is 1 :44 .4-ii-0 .
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*-10) =
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, a 0 0 0 0 416 0 =-,.
/ C., I,-, 0 , f06 0 0000 \
Cr ' 0 0 0 o 0 0 0 1 0 0 0 o o , , . , .. ., , - - /
..
FIG. 46A
---- cp¨,c3o--- f."
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-A- ___________________________________________________________ 33 FIG. 46B
=
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i:.1%=;"--- _........,---.. = -,'"
ii....y.- ..õ,,,-...-1.-- =-:-=',2Liirõ.........
IL
-14õ,, = ..,=-s--r" -00%4(4 T
--.--7iic- il !clop _ il _r..........,..õ-,..==. rg=
1!i_l______---,-*.
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ip .., I .J
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FIG. 47A
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.LQ
o o o 2027 = /
(41*
t 41, .-tA16,-147c71.
)17/1\iiii 2028a 2028b WOW 2026b 29 .47;rp 37b fi=
2026a g 25b 37a 34a 34b 25a FIG. 48 o o o o 23a .13S) 23b - \
AtIP,__µ114111111/..-11111% ¨466-jet 1.11.
er'4FI ¨ III
133a = 1 139b 39a 133b 053 FIG. 49A
, .'il .
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.¨....... ,__,.0 ..=...
......=.
o, I
riiirwaiii... idinat .., 133a 1111111111111 11111111111.EIR
139b 133b 139a FIG. 49B
/
FIG. 50A
Y
5i I
FIG. 50B
5108 ____________________________ eN
S
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Aiegf ,-5100 .. .'%
FIG. 51B
_ eN
/
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5108 ____________________________ I'1 , SO' zez .2 - =N- A
FIG. 52B
54O2 y/
5404 5100 -{
5406 { 4111111111111111 FIG_ 53 s , C
Altir 0., IMP
I
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FIG. 54 /
5406< e;/ ____________________________ FIG. 55A
1.1 g ;-FIG. 55B
4sN
} 5404 NI%
\
Agee tow- 5406 tZ.% 441' =
FIG. 56A FIG. 56B
5702 \
A s.
%
Ar-- . 5406 r. zza 0, 4 = 5702 5108 FIG. 56C FIG. 56D
il = %
% % = r/-A tk fr, }
} 5406 Arllr r 5406 A
FIG. 56E FIG. 56F
srµ
St 5702 k 5702 \
% N
} 5406 AAIX% 1=.A.11 FIG. 56G FIG. 56H
.=`µ $-N, k T/
// 1)>.5406 4.60k 10 A ZI219Nti FIG. 561 FIG. 56J
eN 5712 k =1 k,:, : fir zi i }54o6 A:.=
FIG. 56K FIG. 56L
.iNk vsk At. g }54o6 Att kr6 str" .4kp FIG. 56M FIG. 56N
\ e . . . .= µ= 5100 =,õ ..\=Nµ
,.\.\ = = \/ =,;.....A iii... õii, \,. k, , ,=,/
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''N.10.=== 5702 =
FIG. 560 FIG. 56P
0.>
FIG. 56Q 5704 5100 === 5404 \\KiHs 1:17' FIG. 56R
===\7-FIG. 56S
4eir N
N
tr) N
N'N
s s SS:
s ;
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co s 0 S S
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co co lt) tf) 110 f:C3) 11) co CO
.7*
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to ,44\
co CO
lf) CO
cD
cD
cD
CI
CO
ir) =
co 1() / V. =
/4/Aap, ZAMIMMir._ FIG. 59 =
=="`,, #oi "9 )=`=
6014 $10:1 6010 .
114 ri FIG. 60A
=
6000¨... 6002 6006 \
hoolor =10';eol 6012 ced;
FIG. 60B
CO
CD
CO
\11411111) (t) LI-1111111 =
<NI
co co V
=-/
C=4 CO
\
6002 =
6000 hi 6016 ,,,4111101111111 5108 FIG. 62A
µ.\
&
I r ."
6000 =Ill 6016 41111I1IrP
. 5108 = FIG. 62B
$4 A
6402 sAY _/ 5406 Nµ4, eo =
d I:
FIG. 63A
e; ,." = -'11% - - Ns 5402 St 4 1 5404 . 1 t 6402 e = -,:s 5406 \N
e0 '0 r 0 1 g i i #
0.
4 , g ill 1 i i FIG. 63B
} 5404 \
6014 4 ;
N!
;
6018 = = 6016 FIG. 64 í
FIG. 65
FIG. 31B
---0)111111111(0/11 ji .16 B
MI .140111,1111 0 ___________________________________ 0 FIG. 32A
001!nrillellIMPAILTA
111111111eawrArri p 3108 , Alhasu FIG. 32B
______________________________________________ 3302 A /MI
Alai\
= ________________________________________ Za1111111111 _____ D t õ .71111P> _______ FIG. 33A
Adimh=-7, 3302 -1,11111AIMEL = .
odiar MI IF
FIG. 33B
Bt t ________________________________________________________ I
FIG. 34A
3408 ____________________________ - ____________________ -7111 3410 ____________________________ FIG. 34B
3500¨ 3518 ------ .".=
111 =
--.______ __i `l , A t/ ill .1V---1-1-1111-1411 s ''--- .T--------------- --__N.õ......,_______________..õ,.._ _ :-- '--- -=
\.._/,'' 401110.=,....._...s' ' 3520 - ---- e- .- *- ' 3524 9 ,(000+0======....-_% ' --, ':iIMIIIIIMMI11.101 1 NowyrMOP
-,-,-:.=
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3408 ____________________________________________________________ 3408 tt)-, % 4Pc) ocPc i 0-00o00 / 00 _O 0000000 0 0 ¨00s"
¨ _______________________________________________________ FIG. 35B FIG. 35C
r_ ___________________________________________________________ 3408 FIG. 35D FIG. 35E
o o llIL
o 3, 500 Ir3502k õmg -_ 11111.
3610 11110r 4 oo -Immr jikli 3606 FIG. 36A 3504 FIG. 36B
41ifiNkx 3608 Silt_ 3602 ilk _ FIG. 36C
=
=s, \
\.,., d, =--N
. ., 3712 N\
Aiiimor = k AIR ., -\ 19 '(-44*
........................) .' 'S----------------7--=_-_--,----- _LL.L17-: .
----7 6--7-_-- -?fl \II'lft......... 3706 - ---:----- ---I
4111'.1. -----------_______--5"-- =
....
FIG. 37 =
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FIG. 38A
r¨ 3800 frikT. t- ;1%6 3816 "'*111kir A N 38183816 , ji" NMI _ FIG. 38B
390O--. \ 3904 3902\A.. ' - ' --\ --,'"--/--::---t--- .- 1-4p, 3904 411.11W-\
it \\,.....
CO
eMIK--- 3914 ________________________________________________ 3908 ..----(C4104,/
FIG. 39 ,u) .Fr:
,1?.
tl I
,0 4111110.-' 3916 ....___ B
---------46 s, 0.16' /0321rAT
, s'N..."--.....' 3906 = --I
µ..N....
ilk FIG. 40A 4006 I
A
ir 41140, er#
OP' 01.11 FIG. 40B
u, , .
,-.
.D.
IV
I-I
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I
' ' ' = ' `..
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\
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FIG. 41A .4-47 P livieb, Ikk bie404110101 FIG. 41B
)11L
I
( I
a , , I
I co CN
=:r.
i i r lip \,,ii LW
sz . 45/107 1.1..
(If-o .
CV @)) vs-' a CV
µ3.
411) 0 =
cµi C
C
(.6 .11.41.1 A4320 _ 4334 fish -%.'== =
¨ '<_,111/01., 4330 =
=
1-11-11¨"---"-!.
FIG. 43A
o o o o o fr ;Firail-17-11111-1' ?IN \
\ 4h ilk 8 ) 04' -A !.j.irs.
1A.04.-1?-411110e =
4342 4- ,==r510.
1111111WiriV
FIG. 43E3 cp I() st t\i, c=I
4=111/ 'fft4 in c=I
Alf / All .
=
r,..., A.
.6,...
,...., , .. ...%_, L, ..,t.
d -.........õ,,,/
il i v, '-o t;
,21 de:,...7....
=
0.-44 rik i \ 11---7 I-0) µ
L
is=
wram ......=
FIG. 44A
, 11701 . c:41 if _Is 1 :44 .4-ii-0 .
.,,*
*-10) =
_,-..,..
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, a 0 0 0 0 416 0 =-,.
/ C., I,-, 0 , f06 0 0000 \
Cr ' 0 0 0 o 0 0 0 1 0 0 0 o o , , . , .. ., , - - /
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FIG. 46A
---- cp¨,c3o--- f."
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=
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i:.1%=;"--- _........,---.. = -,'"
ii....y.- ..õ,,,-...-1.-- =-:-=',2Liirõ.........
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1!i_l______---,-*.
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.LQ
o o o 2027 = /
(41*
t 41, .-tA16,-147c71.
)17/1\iiii 2028a 2028b WOW 2026b 29 .47;rp 37b fi=
2026a g 25b 37a 34a 34b 25a FIG. 48 o o o o 23a .13S) 23b - \
AtIP,__µ114111111/..-11111% ¨466-jet 1.11.
er'4FI ¨ III
133a = 1 139b 39a 133b 053 FIG. 49A
, .'il .
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.¨....... ,__,.0 ..=...
......=.
o, I
riiirwaiii... idinat .., 133a 1111111111111 11111111111.EIR
139b 133b 139a FIG. 49B
/
FIG. 50A
Y
5i I
FIG. 50B
5108 ____________________________ eN
S
/ .#: .isf4741, FIG. 51A
Aiegf ,-5100 .. .'%
FIG. 51B
_ eN
/
FIG. 52A
5108 ____________________________ I'1 , SO' zez .2 - =N- A
FIG. 52B
54O2 y/
5404 5100 -{
5406 { 4111111111111111 FIG_ 53 s , C
Altir 0., IMP
I
I, , = ire AiTrATKAI, B
FIG. 54 /
5406< e;/ ____________________________ FIG. 55A
1.1 g ;-FIG. 55B
4sN
} 5404 NI%
\
Agee tow- 5406 tZ.% 441' =
FIG. 56A FIG. 56B
5702 \
A s.
%
Ar-- . 5406 r. zza 0, 4 = 5702 5108 FIG. 56C FIG. 56D
il = %
% % = r/-A tk fr, }
} 5406 Arllr r 5406 A
FIG. 56E FIG. 56F
srµ
St 5702 k 5702 \
% N
} 5406 AAIX% 1=.A.11 FIG. 56G FIG. 56H
.=`µ $-N, k T/
// 1)>.5406 4.60k 10 A ZI219Nti FIG. 561 FIG. 56J
eN 5712 k =1 k,:, : fir zi i }54o6 A:.=
FIG. 56K FIG. 56L
.iNk vsk At. g }54o6 Att kr6 str" .4kp FIG. 56M FIG. 56N
\ e . . . .= µ= 5100 =,õ ..\=Nµ
,.\.\ = = \/ =,;.....A iii... õii, \,. k, , ,=,/
\
"NW 5702 " k= ..,. ,.-µ%=\ \ "
''N.10.=== 5702 =
FIG. 560 FIG. 56P
0.>
FIG. 56Q 5704 5100 === 5404 \\KiHs 1:17' FIG. 56R
===\7-FIG. 56S
4eir N
N
tr) N
N'N
s s SS:
s ;
,11 s *ti CO , t s ik4 1"--S s LO
=sr "
co s 0 S S
S U-S
s s 411i II
-=14 #mi,4%
, Sikfr N
co co lt) tf) 110 f:C3) 11) co CO
.7*
oz, u, CO CO
to ,44\
co CO
lf) CO
cD
cD
cD
CI
CO
ir) =
co 1() / V. =
/4/Aap, ZAMIMMir._ FIG. 59 =
=="`,, #oi "9 )=`=
6014 $10:1 6010 .
114 ri FIG. 60A
=
6000¨... 6002 6006 \
hoolor =10';eol 6012 ced;
FIG. 60B
CO
CD
CO
\11411111) (t) LI-1111111 =
<NI
co co V
=-/
C=4 CO
\
6002 =
6000 hi 6016 ,,,4111101111111 5108 FIG. 62A
µ.\
&
I r ."
6000 =Ill 6016 41111I1IrP
. 5108 = FIG. 62B
$4 A
6402 sAY _/ 5406 Nµ4, eo =
d I:
FIG. 63A
e; ,." = -'11% - - Ns 5402 St 4 1 5404 . 1 t 6402 e = -,:s 5406 \N
e0 '0 r 0 1 g i i #
0.
4 , g ill 1 i i FIG. 63B
} 5404 \
6014 4 ;
N!
;
6018 = = 6016 FIG. 64 í
FIG. 65
8¨) w "4. =N
movinemme FIG. 66 6808 visL
A v jo-el*
.3!
II, A 7 FIG. 67 =
r \1/4 =
cifr FIG. 68 r I Mir, / A
7006 -Yr FIG. 69 __________________________________________________ 5108 7¨'5104 7102¨Z-Conductivity Sensor FIG. 70 7001,µ
A\ lk FIG. 71 , .
, .
, , , 0, , Ari...- .
/
, = ..õ..0( / õ/õ,/ / / ,/,-ialt.10140, = t oo 130 ,--=
..
- 10 hil..1111111 2026b nqi, 4), i 2026a To Patientl / ) 25a 25b .
(441\L'*-------- 2024 =
FIG. 72 /
From Patient o o o o Pressure Ripple Change During an Occlusion It ' (9 250 ( a) ci 150 ,/
=
(.) Time [sec]
FIG. 73A
o o o 108 Change in Integrated End of Stroke Filtered Value For An Occlusion o x 16 _________________________________________ 14 _________________________________________ -c) 12 _____________________________________ 111 = 10 ___________________________________ (I) = 8 ____________________________________ IL
Q) '42 4 ______________________________________ o LLJ
-2 _______________ 9 75 BO = 85 90 95 100 time [sec]
FIG. 73B
, .
, ,--, Zero Degree Phase Relationship , , 0, , VolumeFlow õ 1 - ¨ Pod 1 1 i ---Pod 2 5i ............... 1 (n 1 i ¨.. l i -5 q ...... ... ....... -=:( -10 __________________________________ _i .................................
¨ =-:i ............... ______,_ _ _ i 0 5 0 0 5 0 _____________ 0 secons Pod Volumes ...............................................................................
.
................................................ t\
................................................
.......................................................................... I
\µµ ......... IA ________ 25 µ
=
N = = \ Ni ==-, t ... : µ : r : µ
x t !
k I i ' ¨4 i . 1 = t t¨
\v ............... 1 I ' 1 : 1 1 : -1 1 = 1 t : X : 1 : =
1 - . =
=
. / . ' t : =
. \ 1 = =
, ; 1' I i 5 50 b Seconds ' Total hold up Volume .\, .
=
50 - = = =
= =
T 40 ¨ = ' :
= :
.
¨
:
20 = :
. :
: = =
10 - = =
. ' : =
0 0 15 h b6- 0 5 $;) = 5 __ kl Seconds =
. FIG. 74A
=
, .
, .
, , 0, =
180 Degree Phase Relationship , c, VolumeFlow i ', .............................. ;
=
¨Pod 1 :
-- -Pod 2 ...............................................................................
..........
_________________________________________________________________________ ..............................................................................
seconds Pod Volumes 35 t. /1\ J 1 J 'v.,.
/ nN, i . = " ! ''''''''' ¨ ¨ Pod 1 ,,,:, 30 -== =-: / :. `. / ; = /
. /- - --Pod 2 L,, / . = /
. ,-.
____ 25 = / = 1 ..< = N /
/ = \ . / : \
/ N . I -,1 b 20 -i/=== =======i ..... == ===. = . , .. //
.
/1 '.,.. i:
= . I . ;....
/ .
5 -;/=-=; . = =... .
0 ' 10 ; = ., ; ' ._.," i N./ i seconds Total hold up Volume 70- i ! .; ! ! ! J.
= ; ! !
60 .:
7.-. 50- : ' = -. ' . ' . ' 40- ' =
' ' = : : .
' 30 - : = = .
= ' I
;
10- ' , .
=
0 ; ; ; ; ;
.
seconds FIG. 74B
=.;
.
, .
, =.;
, 90 Degrees Phase Relationship , . VolumeFlow 10-!! .. ¨Pod 1 - --I - - -Pod 2 =
i 0 .;
1 -,--- ---. r .. I-;
I
i ..
-------------------------------------------------------------------------------- ;.1 J =
...............................................................................
... I ... I
10 15 20 25 30 35 40 45 = 50 55 seconds Pod Volumes 35 ' ' ' 'd \ I: : /1 = ..... \ ! /1 \ '''''' = "=/1 \ ---- Pod 1 ,c;
30 - 1 = \ = \ . t ' i \c' - - -Pod 2 .1.
\ . : / = . =
=-4 1 20 !==== : A. t = S , / \: ...... /.... :
( = 1 / ':*
'1 I .
15 \ = ' / : \
10 : : \ = ..... ========/ ( ? /
, 5 ; , il :, 1. \ i : 1 / ,=
seconds Total hold up Volume =
60 _____________________ = = =
_ 50 . =
E 40 ... ;õ ; ......... i .. ; = =
=
.
.
seconds FIG. 74C
(.11111444,11 ) -------÷7 FIG. 75 , 44100, 8001 FIG. 76 %%%%444\
=
8007 ------- \%.
8007 ________________________________________________ 8007 _____________________________ 11 ___________________ 1 i 14 _______________ FIG. 77 _____________________________________ =
_________________________________________________________________ 8008 FIG. 78 ________________________________________ 7 =
FIG. 79 ii/YIP 8010 FIG. 80 co cs \*-1o CNI
1.1%
CNI
CC :4 U¨
C`4 Tr) )11, , clowL,w woo == I
z-----2063 111 11111'}i111,._ ==== ________________________ FIG. 82 =
I
. 00 :
'f ..==:-....umm,:_*--,.........0 "=-=.....,_,=,"
qi i II !
I i I
\ i ,,- -----..j CD
CV
V) =
(i) o (NI
Heater - Fill Pump EI:atien) -------------------------------Drain Reservoir FIG. 84 , .
, .
, , , .
, .
Valves __________________________________________________________________________ 0 a .
Pump .
.
o .
.
Reservoir Balancing _____________________________________________________________ Chamber IN
¨
--) t t =
. Level Probe Heater Patient (Capacitive) FIG. 85 o o o o Valves Pump 1 =
=
_______________________________________________________________________________ ____________ 3 3 Balancing Reservoir Pump 2 Chamber Patient FIG. 86 ______________________________________________ 3 3 Pump =
EPatient) __________________________________ Drain Reservoir Valve FIG. 87
movinemme FIG. 66 6808 visL
A v jo-el*
.3!
II, A 7 FIG. 67 =
r \1/4 =
cifr FIG. 68 r I Mir, / A
7006 -Yr FIG. 69 __________________________________________________ 5108 7¨'5104 7102¨Z-Conductivity Sensor FIG. 70 7001,µ
A\ lk FIG. 71 , .
, .
, , , 0, , Ari...- .
/
, = ..õ..0( / õ/õ,/ / / ,/,-ialt.10140, = t oo 130 ,--=
..
- 10 hil..1111111 2026b nqi, 4), i 2026a To Patientl / ) 25a 25b .
(441\L'*-------- 2024 =
FIG. 72 /
From Patient o o o o Pressure Ripple Change During an Occlusion It ' (9 250 ( a) ci 150 ,/
=
(.) Time [sec]
FIG. 73A
o o o 108 Change in Integrated End of Stroke Filtered Value For An Occlusion o x 16 _________________________________________ 14 _________________________________________ -c) 12 _____________________________________ 111 = 10 ___________________________________ (I) = 8 ____________________________________ IL
Q) '42 4 ______________________________________ o LLJ
-2 _______________ 9 75 BO = 85 90 95 100 time [sec]
FIG. 73B
, .
, ,--, Zero Degree Phase Relationship , , 0, , VolumeFlow õ 1 - ¨ Pod 1 1 i ---Pod 2 5i ............... 1 (n 1 i ¨.. l i -5 q ...... ... ....... -=:( -10 __________________________________ _i .................................
¨ =-:i ............... ______,_ _ _ i 0 5 0 0 5 0 _____________ 0 secons Pod Volumes ...............................................................................
.
................................................ t\
................................................
.......................................................................... I
\µµ ......... IA ________ 25 µ
=
N = = \ Ni ==-, t ... : µ : r : µ
x t !
k I i ' ¨4 i . 1 = t t¨
\v ............... 1 I ' 1 : 1 1 : -1 1 = 1 t : X : 1 : =
1 - . =
=
. / . ' t : =
. \ 1 = =
, ; 1' I i 5 50 b Seconds ' Total hold up Volume .\, .
=
50 - = = =
= =
T 40 ¨ = ' :
= :
.
¨
:
20 = :
. :
: = =
10 - = =
. ' : =
0 0 15 h b6- 0 5 $;) = 5 __ kl Seconds =
. FIG. 74A
=
, .
, .
, , 0, =
180 Degree Phase Relationship , c, VolumeFlow i ', .............................. ;
=
¨Pod 1 :
-- -Pod 2 ...............................................................................
..........
_________________________________________________________________________ ..............................................................................
seconds Pod Volumes 35 t. /1\ J 1 J 'v.,.
/ nN, i . = " ! ''''''''' ¨ ¨ Pod 1 ,,,:, 30 -== =-: / :. `. / ; = /
. /- - --Pod 2 L,, / . = /
. ,-.
____ 25 = / = 1 ..< = N /
/ = \ . / : \
/ N . I -,1 b 20 -i/=== =======i ..... == ===. = . , .. //
.
/1 '.,.. i:
= . I . ;....
/ .
5 -;/=-=; . = =... .
0 ' 10 ; = ., ; ' ._.," i N./ i seconds Total hold up Volume 70- i ! .; ! ! ! J.
= ; ! !
60 .:
7.-. 50- : ' = -. ' . ' . ' 40- ' =
' ' = : : .
' 30 - : = = .
= ' I
;
10- ' , .
=
0 ; ; ; ; ;
.
seconds FIG. 74B
=.;
.
, .
, =.;
, 90 Degrees Phase Relationship , . VolumeFlow 10-!! .. ¨Pod 1 - --I - - -Pod 2 =
i 0 .;
1 -,--- ---. r .. I-;
I
i ..
-------------------------------------------------------------------------------- ;.1 J =
...............................................................................
... I ... I
10 15 20 25 30 35 40 45 = 50 55 seconds Pod Volumes 35 ' ' ' 'd \ I: : /1 = ..... \ ! /1 \ '''''' = "=/1 \ ---- Pod 1 ,c;
30 - 1 = \ = \ . t ' i \c' - - -Pod 2 .1.
\ . : / = . =
=-4 1 20 !==== : A. t = S , / \: ...... /.... :
( = 1 / ':*
'1 I .
15 \ = ' / : \
10 : : \ = ..... ========/ ( ? /
, 5 ; , il :, 1. \ i : 1 / ,=
seconds Total hold up Volume =
60 _____________________ = = =
_ 50 . =
E 40 ... ;õ ; ......... i .. ; = =
=
.
.
seconds FIG. 74C
(.11111444,11 ) -------÷7 FIG. 75 , 44100, 8001 FIG. 76 %%%%444\
=
8007 ------- \%.
8007 ________________________________________________ 8007 _____________________________ 11 ___________________ 1 i 14 _______________ FIG. 77 _____________________________________ =
_________________________________________________________________ 8008 FIG. 78 ________________________________________ 7 =
FIG. 79 ii/YIP 8010 FIG. 80 co cs \*-1o CNI
1.1%
CNI
CC :4 U¨
C`4 Tr) )11, , clowL,w woo == I
z-----2063 111 11111'}i111,._ ==== ________________________ FIG. 82 =
I
. 00 :
'f ..==:-....umm,:_*--,.........0 "=-=.....,_,=,"
qi i II !
I i I
\ i ,,- -----..j CD
CV
V) =
(i) o (NI
Heater - Fill Pump EI:atien) -------------------------------Drain Reservoir FIG. 84 , .
, .
, , , .
, .
Valves __________________________________________________________________________ 0 a .
Pump .
.
o .
.
Reservoir Balancing _____________________________________________________________ Chamber IN
¨
--) t t =
. Level Probe Heater Patient (Capacitive) FIG. 85 o o o o Valves Pump 1 =
=
_______________________________________________________________________________ ____________ 3 3 Balancing Reservoir Pump 2 Chamber Patient FIG. 86 ______________________________________________ 3 3 Pump =
EPatient) __________________________________ Drain Reservoir Valve FIG. 87
Claims (268)
1. A reciprocating positive-displacement pump comprising:
a hemispherical rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that is substantially tangential to the rigid chamber wall; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that is substantially tangential to the rigid chamber wall.
a hemispherical rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that is substantially tangential to the rigid chamber wall; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that is substantially tangential to the rigid chamber wall.
2. A reciprocating positive-displacement pump comprising:
a hemispherical rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that provides low-shear flow out of the pumping chamber.
a hemispherical rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that provides low-shear flow out of the pumping chamber.
3. A reciprocating positive-displacement pump comprising:
a hemispheroid rigid chamber wall; the wall having a perimeter;
a flexible membrane attached to the wall's perimeter, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber, the outlet being spaced away from the wall's perimeter;
wherein the membrane is made from silicone.
a hemispheroid rigid chamber wall; the wall having a perimeter;
a flexible membrane attached to the wall's perimeter, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber, the outlet being spaced away from the wall's perimeter;
wherein the membrane is made from silicone.
4. A reciprocating positive-displacement pump comprising:
a hemispheroid rigid chamber wall; the wall having a perimeter;
a flexible membrane attached to the wall's perimeter, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber, the outlet being spaced away from the wall's perimeter;
wherein the membrane includes bumps that space a central portion of the membrane away from the rigid chamber wall when the membrane is in a minimum-pumping-chamber-volume position.
a hemispheroid rigid chamber wall; the wall having a perimeter;
a flexible membrane attached to the wall's perimeter, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber, the outlet being spaced away from the wall's perimeter;
wherein the membrane includes bumps that space a central portion of the membrane away from the rigid chamber wall when the membrane is in a minimum-pumping-chamber-volume position.
5. A reciprocating positive-displacement pump according to any of claims 1 or 2, wherein the rigid chamber wall has a perimeter, and wherein the flexible membrane is attached to the wall's perimeter.
6. A reciprocating positive-displacement pump according to any of claims 1 or 2, wherein the rigid chamber wall has a perimeter, and wherein the outlet is spaced away from the perimeter.
7. A reciprocating positive-displacement pump according to any of claims 1, 2, or 4, wherein the membrane is made from silicone.
8. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the membrane is made from high-elongation silicone.
9. A reciprocating positive-displacement pump according to any of claims 1, 2, or 3, wherein the membrane includes bumps that space a central portion of the membrane away from the rigid chamber wall when the membrane is in a minimum-pumping-chamber-volume position.
10. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the inlet is oriented to produce a circulatory fluid flow within the pumping chamber toward the outlet and the outlet is oriented so that flow directed out of the pumping chamber peels off of the circulatory flow in a laminar fashion.
11. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, further including a rigid limit structure for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit structure defining an actuation chamber.
12. A reciprocating positive-displacement pump according to claim 11, wherein the actuation chamber is adapted for actuation by pressurized control fluid, and wherein the rigid limit structure includes an integral actuation port.
13. A reciprocating positive-displacement pump according to claim 11, wherein the rigid chamber wall and the rigid limit structure are interconnected.
14. A reciprocating positive-displacement pump according to claim 13, wherein the rigid chamber wall and the rigid limit structure are interconnected by ultrasonic welding.
15. A reciprocating positive-displacement pump according to claim 13, wherein the membrane is held in place between the rigid chamber wall and the rigid limit structure.
16. A reciprocating positive-displacement pump according to claim 11, wherein the rigid limit structure limits movement of the flexible membrane such that the rigid chamber and the flexible membrane urged against the rigid limit structure define the pumping chamber as a spherical volume when the pumping chamber is at maximum volume.
17. A reciprocating positive-displacement pump according to claim 16, wherein the rigid limit structure is a hemispherical limit wall that, together with the flexible membrane, defines a spherical actuation chamber when the pumping chamber is at minimum volume.
18. A reciprocating positive-displacement pump according to claim 11, further including an actuation system that intermittently provides either a positive or a negative pressure to the actuation chamber.
19. A reciprocating positive-displacement pump according to claim 18, wherein the actuation system includes:
a reservoir containing a control fluid at either a positive or a negative pressure, and a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir.
a reservoir containing a control fluid at either a positive or a negative pressure, and a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir.
20. A reciprocating positive-displacement pump according to claim 19, wherein the valving mechanism includes one of:
a binary on-off valve; and a variable-restriction valve.
a binary on-off valve; and a variable-restriction valve.
21. A reciprocating positive-displacement pump according to claim 19, further including:
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
22. A reciprocating positive-displacement pump according to claim 21, wherein the controller causes dithering of the valving mechanism and determines when a stroke ends from pressure information from the actuation-chamber pressure transducer.
23. A reciprocating positive-displacement pump according to claim 22, wherein the controller controls the valving mechanism to cause the flexible membrane to reach either the rigid chamber wall or the rigid limit structure at each of a stroke's -beginning and end, wherein the controller determines the amount of flow through the pump based on a number of strokes.
24. A reciprocating positive-displacement pump according to claim 21, wherein the controller integrates pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
25. A reciprocating positive-displacement pump according to claim 21, further including:
a reservoir pressure transducer for measuring the pressure of the pressure of gas in the reservoir, wherein the controller receives pressure information from the reservoir pressure transducer.
a reservoir pressure transducer for measuring the pressure of the pressure of gas in the reservoir, wherein the controller receives pressure information from the reservoir pressure transducer.
26. A reciprocating positive-displacement pump according to claim 25, wherein the controller compares the pressure information from the actuation-chamber and reservoir pressure transducers to determine whether either of the pressure transducers are malfunctioning.
27. A reciprocating positive-displacement pump according to claim I I, further including an actuation system that alternately provides positive and negative pressure to the actuation chamber.
28. A reciprocating positive-displacement pump according to claim 27, wherein the actuation system includes:
a positive-pressure reservoir;
a negative-pressure reservoir; and a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs.
a positive-pressure reservoir;
a negative-pressure reservoir; and a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs.
29. A reciprocating positive-displacement pump according to claim 28, wherein the valving mechanism includes one of:
separate positive and negative supply valves for controlling the flow of control fluid between the actuation chamber and the reservoirs;wherein each supply valve is one of a binary on-off valve and a variable-restriction valve; and a three-way supply valve for controlling the flow of control fluid between the actuation chamber and the reservoirs.
separate positive and negative supply valves for controlling the flow of control fluid between the actuation chamber and the reservoirs;wherein each supply valve is one of a binary on-off valve and a variable-restriction valve; and a three-way supply valve for controlling the flow of control fluid between the actuation chamber and the reservoirs.
30. A reciprocating positive-displacement pump according to claim 28, further including:
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
31. A reciprocating positive-displacement pump according to claim 30, wherein the controller causes dithering of the valving mechanism and determines when a stroke ends from pressure information from the actuation-chamber pressure transducer.
32. A reciprocating positive-displacement pump according to claim 31, wherein the controller controls the valving mechanism to cause the flexible membrane to reach either the rigid chamber wall or the rigid limit structure at each of a stroke's beginning and end, wherein the controller determines the amount of flow through the pump based on a number of strokes.
33. A reciprocating positive-displacement pump according to claim 30 wherein the controller integrates pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
34. A reciprocating positive-displacement pump according to claim 30, further including:
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure reservoir, wherein the controller receives pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure reservoir, wherein the controller receives pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
35. A reciprocating positive-displacement pump according to claim 34, wherein the controller compares the pressure information from the actuation-chamber, positive-pressure-reservoir, and negative-pressure reservoir pressure transducers to determine whether any of the pressure transducers are malfunctioning.
36. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, further including an inlet valve for preventing flow out of the pumping chamber through the inlet and an outlet valve for preventing flow into the pumping chamber through the outlet.
37. A reciprocating positive-displacement pump according to claim 36, wherein the inlet valve and the outlet valve are passive check valves.
38. A reciprocating positive-displacement pump according to claim 36, wherein the inlet valve and the outlet valve are actively controlled valves.
39. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the pump is adapted for pumping a liquid.
40. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the pump is adapted for pumping a biological liquid.
41. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the pump is adapted for pumping blood.
42. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, wherein the pump is adapted for pumping heated blood.
43. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, further comprising:
a purge port in fluid communication with the pumping chamber, the purge port permitting expulsion of air from the pumping chamber.
a purge port in fluid communication with the pumping chamber, the purge port permitting expulsion of air from the pumping chamber.
44. A reciprocating positive-displacement pump according to any of claims 1, 2, 3, or 4, further comprising:
a secondary inlet in fluid communication with the pumping chamber, the secondary inlet permitting introduction of a secondary fluid into the pumping chamber.
a secondary inlet in fluid communication with the pumping chamber, the secondary inlet permitting introduction of a secondary fluid into the pumping chamber.
45. A reciprocating positive-displacement pump according to claim 44, wherein the secondary inlet comprises one of:
a luer port;
a syringe port; and a hollow spike.
a luer port;
a syringe port; and a hollow spike.
46. A reciprocating positive-displacement pump according to claim 44, wherein the secondary fluid includes one of:
a medical solution;
a chemical solution;
a dilutant, a blood thinner; and an anticoagulant.
a medical solution;
a chemical solution;
a dilutant, a blood thinner; and an anticoagulant.
47. A system for pumping comprising:
a pair of reciprocating positive-displacement pumps as in any of the preceding claims;
an inlet line coupled to both pumps' inlets; and an outlet line coupled to both pumps' outlets.
a pair of reciprocating positive-displacement pumps as in any of the preceding claims;
an inlet line coupled to both pumps' inlets; and an outlet line coupled to both pumps' outlets.
48. A system according to claim 47, wherein the pair of reciprocating positive-displacement pumps are configured to permit independent operation of the pumps for providing different flow-patterns through the inlet and outlet lines.
49. A system according to claim 48, wherein the pumps are pneumatically or hydraulically actuated, and wherein the system includes an independent actuation port for each pump.
50. A system according to claim 47, wherein the pumps are pneumatically or hydraulically actuated, and wherein the system includes a single actuation port for both pumps.
51. A system for pumping a biological fluid, the system comprising:
a disposable unit including an inlet line for the biological fluid, an outlet line for the biological fluid, and first and second spheroid pump pods, each pump pod including a hemispherical rigid chamber wall, a hemispherical rigid actuation wall, a flexible membrane attached to the chamber wall and the actuation wall, so that the flexible membrane and chamber wall define a pumping chamber, and so that the flexible membrane and the actuation wall define an actuation chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, and an actuation port providing fluid communication with the actuation chamber;
and a base unit including receptacle means for receiving and holding the disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to each of the actuation ports.
a disposable unit including an inlet line for the biological fluid, an outlet line for the biological fluid, and first and second spheroid pump pods, each pump pod including a hemispherical rigid chamber wall, a hemispherical rigid actuation wall, a flexible membrane attached to the chamber wall and the actuation wall, so that the flexible membrane and chamber wall define a pumping chamber, and so that the flexible membrane and the actuation wall define an actuation chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, and an actuation port providing fluid communication with the actuation chamber;
and a base unit including receptacle means for receiving and holding the disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to each of the actuation ports.
52. A system according to claim 51, wherein the first and second pump pods are rigidly attached to each other, and wherein the receptacle means includes means for receiving both the first and second pump pods in a single step.
53. A system according to one of claims 51 or 52, wherein the base unit further includes first and second pressure transducers for measuring respectively pressures of the control fluid provided to first pump pod's actuation port and of the control fluid provided to the second pump pod's actuation port; and a controller for receiving pressure information from the first and second pressure transducers and for controlling the actuation system.
54. A system according to claim 53, wherein the controller causes the actuation system to actuate the pump pods out of phase with each other, such that when one pump pod's pumping chamber is substantially full the other pump pod's pumping chamber is substantially empty.
55. A disposable unit for use in a system for pumping a biological fluid, the disposable unit comprising:
an inlet line for the biological fluid;
an outlet line for the biological fluid; and first and second spheroid pump pods, each pump pod including a hemispherical rigid chamber wall, a hemispherical rigid actuation wall, a flexible membrane attached to the chamber wall and the actuation wall, so that the flexible membrane and chamber wall define a pumping chamber, and so that the flexible membrane and the actuation wall define an actuation chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, and an actuation port providing fluid communication with the actuation chamber.
an inlet line for the biological fluid;
an outlet line for the biological fluid; and first and second spheroid pump pods, each pump pod including a hemispherical rigid chamber wall, a hemispherical rigid actuation wall, a flexible membrane attached to the chamber wall and the actuation wall, so that the flexible membrane and chamber wall define a pumping chamber, and so that the flexible membrane and the actuation wall define an actuation chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, and an actuation port providing fluid communication with the actuation chamber.
56. A disposable unit according to claim 55, wherein each pump pod includes:
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that provides low-shear flow out of the pumping chamber.
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that provides low-shear flow out of the pumping chamber.
57. A disposable unit according to claim 56, wherein each pump pod includes:
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that is substantially tangential to the rigid chamber wall; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that is substantially tangential to the rigid chamber wall.
an inlet for directing flow through the rigid chamber wall into the pumping chamber in a direction that is substantially tangential to the rigid chamber wall; and an outlet for directing flow through the rigid chamber wall out of the pumping chamber in a direction that is substantially tangential to the rigid chamber wall.
58. A disposable unit according to one of claims 55-57, further including a heat-exchanger component in fluid communication with first and second spheroid pump pods, the heat-exchanger component being adapted to be received by a heat exchanger for heating the biological fluid.
59. A disposable unit according to claim 58, wherein the heat-exchanger component includes a flexible bag defining a fluid path.
60. A system for pumping a biological fluid, the system comprising:
a disposable unit including an inlet line for the biological fluid, an outlet line for the biological fluid, and first and second pump pods, each pump pod being capable of delivering a stroke volume during each stroke, and each pump pod having a rigid pod wall enclosing a pump chamber, a reciprocating member adjacent the pump chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, arid an actuation port defined by the rigid pod wall; and a base unit including receptacle means for receiving and holding the disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to each of the actuation ports, wherein the base unit is capable of receiving and holding disposable units having pod pumps with different stroke volumes.
a disposable unit including an inlet line for the biological fluid, an outlet line for the biological fluid, and first and second pump pods, each pump pod being capable of delivering a stroke volume during each stroke, and each pump pod having a rigid pod wall enclosing a pump chamber, a reciprocating member adjacent the pump chamber, an inlet valve for permitting flow from the inlet line into the pumping chamber but preventing flow out of the pumping chamber into the inlet line, an outlet valve for permitting flow from the pumping chamber into the outlet line but preventing flow from the outlet line into the pumping chamber, arid an actuation port defined by the rigid pod wall; and a base unit including receptacle means for receiving and holding the disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to each of the actuation ports, wherein the base unit is capable of receiving and holding disposable units having pod pumps with different stroke volumes.
61. A base unit for pumping a biological fluid, the base unit comprising:
receptacle means for receiving and holding a disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to the disposable unit, wherein the base unit is capable of receiving and holding disposable units having pod pumps with different stroke volumes, and wherein the disposable units include first and second pump pods, each pump pod being capable of delivering a stroke volume during each stroke, and each pump pod having a rigid pod wall enclosing a pump chamber, and an actuation port defined by the rigid pod wall for permitting fluid communication between the actuation system and the reciprocating member.
receptacle means for receiving and holding a disposable unit, and an actuation system for providing a control fluid under positive or negative pressure to the disposable unit, wherein the base unit is capable of receiving and holding disposable units having pod pumps with different stroke volumes, and wherein the disposable units include first and second pump pods, each pump pod being capable of delivering a stroke volume during each stroke, and each pump pod having a rigid pod wall enclosing a pump chamber, and an actuation port defined by the rigid pod wall for permitting fluid communication between the actuation system and the reciprocating member.
62. A pump comprising:
means for drawing fluid into or urging fluid out of a pumping chamber;
means for determining a flow rate through the pumping chamber; and a controller for determining an amount of work required to achieve the flow rate and for generating an alarm if the amount of work indicates an aberrant flow condition.
means for drawing fluid into or urging fluid out of a pumping chamber;
means for determining a flow rate through the pumping chamber; and a controller for determining an amount of work required to achieve the flow rate and for generating an alarm if the amount of work indicates an aberrant flow condition.
63. A reciprocating positive-displacement pump comprising:
a rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber;
an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
a rigid limit wall for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit wall forming an actuation chamber, the rigid chamber wall and the rigid limit wall providing physical limits to the movement of the flexible membrane through a stroke;
an actuation system that intermittently provides either positive or negative pressure to the actuation chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the actuation system to cause the flexible membrane to reach the physical limits at a stroke's beginning and end, wherein the controller determines the amount of flow through the pump based on a number of strokes, and wherein the controller integrates pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
a rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber;
an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
a rigid limit wall for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit wall forming an actuation chamber, the rigid chamber wall and the rigid limit wall providing physical limits to the movement of the flexible membrane through a stroke;
an actuation system that intermittently provides either positive or negative pressure to the actuation chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the actuation system to cause the flexible membrane to reach the physical limits at a stroke's beginning and end, wherein the controller determines the amount of flow through the pump based on a number of strokes, and wherein the controller integrates pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
64. A reciprocating positive-displacement pump according to claim 63, wherein the actuation system alternately provides positive and negative pressure to the actuation chamber.
65. A reciprocating positive-displacement pump according to claim 64, wherein the pneumatic actuation system includes:
a positive-pressure reservoir;
a negative-pressure reservoir; and a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs.
a positive-pressure reservoir;
a negative-pressure reservoir; and a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs.
66. A reciprocating positive-displacement pump according to claim 65, further including a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure reservoir, and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure reservoir, wherein the controller receives pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
67. A reciprocating positive-displacement pump according to claim 66, wherein the controller compares the pressure information from the actuation-chamber, positive-pressure-reservoir and negative-pressure-reservoir pressure transducers to determine whether any of the pressure transducers are malfunctioning.
68. A reciprocating positive-displacement pump according to claim 63, wherein the actuation system includes:
a reservoir containing a control fluid at either a positive or a negative pressure;
and a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir.
a reservoir containing a control fluid at either a positive or a negative pressure;
and a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir.
69. A reciprocating positive-displacement pump according to claim 68, further including-a reservoir pressure transducer for measuring the pressure of the pressure of control fluid in the reservoir, wherein the controller receives pressure information from the reservoir pressure transducer.
70. A reciprocating positive-displacement pump according to claim 69, wherein the controller compares the pressure information from the actuation-chamber and reservoir pressure transducers to determine whether either of the pressure transducers are malfunctioning.
71. A reciprocating positive-displacement pump according to any of claims 65 or 68, wherein the controller causes dithering of valving mechanism and determines when a stroke ends from pressure information from the actuation-chamber pressure transducer.
72. A reciprocating positive-displacement pump according to claim 63, further including an inlet valve for preventing flow out of the pump and an outlet valve for preventing flow into the pump.
73. A reciprocating positive-displacement pump according to claim 63, wherein the pump is adapted for pumping a liquid.
74. A method for controlling flow comprising:
pumping fluid through a pumping chamber by at least one of drawing fluid into the pumping chamber and urging fluid out of a pumping chamber;
determining a flow rate through the pumping chamber;
determining an amount of work required to achieve the flow rate; and generating an alarm if the amount of work in relation to the flow rate indicates an aberrant flow condition.
pumping fluid through a pumping chamber by at least one of drawing fluid into the pumping chamber and urging fluid out of a pumping chamber;
determining a flow rate through the pumping chamber;
determining an amount of work required to achieve the flow rate; and generating an alarm if the amount of work in relation to the flow rate indicates an aberrant flow condition.
75. A method according to claim 74, wherein pumping the fluid, determining the flow rate, and determining the amount of work comprises:
providing a rigid chamber wall, a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define the pumping chamber;
providing an inlet for directing flow through the rigid chamber wall into the pumping chamber and an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
providing a rigid limit wall for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit wall forming an actuation chamber, the rigid chamber wall and the rigid limit wall providing physical limits to the movement of the flexible membrane through a stroke;
providing an actuation system that intermittently provides either positive or negative pressure to the actuation chamber;
providing an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
receiving pressure information from the actuation-chamber pressure transducer;
controlling the actuation system to cause the flexible membrane to reach the physical limits at a stroke's beginning and end;
determining the amount of flow through the pump based on a number of strokes; and integrating pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
providing a rigid chamber wall, a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define the pumping chamber;
providing an inlet for directing flow through the rigid chamber wall into the pumping chamber and an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
providing a rigid limit wall for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit wall forming an actuation chamber, the rigid chamber wall and the rigid limit wall providing physical limits to the movement of the flexible membrane through a stroke;
providing an actuation system that intermittently provides either positive or negative pressure to the actuation chamber;
providing an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
receiving pressure information from the actuation-chamber pressure transducer;
controlling the actuation system to cause the flexible membrane to reach the physical limits at a stroke's beginning and end;
determining the amount of flow through the pump based on a number of strokes; and integrating pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
76. A reciprocating positive-displacement pump comprising:
a reciprocating member having a first face towards a pumping chamber and a second face towards an actuation chamber;
an inlet for directing flow into the pumping chamber;
an outlet for directing flow out of the pumping chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
an actuation system that intermittently provides positive or negative pressure to the actuation chamber, wherein the actuation system includes a reservoir containing control fluid under positive or negative pressure, a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir, and a reservoir pressure transducer for measuring the pressure of the control fluid in the reservoir, and a controller that controls the actuation system to move the reciprocating member, receives pressure information from the actuation-chamber and reservoir pressure transducers, and compares the pressure information to determine whether either of the pressure transducers are malfunctioning.
a reciprocating member having a first face towards a pumping chamber and a second face towards an actuation chamber;
an inlet for directing flow into the pumping chamber;
an outlet for directing flow out of the pumping chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
an actuation system that intermittently provides positive or negative pressure to the actuation chamber, wherein the actuation system includes a reservoir containing control fluid under positive or negative pressure, a valving mechanism for controlling the flow of control fluid between the actuation chamber and the reservoir, and a reservoir pressure transducer for measuring the pressure of the control fluid in the reservoir, and a controller that controls the actuation system to move the reciprocating member, receives pressure information from the actuation-chamber and reservoir pressure transducers, and compares the pressure information to determine whether either of the pressure transducers are malfunctioning.
77. A pump according to claim 76, wherein the controller controls the pressure of the reservoir to ensure it does not exceed a pre-set limit.
78. A reciprocating positive-displacement pump comprising:
a rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber;
an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
a rigid actuation wall, the flexible membrane and the rigid limit wall forming an actuation chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
an actuation system that alternately provides positive and negative pressure to the actuation chamber, wherein the actuation system includes a positive-pressure reservoir, a negative-pressure reservoir, a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs, a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure reservoir, and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure reservoir; and a controller that controls the actuation system to move the flexible membrane, receives pressure information from the actuation-chamber, positive-pressure-reservoir and negative-pressure-reservoir pressure transducers, and compares the pressure information to determine whether any of the pressure transducers are malfunctioning.
a rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing flow through the rigid chamber wall into the pumping chamber;
an outlet for directing flow through the rigid chamber wall out of the pumping chamber;
a rigid actuation wall, the flexible membrane and the rigid limit wall forming an actuation chamber;
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber;
an actuation system that alternately provides positive and negative pressure to the actuation chamber, wherein the actuation system includes a positive-pressure reservoir, a negative-pressure reservoir, a valving mechanism for controlling the flow of control fluid between the actuation chamber and each of the reservoirs, a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure reservoir, and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure reservoir; and a controller that controls the actuation system to move the flexible membrane, receives pressure information from the actuation-chamber, positive-pressure-reservoir and negative-pressure-reservoir pressure transducers, and compares the pressure information to determine whether any of the pressure transducers are malfunctioning.
79. A valving system including:
a valve cassette containing a plurality of valves, each valve including a valving chamber and an actuation chamber, each valve being actuatable by a control fluid in the actuation chamber;
a control cassette having a plurality of fluid-interface ports for providing fluid communication with a control fluid from a base unit; and a plurality of tubes extending between the valve cassette and the control cassette, each tube providing fluid communication between a fluid-interface port and at least one actuation chamber, such that the base unit can actuate a valve by pressurizing control fluid in a fluid interface port.
a valve cassette containing a plurality of valves, each valve including a valving chamber and an actuation chamber, each valve being actuatable by a control fluid in the actuation chamber;
a control cassette having a plurality of fluid-interface ports for providing fluid communication with a control fluid from a base unit; and a plurality of tubes extending between the valve cassette and the control cassette, each tube providing fluid communication between a fluid-interface port and at least one actuation chamber, such that the base unit can actuate a valve by pressurizing control fluid in a fluid interface port.
80. A valving system according to claim 79, wherein the valve cassette includes a pump actuatable by a control fluid, and wherein the plurality of tubes includes a tube providing fluid communication between a fluid-interface port and the pump, such that the base unit can actuate the pump by pressurizing control fluid in a fluid interface port.
81. A pumping system including:
a pump cassette containing a plurality of pumps, each pump including a pumping chamber and an actuation chamber, each pump being actuatable by a control fluid in the actuation chamber;
a control cassette having a plurality of fluid-interface ports for providing fluid communication with a control fluid from a base unit; and a plurality of tubes extending between the pump cassette and the control cassette, each tube providing fluid communication between a fluid-interface port and at least one actuation chamber, such that the base unit can actuate a pump by pressurizing control fluid in a fluid interface port.
a pump cassette containing a plurality of pumps, each pump including a pumping chamber and an actuation chamber, each pump being actuatable by a control fluid in the actuation chamber;
a control cassette having a plurality of fluid-interface ports for providing fluid communication with a control fluid from a base unit; and a plurality of tubes extending between the pump cassette and the control cassette, each tube providing fluid communication between a fluid-interface port and at least one actuation chamber, such that the base unit can actuate a pump by pressurizing control fluid in a fluid interface port.
82. A pumping system according to claim 81, wherein the pump cassette includes a valve actuatable by a control fluid, and wherein the plurality of tubes includes a tube providing fluid communication between a fluid-interface port and the valve, such that the base unit can actuate the valve by pressurizing control fluid in a fluid interface port.
83. A diaphragm for use in a reciprocating positive-displacement pump, the diaphragm having a circular rim and a pre-formed hemispheroid membrane attached to the rim.
84. A diaphragm according to claim 83, wherein the membrane includes a configuration of raised structures on a pump chamber side.
85. A diaphragm for use in a reciprocating positive-displacement pump, the diaphragm having a rim and a membrane attached to the rim, the membrane including a configuration of raised structures on a pump chamber side.
86. A diaphragm according to any of claims claim 84 or 85, wherein the raised structures include raised bumps.
87. A diaphragm according to claim 86, wherein the raised structures are located away from the rim.
88. A diaphragm according to any of claims 83 or 85, wherein the rim is adapted for interconnection with at least one of a pump chamber wall and an actuation chamber wall.
89. A diaphragm according to any of claims 83 or 85, wherein the rim and the membrane are made from silicone.
90. A diaphragm according to claim 89, wherein the rim and the membrane are made from high-elongation silicone.
91. A diaphragm according to any of claims 83 or 85, wherein the rim and the membrane are integral.
92. A pumping system comprising:
an actuation system for operating a pump pod, the actuation system including a standardized actuation interface for interconnection with pump pods having different pump volumes, an actuation-chamber pressure transducer for measuring pressure in an actuation chamber of the pump pod; and a controller that controls the actuation system to operate the pump pod based on pressure information received from the actuation-chamber pressure transducer, whereby operation of pump pods is independent of pump volume.
an actuation system for operating a pump pod, the actuation system including a standardized actuation interface for interconnection with pump pods having different pump volumes, an actuation-chamber pressure transducer for measuring pressure in an actuation chamber of the pump pod; and a controller that controls the actuation system to operate the pump pod based on pressure information received from the actuation-chamber pressure transducer, whereby operation of pump pods is independent of pump volume.
93. A pumping system comprising:
an actuation system for operating a pump pod, the actuation system including a standardized actuation interface for interconnection with pump pods having different stroke lengths;
an actuation-chamber pressure transducer for measuring pressure in an actuation chamber of the pump pod; and a controller that controls the actuation system to operate the pump pod based on pressure information received from the actuation-chamber pressure transducer, whereby operation of pump pods is independent of stroke length.
an actuation system for operating a pump pod, the actuation system including a standardized actuation interface for interconnection with pump pods having different stroke lengths;
an actuation-chamber pressure transducer for measuring pressure in an actuation chamber of the pump pod; and a controller that controls the actuation system to operate the pump pod based on pressure information received from the actuation-chamber pressure transducer, whereby operation of pump pods is independent of stroke length.
94. A pod pump comprising:
a three-piece housing defining an interior chamber, the housing having a two-piece pumping chamber wall coupled to an actuation chamber wall; and a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber, the housing including a first port in fluid communication with the actuation chamber and at least one second port in fluid communication with the pumping chamber.
a three-piece housing defining an interior chamber, the housing having a two-piece pumping chamber wall coupled to an actuation chamber wall; and a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber, the housing including a first port in fluid communication with the actuation chamber and at least one second port in fluid communication with the pumping chamber.
95. A pod pump according to claim 94, wherein the three pieces of the housing are interconnected by ultrasonic welding.
96. A pod pump according to claim 94, further including, for each second port, a valve secured between the two pumping chamber wall pieces.
97. A pod pump comprising:
a housing defining an interior chamber; and a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber, the housing including a single port in communication with the pumping chamber for use as both a fluid inlet and a fluid outlet.
a housing defining an interior chamber; and a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber, the housing including a single port in communication with the pumping chamber for use as both a fluid inlet and a fluid outlet.
98. A pod pump comprising:
a housing defining an interior chamber;
a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber; and a component disposed in the actuation chamber for at least one of limiting motion of the diaphragm, damping the diaphragm's travel, filtering fluid entering or leaving the actuation chamber, damping sound or vibration in the pod pump, and performing fluid management system measurements on fluid in the pumping chamber.
a housing defining an interior chamber;
a diaphragm secured to the housing within the interior chamber, the diaphragm dividing the interior chamber into a pumping chamber and an actuation chamber; and a component disposed in the actuation chamber for at least one of limiting motion of the diaphragm, damping the diaphragm's travel, filtering fluid entering or leaving the actuation chamber, damping sound or vibration in the pod pump, and performing fluid management system measurements on fluid in the pumping chamber.
99. A sensing probe comprising:
a probe housing;
a thermal sensor in said probe housing having a sensing end and a connector end;
a probe tip thermally coupled to said sensing end of the thermal sensor and attached to said probe housing, the probe tip adapted for thermal coupling with an inner surface of a thermal well; and at least two leads connected to said connector end of said thermal sensor, whereby thermal energy is transferred from said thermal well to said thermal sensor and whereby temperature information is conveyed through said leads.
a probe housing;
a thermal sensor in said probe housing having a sensing end and a connector end;
a probe tip thermally coupled to said sensing end of the thermal sensor and attached to said probe housing, the probe tip adapted for thermal coupling with an inner surface of a thermal well; and at least two leads connected to said connector end of said thermal sensor, whereby thermal energy is transferred from said thermal well to said thermal sensor and whereby temperature information is conveyed through said leads.
100. A sensing probe according to claim 99, further comprising a third lead attached to one of the probe housing, the thermal sensor, and the probe tip for permitting conductivity sensing.
101. A sensing probe according claim 99, further comprising urethane resin between said probe tip and said probe housing.
102. A sensing probe comprising:
a probe housing having a probe tip adapted for thermal coupling with an inner surface of a thermal well;
a thermal sensor in said housing having a sensing end and a connector end, said sensing end thermally coupled to said probe tip; and at least three leads, wherein said leads transfer electrical signals and whereby said signals are used to determine temperature and conductivity.
a probe housing having a probe tip adapted for thermal coupling with an inner surface of a thermal well;
a thermal sensor in said housing having a sensing end and a connector end, said sensing end thermally coupled to said probe tip; and at least three leads, wherein said leads transfer electrical signals and whereby said signals are used to determine temperature and conductivity.
103. A sensing probe according to any of claims 99-102, further comprising thermal epoxy between said thermal sensor and said probe tip.
104. A sensing probe according to any of claims 99-102, where said probe tip is copper.
105. A sensing probe according to any of claims 99-102, wherein said probe tip is steel.
106. A sensing probe according to any of claims 99-102, wherein the probe tip is a metal including at least one of silver, copper, steel, and stainless steel.
107. A sensing probe according to any of claims 99-102, where said probe housing is plastic.
108. A sensing probe according to any of claims 99-102, wherein said probe housing is metal.
109. A sensing probe according to any of claims 99-102, wherein said housing further comprises a flange disposed about said probe housing.
110. A sensing probe according to claim 109, further comprising a spring in communication with the flange.
111. A sensing probe according to claim 99, wherein the probe tip includes a flange for mating with the housing.
112. A sensing probe according to claim 99, further comprising:
a conductivity sensor attached to one of the probe housing, the thermal sensor, and the probe tip for permitting conductivity sensing; and a third lead attached to the conductivity sensor for transmitting conductivity information.
a conductivity sensor attached to one of the probe housing, the thermal sensor, and the probe tip for permitting conductivity sensing; and a third lead attached to the conductivity sensor for transmitting conductivity information.
113. A sensing probe according to claim 102, further comprising a conductivity sensor attached to the housing, wherein at least one of the leads is attached to the conductivity sensor for transmitting conductivity information.
114. A sensing probe according to any of claims 99-102, wherein the housing includes an integrated flexible member.
115. A sensor apparatus comprising:
a probe housing having a probe tip;
a thermal sensor in said housing having a sensing end and a connector end, said sensing end thermally coupled to said probe tip; and at least three leads, wherein said leads transfer electrical signals and whereby said signals are used to determine a temperature and conductivity.
a probe housing having a probe tip;
a thermal sensor in said housing having a sensing end and a connector end, said sensing end thermally coupled to said probe tip; and at least three leads, wherein said leads transfer electrical signals and whereby said signals are used to determine a temperature and conductivity.
116. The sensor apparatus of claim 115 further comprising a thermal well of a predetermined size and shape wherein said thermal well mates with said probe and said probe tip is thermal coupled to said thermal well.
117. A thermal well comprising:
a hollow housing of a thermally conductive material, said housing having an outer surface and an inner surface, said inner surface of a predetermined shape so as to form a mating relationship with a sensing probe, whereby said mating thermally couples the inner surface with a sensing probe.
a hollow housing of a thermally conductive material, said housing having an outer surface and an inner surface, said inner surface of a predetermined shape so as to form a mating relationship with a sensing probe, whereby said mating thermally couples the inner surface with a sensing probe.
118. The thermal well of claim 117 further comprising a predetermined volume of thermal grease on said inner surface.
119. A method for determining temperature and conductivity of a subject media, said method comprising the steps of:
thermally coupling a thermal well and a sensing probe such that temperature and conductivity can be determined;
transferring thermal and conductivity signals through at least 3 leads from said sensing probe; and determining temperature and conductivity using said signals.
thermally coupling a thermal well and a sensing probe such that temperature and conductivity can be determined;
transferring thermal and conductivity signals through at least 3 leads from said sensing probe; and determining temperature and conductivity using said signals.
120. A method for detecting air in a fluid line, said method comprising:
thermally coupling at least two thermal wells located in a fluid line to sensing probes such that temperature and conductivity can be determined;
transferring conductivity signals through at least 3 leads from said sensing probes;
determining conductivity for each sensing probe;
calculating the difference of conductivity from each sensing probe; and determining if said difference exceeds a threshold.
thermally coupling at least two thermal wells located in a fluid line to sensing probes such that temperature and conductivity can be determined;
transferring conductivity signals through at least 3 leads from said sensing probes;
determining conductivity for each sensing probe;
calculating the difference of conductivity from each sensing probe; and determining if said difference exceeds a threshold.
121. Apparatus comprising a fluid conduit including a well for at least one of transmitting temperature and permitting conductivity sensing of fluid passing through the conduit, wherein the well is adapted for interconnection with a sensor.
122. Apparatus according to claim 121, configured so that a portion of the well comes into contact with fluid in the conduit.
123. Apparatus according to claim 121, configured so that no portion of the well comes into contact with fluid in the conduit.
124. Apparatus according to claim 121, wherein the fluid conduit comprises plastic tubing.
125. Apparatus according to claim 121, wherein the fluid conduit comprises metal tubing.
126. Apparatus according to claim 121, wherein the well and the conduit are integrally formed from the same material.
127. Apparatus according to claim 121, wherein the well is coupled to the fluid conduit.
128. Apparatus according to claim 127, wherein the well is coupled to the fluid conduit using at least one of press fit connection, flexible tabs, adhesive, ultrasonic weld, and a retaining plate and fastener.
129. Apparatus according to claim 127, further including an o-ring between the well and the fluid conduit.
130. Apparatus according to claim 128, wherein the o-ring includes one of a round cross-section, a square cross-section, and an X-shaped cross-section.
131. Apparatus according to claim 129, wherein the well includes a groove to receive a portion of the o-ring.
132. Apparatus according to claim 127, wherein a portion of the well in contact with the conduit is flexible so as to deform the conduit.
133. Apparatus according to claim 132, wherein the portion of the well in contact with the conduit includes a plurality of cuts to provide such flexibility.
134. Apparatus according to claim 121, wherein the well is embedded in the fluid conduit.
135. Apparatus according to claim 134, wherein the well is insert molded into the fluid conduit.
136. Apparatus according to claim 121, wherein the well and the conduit are made of different materials.
137. Apparatus according to claim 136, wherein the conduit is plastic and the well is metallic.
138. Apparatus according to claim 127, wherein the well includes protrusions to help secure the well to the conduit.
139. Apparatus according to claim 121, wherein the conduit has an inner surface and an outer surface and wherein a sensor end of the well is flush with the outer surface.
140. Apparatus according to claim 121, wherein the conduit has an inner surface and an outer surface and wherein a sensor end of the well protrudes beyond the outer surface.
141. Apparatus according to claim 121, wherein the conduit has an inner surface and an outer surface and wherein a sensor end of the well is recessed from the outer surface.
142. A fluid pumping apparatus comprising at least one pump and a well for at least one of transmitting temperature and permitting conductivity sensing of fluid passing through the conduit, wherein the well is adapted for interconnection with a sensor.
143. A fluid pumping apparatus according to claim 142, wherein the at least one pump includes at least one pod pump.
144. A fluid pumping apparatus according to claim 143, wherein the at least one pod pump comprises a pair of pod pumps.
145. A fluid pumping apparatus according to claim 142, wherein the at least one pump and the well are integrated into a cassette.
146. A sensing system comprising:
a sensing probe as in any of claims 99-114; and a well as in any of claims 121-141, the well in communication with the sensing probe for at least one of thermal sensing and conductivity sensing.
a sensing probe as in any of claims 99-114; and a well as in any of claims 121-141, the well in communication with the sensing probe for at least one of thermal sensing and conductivity sensing.
147. A method for heating or cooling a fluid, the method comprising:
providing at least one reciprocating positive-displacement pump, each pump having:
a curved rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing fluid through the rigid chamber wall into the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing fluid through the rigid chamber wall out of the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow out of the pumping chamber;
providing a heat exchanger; and pumping.the fluid from a source using the at least one reciprocating positive-displacement pump so as to cause the fluid to pass through the heat exchanger.
providing at least one reciprocating positive-displacement pump, each pump having:
a curved rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing fluid through the rigid chamber wall into the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow into the pumping chamber;
and an outlet for directing fluid through the rigid chamber wall out of the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow out of the pumping chamber;
providing a heat exchanger; and pumping.the fluid from a source using the at least one reciprocating positive-displacement pump so as to cause the fluid to pass through the heat exchanger.
148. A method according to claim 147, wherein each pump is provided with a rigid chamber wall that is hemispheroid.
149. A method according to claim 147, wherein each pump is provided with a rigid limit structure for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit structure defining an actuation chamber.
150. A method according to claim 149, wherein each pump is provided with a rigid chamber wall that is hemispheroid and a rigid limit structure that is hemispheroid, such that the pumping chamber is spheroid when the membrane is urged against the rigid limit structure and the actuation chamber is spheroid when the membrane is urged against the rigid chamber wall.
151. A method according to claim 147, wherein providing the at least one reciprocating positive-displacement pump comprises:
providing a pair of reciprocating positive-displacement pumps as in any of the preceding claims.
providing a pair of reciprocating positive-displacement pumps as in any of the preceding claims.
152. A method according to claim 151, wherein pumping the fluid comprises:
operating the pair of pumps out of phase so as to produce a substantially continuous fluid flow.
operating the pair of pumps out of phase so as to produce a substantially continuous fluid flow.
153. A method according to claim 147, wherein pumping the fluid comprises:
providing a disposable unit including a heat-exchanger component;
placing the heat-exchanger component in proximity with the heat exchanger;
and pumping the fluid through the heat-exchanger component so as to heat or cool the fluid in the heat-exchanger component.
providing a disposable unit including a heat-exchanger component;
placing the heat-exchanger component in proximity with the heat exchanger;
and pumping the fluid through the heat-exchanger component so as to heat or cool the fluid in the heat-exchanger component.
154. A method according to claim 153, wherein the heat-exchanger component includes at least one of a heat-exchanger bag, a length of tubing, and a radiator.
155. A method according to claim 147, wherein the source is a patient and wherein the fluid is a bodily fluid.
156. A method according to claim 147, further comprising:
pumping the heated fluid to a patient.
pumping the heated fluid to a patient.
157. A method according to claim 156, further comprising:
monitoring the patient's temperature; and controlling operation of at least one of (a) the at least one pump and (b) the heat exchanger in order to attain a predetermined patient temperature.
monitoring the patient's temperature; and controlling operation of at least one of (a) the at least one pump and (b) the heat exchanger in order to attain a predetermined patient temperature.
158. A method according to claim 157, wherein monitoring the patient's temperature comprises:
taking a temperature reading from a first location in the patient's body;
taking a temperature reading from a second location in the patient's body;
comparing the temperature readings from the first and second locations;
generating a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location;
determining if the temperature reading from the first location is above a pre-set upper limit; and generating a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
taking a temperature reading from a first location in the patient's body;
taking a temperature reading from a second location in the patient's body;
comparing the temperature readings from the first and second locations;
generating a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location;
determining if the temperature reading from the first location is above a pre-set upper limit; and generating a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
159. A method according to claim 149, further comprising:
providing a pneumatic actuation system for intermittently providing either a positive or a negative pressure to the actuation chamber of each pump.
providing a pneumatic actuation system for intermittently providing either a positive or a negative pressure to the actuation chamber of each pump.
160. A method according to claim 159, wherein the pneumatic actuation system is provided with:
a reservoir containing a gas at either a positive or a negative pressure, and a valving mechanism for controlling the flow of gas between the gas reservoir and the actuation chamber of each pump.
a reservoir containing a gas at either a positive or a negative pressure, and a valving mechanism for controlling the flow of gas between the gas reservoir and the actuation chamber of each pump.
161. A method according to claim 160, wherein the pneumatic actuation system is further provided with at least one actuation-chamber pressure transducer for measuring the pressure of the actuation chamber of each pump, and a controller that receives pressure information from the at least one actuation-chamber pressure transducer and controls the valving mechanism.
162. A method according to claim 161, wherein the pneumatic actuation system is further provided with a reservoir pressure transducer for measuring the pressure of the gas in the reservoir, and wherein the controller receives pressure information from the reservoir pressure transducer.
163. A method according to claim 162, wherein the controller compares the pressure information from the actuation-chamber and reservoir pressure transducers to determine whether any of the pressure transducers is malfunctioning.
164. A method according to claim 149, further comprising:
providing a pneumatic actuation system for alternately providing positive and negative pressure to the actuation chamber of each pump.
providing a pneumatic actuation system for alternately providing positive and negative pressure to the actuation chamber of each pump.
165. A method according to claim 164, wherein the pneumatic actuation system is provided with:
a positive-pressure gas reservoir;
a negative-pressure gas reservoir; and a valving mechanism for controlling the flow of gas between the gas reservoirs and the actuation chamber of each pump.
a positive-pressure gas reservoir;
a negative-pressure gas reservoir; and a valving mechanism for controlling the flow of gas between the gas reservoirs and the actuation chamber of each pump.
166. A method according to claim 165, wherein the pneumatic actuation system is further provided with:
at least one actuation-chamber pressure transducer for measuring the pressure of the actuation chamber of each pump, and a controller that receives pressure information from the at least one actuation-chamber pressure transducer and controls the valving mechanism.
at least one actuation-chamber pressure transducer for measuring the pressure of the actuation chamber of each pump, and a controller that receives pressure information from the at least one actuation-chamber pressure transducer and controls the valving mechanism.
167. A method according to claim 166, wherein the pneumatic actuation system is further provided with:
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure gas reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure gas reservoir, wherein the controller receives pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure gas reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure gas reservoir, wherein the controller receives pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
168. A method according to claim 167, wherein the controller compares the pressure information from the actuation-chamber, positive-pressure-reservoir, and negative-pressure reservoir pressure transducers to determine whether any of the pressure transducers are malfunctioning.
169. A method according to claim 168, wherein the controller causes dithering of the valving mechanism and determines an end of stroke from pressure information received from the at least one actuation-chamber pressure transducer.
170. A method according to claim 169, wherein the controller controls the valving mechanism to cause the flexible membrane of each pump to reach either the rigid chamber wall or the rigid limit structure at each of a stroke's beginning and end, and wherein the controller determines the amount of flow through each pump based on a number of strokes.
171. A method according to claim 170, wherein the controller integrates pressure information an actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
172. A method according to claim 147, wherein the inlet of each pump is provided with an inlet valve for preventing flow out of the pumping chamber through the inlet and the outlet of each pump is provided with an outlet valve for preventing flow into the pumping chamber through the outlet.
173. A method according to claim 172, wherein the inlet valve and the outlet valve are passive check valves.
174. A method according to claim 172, wherein the inlet valve and the outlet valve are actively controlled valves, and wherein pumping the fluid comprises operating the valves.
175. A disposable unit for use in a heat exchanger system, the disposable unit comprising:
at least one reciprocating positive-displacement pump, each pump having a curved rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing fluid through the rigid chamber wall into the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow into the pumping chamber; and an outlet for directing fluid through the rigid chamber wall out of the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow out of the pumping chamber; and a heat-exchanger component, in fluid communication with the at least one pump and adapted to be received by a heat exchanger.
at least one reciprocating positive-displacement pump, each pump having a curved rigid chamber wall;
a flexible membrane attached to the rigid chamber wall, so that the flexible membrane and rigid chamber wall define a pumping chamber;
an inlet for directing fluid through the rigid chamber wall into the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow into the pumping chamber; and an outlet for directing fluid through the rigid chamber wall out of the pumping chamber in at least one of (a) a direction that is substantially tangential to the rigid chamber wall and (b) a direction that provides low-shear flow out of the pumping chamber; and a heat-exchanger component, in fluid communication with the at least one pump and adapted to be received by a heat exchanger.
176. A disposable unit according to claim 175, wherein the heat-exchanger component includes at least one of a heat-exchanger bag, a length of tubing, and a radiator.
177. A disposable unit according to clam 175, wherein each pump includes a rigid chamber wall that is hemispheroid.
178. A disposable unit according to claim 175, wherein each pump includes a rigid limit structure for limiting movement of the membrane and limiting the maximum volume of the pumping chamber, the flexible membrane and the rigid limit structure defining an actuation chamber.
179. A disposable unit according to claim 150, wherein each pump includes a rigid chamber wall that is hemispheroid and a rigid limit structure that is hemispheroid, such that the pumping chamber is spheroid when the membrane is urged against the rigid limit structure and the actuation chamber is spheroid when the membrane is urged against the rigid chamber wall.
180. A disposable unit according to claim 175, wherein the at least one reciprocating positive-displacement pump comprises a pair of reciprocating positive-displacement pumps as in any of claims 175-179.
181. A disposable unit according to claim 180, wherein the pair of pumps are capable of being operated out of phase so as to produce a substantially continuous fluid flow.
182. A disposable unit according to claim 175, wherein the inlet of each pump includes an inlet valve for preventing flow out of the pumping chamber through the inlet and the outlet of each pump includes an outlet valve for preventing flow into the pumping chamber through the outlet.
183. A disposable unit according to claim 182, wherein the inlet valve and the outlet valve are passive check valves.
184. A disposable unit according to claim 182, wherein the inlet valve and the outlet valve are actively controlled valves.
185. A disposable unit according to claim 175, wherein the heat-exchanger component includes an inlet in fluid communication with the outlet of the at least one pump for pumping fluid into the heat-exchanger component for heating or cooling.
186. A disposable unit according to claim 175, wherein the heat-exchanger component includes an outlet in fluid communication with the inlet of the at least one pump for pumping heated or cooled fluid out of the heat-exchanger component.
187. A disposable unit according to claim 175, further comprising:
a filter in fluid communication with an outlet of the heat-exchanger component for filtering heated or cooled fluid flowing out of the heat-exchanger component.
a filter in fluid communication with an outlet of the heat-exchanger component for filtering heated or cooled fluid flowing out of the heat-exchanger component.
188. A disposable unit according to claim 175, further comprising:
a manifold including:
at least one inlet port for providing fluidic connection to an inlet of the heat-exchanger component; and an outlet port for providing fluidic connection to an outlet of the heat-exchanger component.
a manifold including:
at least one inlet port for providing fluidic connection to an inlet of the heat-exchanger component; and an outlet port for providing fluidic connection to an outlet of the heat-exchanger component.
189. A disposable unit according to claim 188, wherein the manifold includes a pair of inlet ports for providing fluidic connection to the inlet of the heat-exchanger component.
190. A disposable unit according to claim 189, wherein the at least one reciprocating positive-displacement pump comprises a pair of reciprocating positive-displacement pumps as in any of claims 175-179, and wherein the pair of pumps are coupled to the pair of inlet ports.
191. A disposable unit according to claim 190, wherein the outlets of the pair of pumps are coupled respectively to the pair of inlet ports.
192. A disposable unit according to claim 188, wherein the manifold further includes at least one sensor component, each sensor component disposed in a port and capable of transmitting thermal information regarding fluid passing through the port.
193. A disposable unit according to claim 192, wherein the manifold includes an inlet sensor component disposed in an inlet port and an outlet sensor component disposed in the outlet port.
194. A disposable unit according to claim 192, wherein each sensor component includes a thermal well.
195. A disposable unit according to claim 175, wherein the manifold includes:
an inlet fluid channel connector coupled to the inlet of the heat-exchanger component and in fluid communication with the at least one inlet port; and an outlet fluid channel connector coupled to the outlet of the heat-exchanger component and in fluid communication with the outlet port.
an inlet fluid channel connector coupled to the inlet of the heat-exchanger component and in fluid communication with the at least one inlet port; and an outlet fluid channel connector coupled to the outlet of the heat-exchanger component and in fluid communication with the outlet port.
1 96. A disposable unit according to claim 175, further comprising:
a patient connection circuit coupled to the at least one pump and in fluid communication with the heat-exchanger component.
a patient connection circuit coupled to the at least one pump and in fluid communication with the heat-exchanger component.
197 A disposable unit according to claim 196, wherein the patient connection circuit includes a length of tubing and a protective material covering a portion of the length of tubing.
198. A disposable unit according to claim 196, further comprising:
a fluid delivery line in fluid communication with the patient connection circuit.
a fluid delivery line in fluid communication with the patient connection circuit.
199. A disposable unit according to claim 198, wherein the fluid delivery line includes a connector for coupling with a fluid source.
200. A disposable unit according to claim 175, further comprising:
a separate fluid inlet in fluid communication with the heat-exchanger component.
a separate fluid inlet in fluid communication with the heat-exchanger component.
201. A disposable unit according to claim 200, wherein the separate fluid inlet includes at least one of a luer port, a syringe interface, and a spike.
202. A disposable unit according to claim 175, wherein the at least one pump is integrated into a cassette.
203. A heat-exchanger system comprising:
a heat exchanger for receiving a heat-exchanger component of a disposable unit according to any one of claims 175-202;
a pneumatic actuation system for operating at least one pump of the disposable unit for pumping fluid through the heat-exchanger component; and a controller for controlling the pneumatic actuation system.
a heat exchanger for receiving a heat-exchanger component of a disposable unit according to any one of claims 175-202;
a pneumatic actuation system for operating at least one pump of the disposable unit for pumping fluid through the heat-exchanger component; and a controller for controlling the pneumatic actuation system.
204. A heat-exchanger system according to claim 203, further comprising the disposable unit.
205. A heat-exchanger system according to claim 203, further including first and second temperature probes located in a patient's body, and wherein the controller is adapted for monitoring the patient's temperature based on readings from the first and second temperature probes.
206. A heat-exchanger system according to claim 205, wherein the controller is adapted to compare the temperature readings from the first and second locations;
generate a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location; determine if the temperature reading from the first or second location is above a pre-set upper limit; and generate a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
generate a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location; determine if the temperature reading from the first or second location is above a pre-set upper limit; and generate a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
207. A heat-exchanger system according to claim 203, wherein the pneumatic actuation system includes:
a reservoir containing a gas at either a positive or a negative pressure; and a valving mechanism for controlling the flow of gas between the at least one pump and the gas reservoir.
a reservoir containing a gas at either a positive or a negative pressure; and a valving mechanism for controlling the flow of gas between the at least one pump and the gas reservoir.
208. A heat-exchanger system according to claim 207, further including:
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber, wherein the controller is adapted to receive pressure information from the actuation-chamber pressure transducer and control the valving mechanism.
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber, wherein the controller is adapted to receive pressure information from the actuation-chamber pressure transducer and control the valving mechanism.
209. A heat-exchanger system according to claim 208, further including:
a reservoir pressure transducer for measuring the pressure of the pressure of gas in the reservoir, wherein the controller is adapted to receive pressure information from the reservoir pressure transducer.
a reservoir pressure transducer for measuring the pressure of the pressure of gas in the reservoir, wherein the controller is adapted to receive pressure information from the reservoir pressure transducer.
210. A heat-exchanger system according to claim 209, wherein the controller is adapted to compare the pressure information from the actuation-chamber and reservoir pressure transducers to determine whether either of the pressure transducers are malfunctioning.
211. A heat-exchanger system according to claim 203, wherein the pneumatic actuation system is adapted to alternately provide positive and negative pressure to the at least one pump.
212. A heat-exchanger system according to claim 211, wherein the pneumatic actuation system includes:
a positive-pressure gas .reservoir;
a negative-pressure gas reservoir; and a valving mechanism for controlling the flow of ga.s between the at least one pump and each of the gas reservoirs.
a positive-pressure gas .reservoir;
a negative-pressure gas reservoir; and a valving mechanism for controlling the flow of ga.s between the at least one pump and each of the gas reservoirs.
213. A heat-exchanger system according to claim 212, further including:
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
an actuation-chamber pressure transducer for measuring the pressure of the actuation chamber; and a controller that receives pressure information from the actuation-chamber pressure transducer and controls the valving mechanism.
214. A heat-exchanger system according to claim 213, further including:
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure gas reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure gas reservoir, wherein the controller is adapted to receive pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
a positive-pressure-reservoir pressure transducer for measuring the pressure of the positive-pressure gas reservoir; and a negative-pressure-reservoir pressure transducer for measuring the pressure of the negative-pressure gas reservoir, wherein the controller is adapted to receive pressure information from the positive-pressure-reservoir and negative-pressure-reservoir pressure transducers.
215. A heat-exchanger system according to claim 214, wherein the controller compares the pressure information from the actuation-chamber, positive-pressure-reservoir and negative-pressure reservoir pressure transducers to determine whether any of the pressure transducers are malfunctioning.
216 A heat-exchanger system according to one of claims 208 or 213, wherein the controller is adapted to cause dithering of the valving mechanism and determines when a pump stroke ends from pressure information received from the actuation-chamber pressure transducer.
217. A heat-exchanger system according to one of claims 207 or 212, wherein the controller is adapted to control the valving mechanism to cause complete pump strokes, and wherein the controller is adapted to determine the amount of flow through the at least one pump based on a number of strokes.
218. A heat-exchanger system according to one of claims 208 or 213, wherein the controller is adapted to integrate pressure information from the actuation-chamber pressure transducer over time during a stroke to detect an aberrant flow condition.
219. A heat-exchanger system according to claim 203, adapted for pumping and heating blood.
220. A heat-exchanger system according to claim 203, wherein the heat exchanger includes a heating or cooling plate.
221. A heat-exchanger system according to claim 220, wherein the plate is adapted to receive a heat-exchanger bag.
222. A heat-exchanger system according to claim 220, wherein the plate is adapted to receive a heat-exchanger radiator cartridge.
223. A heat-exchanger system according to claim 220, wherein the plate includes an integral radiator having a channel for receiving a length of tubing.
224. A heat-exchanger system according to claim 223, wherein the channel comprises:
an inner loop;
an outer loop; and a serpentine portion connecting the inner and outer loops, such that fluid flowing through portions of tubing disposed in the inner and outer loops of the channel flow in opposite directions.
an inner loop;
an outer loop; and a serpentine portion connecting the inner and outer loops, such that fluid flowing through portions of tubing disposed in the inner and outer loops of the channel flow in opposite directions.
225. A heat-exchanger system according to claim 203, further comprising:
a manifold interface for receiving a manifold of the disposable unit,
a manifold interface for receiving a manifold of the disposable unit,
226. A heat-exchanger system according to claim 225, wherein the manifold interface includes at least one sensor for mating with a corresponding sensor component of the manifold.
227. A heat-exchanger system according to claim 226, wherein the controller is adapted to receive temperature information from the at least one sensor and control at least one of the heat exchanger and the pneumatic actuation system based on the temperature information.
228. A heat-exchanger system according to claim 226, wherein the controller is adapted to utilize the at least one sensor for measuring conductivity.
229. A heat-exchanger system according to claim 225, wherein the manifold interface includes at least one pneumatic interface for providing pneumatic pressure to the at least one pump.
230. A heat-exchanger system according to claim 225, wherein the manifold interface includes a data key interface for receiving a data key of the disposable unit, and wherein the controller is adapted to control the heat exchanger and the pneumatic interface based on information received from the data key via the data key interface.
231. A heat-exchanger system according to claim 230, wherein the controller is further adapted to transmit information to the data key via the data key interface.
232. A radiator for use in a heat-exchanger system, the radiator comprising:
a body including a thermally conductive material; and a channel disposed in the body for receiving a length of tubing.
a body including a thermally conductive material; and a channel disposed in the body for receiving a length of tubing.
233 A radiator according to claim 232, wherein the channel comprises:
an inner loop;
an outer loop; and a serpentine portion connecting the inner and outer loops, such that fluid flowing through portions of tubing disposed in the inner and outer loops of the channel flow in opposite directions.
an inner loop;
an outer loop; and a serpentine portion connecting the inner and outer loops, such that fluid flowing through portions of tubing disposed in the inner and outer loops of the channel flow in opposite directions.
234. A method of moving blood between a patient-access device and a heat exchanger for heating the blood, the method comprising:
providing a reciprocating positive-displacement pump;
providing a flow line having a first portion between the patient-access device and the pump and having a second portion between the pump and the heat exchanger;
providing for each of the first and second portions of the flow line a valve for permitting flow in only one direction of the flow line; and actuating the pump to cause the flow of blood between the patient-access device and the heat exchanger.
providing a reciprocating positive-displacement pump;
providing a flow line having a first portion between the patient-access device and the pump and having a second portion between the pump and the heat exchanger;
providing for each of the first and second portions of the flow line a valve for permitting flow in only one direction of the flow line; and actuating the pump to cause the flow of blood between the patient-access device and the heat exchanger.
235 A method according to claim 234, wherein the pump is provided with a flexible membrane as a reciprocating member.
236. A method according to claim 235, wherein the pump is provided with a pneumatic actuation system for alternately providing positive and negative pressure to the membrane.
237. A method according to claim 234, further including monitoring the patient's temperature.
238. A method according to claim 237, wherein monitoring the patient's temperature includes taking a temperature reading from a first location in the patient's body;
taking a temperature reading from a second location in the patient's body;
comparing the temperature readings from the first and second locations;
generating a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location;
determining if the temperature reading from the first or second location is above a pre-set upper limit; and generating a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
taking a temperature reading from a second location in the patient's body;
comparing the temperature readings from the first and second locations;
generating a first alarm signal indicating faulty temperature readings, if the temperature reading at the first location is not within a pre-set range from the temperature reading at the second location;
determining if the temperature reading from the first or second location is above a pre-set upper limit; and generating a second alarm signal indicating an overheated condition, if a reading is above the pre-set upper limit.
239. A system for extracorporeal thermal therapy, the system comprising:
a heat exchanger for heating the blood;
a reciprocating positive-displacement pump for moving blood between a patient-access device and the heat exchanger, the pump having an inlet line and an outlet line;
a first valve, located in the inlet line, for preventing flow of blood out of the pump; and a second valve, located in the outlet line, for preventing flow of blood into the pump.
a heat exchanger for heating the blood;
a reciprocating positive-displacement pump for moving blood between a patient-access device and the heat exchanger, the pump having an inlet line and an outlet line;
a first valve, located in the inlet line, for preventing flow of blood out of the pump; and a second valve, located in the outlet line, for preventing flow of blood into the pump.
240. A system according to claim 239, wherein the pump includes a flexible membrane as a reciprocating member.
241. A system according to claim 240, wherein the pump is adapted to be actuated by a pneumatic actuation system that alternately provides positive and negative pressure to the membrane to cause the membrane to reciprocate.
242. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising a pump according to one of above claims, and further including a heat-exchange flow path having an inlet for unheated blood an outlet for heated blood;
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a first temperature sensor located at the inlet for measuring the temperature of the blood entering the heat exchanger;
a second temperature sensor located at the outlet for measuring the temperature of the blood exiting the heat exchanger;
a metering system that measures the flow rate of blood passing through the heat exchanger; and a controller in communication with the converter, the first and second temperature sensors, and the metering system, the controller receiving information regarding the amount of power being used by the converter, receiving temperature information from the first and second temperature sensors, receiving flow-rate information from the metering system, analyzing the received information in order to determine whether a fault condition exists, and generating a signal if a fault condition is detected.
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a first temperature sensor located at the inlet for measuring the temperature of the blood entering the heat exchanger;
a second temperature sensor located at the outlet for measuring the temperature of the blood exiting the heat exchanger;
a metering system that measures the flow rate of blood passing through the heat exchanger; and a controller in communication with the converter, the first and second temperature sensors, and the metering system, the controller receiving information regarding the amount of power being used by the converter, receiving temperature information from the first and second temperature sensors, receiving flow-rate information from the metering system, analyzing the received information in order to determine whether a fault condition exists, and generating a signal if a fault condition is detected.
243. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising:
an inlet for unheated blood;
an outlet for heated blood;
a flow path from the inlet to the outlet;
a set of heating elements overlapping the flow path, including at least first and second heating elements, the second heating element being located adjacent the flow path near the outlet, and the first heating element being located adjacent the flow path at a point upstream of the second heating element;
a first temperature sensor located adjacent the flow path upstream of the first heating element;
a second temperature sensor located adjacent the flow path between the first and second heating elements; and a controller for receiving temperature information from the first and second temperature sensors and for generating a signal if a temperature difference being measured by the first and second sensors exceeds a limit.
an inlet for unheated blood;
an outlet for heated blood;
a flow path from the inlet to the outlet;
a set of heating elements overlapping the flow path, including at least first and second heating elements, the second heating element being located adjacent the flow path near the outlet, and the first heating element being located adjacent the flow path at a point upstream of the second heating element;
a first temperature sensor located adjacent the flow path upstream of the first heating element;
a second temperature sensor located adjacent the flow path between the first and second heating elements; and a controller for receiving temperature information from the first and second temperature sensors and for generating a signal if a temperature difference being measured by the first and second sensors exceeds a limit.
244. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising:
an inlet for unheated blood;
an outlet for heated blood;
a flow path from the inlet to the outlet;
a set of heating elements overlapping the flow path, including at least first, second and third heating elements, the third heating element being located adjacent the flow path near the outlet, the second heating element being located adjacent the flow path at a point prior to the third heating element, and the first heating element being located adjacent the flow path at a point prior to the second heating element;
a first temperature sensor located adjacent the flow path between the first and second heating elements;
a second temperature sensor located adjacent the flow path between the second and third heating elements; and a controller for receiving temperature information from the first and second temperature sensors and for generating a signal if a temperature difference being measured by the first and second sensors exceeds a limit.
an inlet for unheated blood;
an outlet for heated blood;
a flow path from the inlet to the outlet;
a set of heating elements overlapping the flow path, including at least first, second and third heating elements, the third heating element being located adjacent the flow path near the outlet, the second heating element being located adjacent the flow path at a point prior to the third heating element, and the first heating element being located adjacent the flow path at a point prior to the second heating element;
a first temperature sensor located adjacent the flow path between the first and second heating elements;
a second temperature sensor located adjacent the flow path between the second and third heating elements; and a controller for receiving temperature information from the first and second temperature sensors and for generating a signal if a temperature difference being measured by the first and second sensors exceeds a limit.
245. A heat exchanger according to claim 244, wherein the flow path courses through a substantially planar disposable unit.
246. A heat exchanger according to claim 245, further including at least a first thermally conductive /late located between the heating elements and the disposable unit.
247. A heat exchanger according to claim 246, further including a second thermally conductive plate located adjacent the disposable unit opposite the first thermally conductive plate;
a second set of heating elements located on a side of the second plate opposite the disposable unit and overlapping the flow path, including at least fourth, fifth and sixth heating elements, the sixth heating element being located adjacent the flow path near the outlet, the fifth heating element being located adjacent the flow path at a point prior to the sixth heating element, and the fourth heating element being located adjacent the flow path at a point prior to the fifth heating element;
a third temperature sensor located adjacent the flow path between the fourth and fifth heating elements; and a fourth temperature sensor located adjacent the flow path between the fifth and sixth heating elements;
wherein the controller receives temperature information from the third and fourth temperature sensors and generates a signal if a temperature difference being measured by the third and fourth sensors exceeds a limit.
a second set of heating elements located on a side of the second plate opposite the disposable unit and overlapping the flow path, including at least fourth, fifth and sixth heating elements, the sixth heating element being located adjacent the flow path near the outlet, the fifth heating element being located adjacent the flow path at a point prior to the sixth heating element, and the fourth heating element being located adjacent the flow path at a point prior to the fifth heating element;
a third temperature sensor located adjacent the flow path between the fourth and fifth heating elements; and a fourth temperature sensor located adjacent the flow path between the fifth and sixth heating elements;
wherein the controller receives temperature information from the third and fourth temperature sensors and generates a signal if a temperature difference being measured by the third and fourth sensors exceeds a limit.
248. A heat exchanger according to claim 247, wherein the first and second plates are adapted to squeeze together, upon actuation by the controller, in order to urge blood out of the disposable.
249. A heat exchanger according to one of claims 244 or 247, wherein the signal generated by the controller causes an alarm indication.
250. A heat exchanger according to one of claims 244 or 247, wherein the signal generated by the controller causes the hyperthermia treatment to end.
251. A heat exchanger according to one of claims 244 or 247, further including additional heating elements being located at points along the flow path prior to the first heating element.
252. A heat exchanger according to one of claims 244 or 247, further including additional heating elements being located at points along the flow path between the first and third heating elements.
253. A heat exchanger according to claim 244, wherein the flow path is defined by a flexible bag.
254. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising:
an inlet for unheated blood;
an outlet for heated blood;
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a first temperature sensor located at the inlet for measuring the temperature of the blood entering the heat exchanger;
a second temperature sensor located at the outlet for measuring the temperature of the blood exiting the heat exchanger;
a metering system that measures the flow rate of blood passing through the heat exchanger; and a controller in communication with the converter, the first and second temperature sensors, and the metering system, the controller receiving information regarding the amount of power being used by the converter, receiving temperature information from the first and second temperature sensors, receiving flow-rate information from the metering system, analyzing the received information in order to determine whether a fault condition exists, and generating a signal if a fault condition is detected.
an inlet for unheated blood;
an outlet for heated blood;
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a first temperature sensor located at the inlet for measuring the temperature of the blood entering the heat exchanger;
a second temperature sensor located at the outlet for measuring the temperature of the blood exiting the heat exchanger;
a metering system that measures the flow rate of blood passing through the heat exchanger; and a controller in communication with the converter, the first and second temperature sensors, and the metering system, the controller receiving information regarding the amount of power being used by the converter, receiving temperature information from the first and second temperature sensors, receiving flow-rate information from the metering system, analyzing the received information in order to determine whether a fault condition exists, and generating a signal if a fault condition is detected.
255. A heat exchanger according to claim 254, further including a disposable unit containing a flow path of the blood from the inlet to the outlet, the disposable unit being made primarily of a thermoplastic material and containing a metal thermowell at each of the inlet and outlet to improve thermal conductivity between the first temperature sensor and the blood in the inlet and between the second temperature sensor and the blood in the outlet.
256. A heat exchanger according to claim 255, further including at least a first thermally conductive plate for conducting heat from the converter to the disposable.
257. A heat exchanger according to claim 256, further including an electrical-conductivity sensor for measuring the resistance between a thermowell and the first plate, the controller being in communication with the electrical-conductivity sensor and generating a second signal if the measured resistance is too low.
258. A heat exchanger according to claim 257, further including a second thermally conductive plate for conducting heat from the converter to a side of the disposable opposite the first plate.
259. A heat exchanger according to claim 258, wherein the electrical-conductivity sensor for measuring the resistance between a thermowell and the second plate, the controller being in communication with the electrical-conductivity sensor and generating a second signal if the measured resistance between the thermowell and second plate is too low.
260. A heat exchanger according to claim 259, wherein the first and second plates are adapted to squeeze together, upon actuation by the controller, in order to urge blood out of the disposable.
261. A heat exchanger according to one of claims 254, 257, or 259, wherein the signal generated by the controller causes an alarm indication.
262. A heat exchanger according to one of claims 254, 257, or 259, wherein the signal generated by the controller causes the hyperthermia treatment to end.
263. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising:
an inlet for unheated blood;
an outlet for heated blood;
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a disposable unit containing a flow path of the blood from the inlet to the outlet, the disposable unit being made primarily of a thermoplastic material;
an electrical-conductivity sensor for measuring the resistance between the blood in the flow path a thermowell and the converter; and a controller in communication with the electrical-conductivity sensor and generating a signal if the measured resistance does not satisfy a safety parameter.
an inlet for unheated blood;
an outlet for heated blood;
an electricity-to-heat converter that turns electrical power into heat for absorption by the blood;
a disposable unit containing a flow path of the blood from the inlet to the outlet, the disposable unit being made primarily of a thermoplastic material;
an electrical-conductivity sensor for measuring the resistance between the blood in the flow path a thermowell and the converter; and a controller in communication with the electrical-conductivity sensor and generating a signal if the measured resistance does not satisfy a safety parameter.
264. A heat exchanger according to claim 263, wherein the controller generates a signal if the measured resistance is too low.
265. A heat exchanger according to claim 263, wherein the controller generates a signal if the measured resistance is too high.
266. A heat exchanger for heating extracorporeal blood for hyperthermia treatment, the heat exchanger comprising:
a disposable unit having an inlet for unheated blood, an outlet for heated blood, and a flow path of the blood from the inlet to the outlet; and a base unit having a heater for heating blood in the flow path, the heater including a first thermally conductive plate for conducting heat to a first side of the disposable unit, and a second thermally conductive plate for conducting heat to a second side of the disposable unit opposite the first plate, the first and second plates being adapted to squeeze together, upon actuation by a controller, in order to urge blood out of the disposable.
a disposable unit having an inlet for unheated blood, an outlet for heated blood, and a flow path of the blood from the inlet to the outlet; and a base unit having a heater for heating blood in the flow path, the heater including a first thermally conductive plate for conducting heat to a first side of the disposable unit, and a second thermally conductive plate for conducting heat to a second side of the disposable unit opposite the first plate, the first and second plates being adapted to squeeze together, upon actuation by a controller, in order to urge blood out of the disposable.
267. A method of locating temperature probes for monitoring a patient's temperature, the method comprising:
taking temperature readings from a first temperature probe to be located at a first location in the patient's body;
taking temperature readings from a second temperature probe to be located at a second location in the patient's body;
comparing the temperature readings from the first and second probes;
positioning the first and second temperature probes in the patient's body;
determining if the temperature reading from the first or second location is above a pre-set limit; and generating a placement signal, if the temperature reading from the first probe is within a pre-set range from the temperature reading from the second probe, and if the reading from the first or second location is above a pre-set limit.
taking temperature readings from a first temperature probe to be located at a first location in the patient's body;
taking temperature readings from a second temperature probe to be located at a second location in the patient's body;
comparing the temperature readings from the first and second probes;
positioning the first and second temperature probes in the patient's body;
determining if the temperature reading from the first or second location is above a pre-set limit; and generating a placement signal, if the temperature reading from the first probe is within a pre-set range from the temperature reading from the second probe, and if the reading from the first or second location is above a pre-set limit.
268. A method of providing a hyperthermic treatment to a patient, the method comprising:
providing a heat-exchanger system for heating blood from the patient and pumping heated blood to the patient;
connecting a first temperature probe from the patient to the heat-exchanger system, the heat-exchanger system controlling the blood heating and pumping based on temperature information received from the first temperature probe and displaying the temperature information received from the first temperature probe to an operator;
monitoring patient temperature by the operator using an independent second temperature probe; and terminating the treatment if either of the temperature probes conveys an unacceptable temperature reading.
providing a heat-exchanger system for heating blood from the patient and pumping heated blood to the patient;
connecting a first temperature probe from the patient to the heat-exchanger system, the heat-exchanger system controlling the blood heating and pumping based on temperature information received from the first temperature probe and displaying the temperature information received from the first temperature probe to an operator;
monitoring patient temperature by the operator using an independent second temperature probe; and terminating the treatment if either of the temperature probes conveys an unacceptable temperature reading.
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Families Citing this family (289)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1998038953A1 (en) * | 1997-03-03 | 1998-09-11 | Medical Solutions, Inc. | Method and apparatus for pressure infusion and temperature control of infused liquids |
US6467953B1 (en) | 1999-03-30 | 2002-10-22 | Medical Solutions, Inc. | Method and apparatus for monitoring temperature of intravenously delivered fluids and other medical items |
US6877713B1 (en) | 1999-07-20 | 2005-04-12 | Deka Products Limited Partnership | Tube occluder and method for occluding collapsible tubes |
US7238171B2 (en) | 2001-03-12 | 2007-07-03 | Medical Solutions, Inc. | Method and apparatus for controlling pressurized infusion and temperature of infused liquids |
US8226605B2 (en) | 2001-12-17 | 2012-07-24 | Medical Solutions, Inc. | Method and apparatus for heating solutions within intravenous lines to desired temperatures during infusion |
AU2003230862A1 (en) | 2002-04-11 | 2003-10-27 | Deka Products Limited Partnership | System and method for delivering a target volume of fluid |
DE10224750A1 (en) | 2002-06-04 | 2003-12-24 | Fresenius Medical Care De Gmbh | Device for the treatment of a medical fluid |
CA2479720C (en) * | 2004-08-26 | 2007-03-13 | Dryair Inc. | Reversing circulation for heating and cooling conduits |
US7611504B1 (en) | 2004-03-09 | 2009-11-03 | Patented Medical Solutions Llc | Method and apparatus for facilitating injection of medication into an intravenous fluid line while maintaining sterility of infused fluids |
US20060217771A1 (en) | 2005-02-07 | 2006-09-28 | Medtronic, Inc. | Potassium monitoring |
US8197231B2 (en) | 2005-07-13 | 2012-06-12 | Purity Solutions Llc | Diaphragm pump and related methods |
US7951182B2 (en) * | 2005-07-14 | 2011-05-31 | Zoll Circulation, Inc. | System and method for leak detection in external cooling pad |
US8092414B2 (en) | 2005-11-09 | 2012-01-10 | Nxstage Medical, Inc. | Diaphragm pressure pod for medical fluids |
US10010686B2 (en) * | 2006-02-27 | 2018-07-03 | Ivenix, Inc. | Fluid control system and disposable assembly |
US20080240929A1 (en) * | 2007-03-30 | 2008-10-02 | Deka Products Limited Partnership | Pumping Cassette |
US20140199193A1 (en) | 2007-02-27 | 2014-07-17 | Deka Products Limited Partnership | Blood treatment systems and methods |
US10537671B2 (en) | 2006-04-14 | 2020-01-21 | Deka Products Limited Partnership | Automated control mechanisms in a hemodialysis apparatus |
US8366316B2 (en) * | 2006-04-14 | 2013-02-05 | Deka Products Limited Partnership | Sensor apparatus systems, devices and methods |
CA3123166A1 (en) | 2006-04-14 | 2007-10-25 | Deka Products Limited Partnership | Systems, devices and methods for fluid pumping, heat exchange, thermal sensing, and conductivity sensing |
US8497683B2 (en) * | 2006-10-03 | 2013-07-30 | Invensys Systems, Inc. | Spectroscopic sample analyzer and sample handling system |
US9476847B2 (en) | 2006-10-03 | 2016-10-25 | Invensys Systems, Inc. | Spectroscopic crude oil analysis |
US7667461B2 (en) * | 2006-10-03 | 2010-02-23 | Invensys Systems, Inc. | Sample analyzer and sampling system |
US8425471B2 (en) | 2007-02-27 | 2013-04-23 | Deka Products Limited Partnership | Reagent supply for a hemodialysis system |
US10463774B2 (en) | 2007-02-27 | 2019-11-05 | Deka Products Limited Partnership | Control systems and methods for blood or fluid handling medical devices |
AU2016204226B2 (en) * | 2007-02-27 | 2017-08-24 | Deka Products Limited Partnership | Sensor apparatus systems, devices and methods |
US8491184B2 (en) | 2007-02-27 | 2013-07-23 | Deka Products Limited Partnership | Sensor apparatus systems, devices and methods |
US9517295B2 (en) | 2007-02-27 | 2016-12-13 | Deka Products Limited Partnership | Blood treatment systems and methods |
US8357298B2 (en) * | 2007-02-27 | 2013-01-22 | Deka Products Limited Partnership | Hemodialysis systems and methods |
US8042563B2 (en) | 2007-02-27 | 2011-10-25 | Deka Products Limited Partnership | Cassette system integrated apparatus |
US9028691B2 (en) * | 2007-02-27 | 2015-05-12 | Deka Products Limited Partnership | Blood circuit assembly for a hemodialysis system |
CA2681912C (en) | 2007-02-27 | 2015-09-29 | Deka Products Limited Partnership | Hemodialysis systems and methods |
US8393690B2 (en) | 2007-02-27 | 2013-03-12 | Deka Products Limited Partnership | Enclosure for a portable hemodialysis system |
US8317492B2 (en) * | 2007-02-27 | 2012-11-27 | Deka Products Limited Partnership | Pumping cassette |
US20090107335A1 (en) * | 2007-02-27 | 2009-04-30 | Deka Products Limited Partnership | Air trap for a medical infusion device |
WO2008106452A1 (en) * | 2007-02-27 | 2008-09-04 | Deka Products Limited Partnership | Peritoneal dialysis sensor apparatus systems, devices and methods |
US8562834B2 (en) * | 2007-02-27 | 2013-10-22 | Deka Products Limited Partnership | Modular assembly for a portable hemodialysis system |
US8409441B2 (en) | 2007-02-27 | 2013-04-02 | Deka Products Limited Partnership | Blood treatment systems and methods |
US7846130B2 (en) * | 2007-03-13 | 2010-12-07 | Quality In Flow Ltd. | Portable intravenous fluid heating system |
CN101686872A (en) * | 2007-03-23 | 2010-03-31 | 热治疗系统股份有限公司 | Portable hyperthermia apparatus |
US8273048B2 (en) * | 2007-04-11 | 2012-09-25 | Transonic Systems, Inc. | System and method for diverting flow to facilitate measurement of system parameters |
US7874724B2 (en) * | 2007-04-11 | 2011-01-25 | Trane International Inc. | Method for sensing the liquid level in a compressor |
US9044371B2 (en) * | 2007-06-13 | 2015-06-02 | Trailerlogic, Llc | Scalable and portable human remains cold storage system |
US8330579B2 (en) * | 2007-07-05 | 2012-12-11 | Baxter International Inc. | Radio-frequency auto-identification system for dialysis systems |
US8287724B2 (en) * | 2007-07-05 | 2012-10-16 | Baxter International Inc. | Dialysis fluid measurement systems using conductive contacts |
US20090007642A1 (en) * | 2007-07-05 | 2009-01-08 | Baxter International Inc. | Dialysis fluid measurement method and apparatus using conductive contacts |
US8328458B2 (en) * | 2007-07-20 | 2012-12-11 | Twin Bay Medical, Inc. | Sanitary clamp |
US11000407B2 (en) * | 2007-08-07 | 2021-05-11 | Belmont Instrument, Llc | Hyperthermia, system, method, and components |
US9358331B2 (en) | 2007-09-13 | 2016-06-07 | Fresenius Medical Care Holdings, Inc. | Portable dialysis machine with improved reservoir heating system |
US8597505B2 (en) | 2007-09-13 | 2013-12-03 | Fresenius Medical Care Holdings, Inc. | Portable dialysis machine |
US8535522B2 (en) | 2009-02-12 | 2013-09-17 | Fresenius Medical Care Holdings, Inc. | System and method for detection of disconnection in an extracorporeal blood circuit |
US8240636B2 (en) | 2009-01-12 | 2012-08-14 | Fresenius Medical Care Holdings, Inc. | Valve system |
US9199022B2 (en) | 2008-09-12 | 2015-12-01 | Fresenius Medical Care Holdings, Inc. | Modular reservoir assembly for a hemodialysis and hemofiltration system |
US9308307B2 (en) | 2007-09-13 | 2016-04-12 | Fresenius Medical Care Holdings, Inc. | Manifold diaphragms |
US8105487B2 (en) | 2007-09-25 | 2012-01-31 | Fresenius Medical Care Holdings, Inc. | Manifolds for use in conducting dialysis |
EP2246080B1 (en) * | 2007-10-12 | 2016-02-10 | DEKA Products Limited Partnership | An extracorporeal blood flow system |
US20100056975A1 (en) * | 2008-08-27 | 2010-03-04 | Deka Products Limited Partnership | Blood line connector for a medical infusion device |
CA2702385C (en) * | 2007-10-12 | 2017-07-18 | Deka Products Limited Partnership | Apparatus and methods for hemodialysis |
US8771508B2 (en) | 2008-08-27 | 2014-07-08 | Deka Products Limited Partnership | Dialyzer cartridge mounting arrangement for a hemodialysis system |
US8863772B2 (en) | 2008-08-27 | 2014-10-21 | Deka Products Limited Partnership | Occluder for a medical infusion system |
US8114276B2 (en) | 2007-10-24 | 2012-02-14 | Baxter International Inc. | Personal hemodialysis system |
EP2203136B1 (en) * | 2007-10-31 | 2016-09-07 | seiratherm GmbH | Apparatus for adjusting or stabilizing the body temperature of a patient |
ATE517339T1 (en) * | 2007-11-13 | 2011-08-15 | Hoffmann La Roche | INTERCHANGEABLE CONSUMABLES CASSETTE WITH INTEGRATED AIR FILTER FOR ANALYZERS |
CA2960103C (en) | 2007-11-29 | 2020-03-10 | Fredenius Medical Care Holdings, Inc. | System and method for conducting hemodialysis and hemofiltration |
US9078971B2 (en) | 2008-01-23 | 2015-07-14 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US11833281B2 (en) | 2008-01-23 | 2023-12-05 | Deka Products Limited Partnership | Pump cassette and methods for use in medical treatment system using a plurality of fluid lines |
US10195330B2 (en) | 2008-01-23 | 2019-02-05 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US8708950B2 (en) * | 2010-07-07 | 2014-04-29 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US9248225B2 (en) | 2008-01-23 | 2016-02-02 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US10201647B2 (en) | 2008-01-23 | 2019-02-12 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US7836761B2 (en) | 2008-02-07 | 2010-11-23 | Robert Brian Tonner | Immersion thermowell for temperature and water level sensing |
US20090211016A1 (en) * | 2008-02-26 | 2009-08-27 | Earl David Forrest | Bath accessory assembly |
IT1390930B1 (en) * | 2008-07-11 | 2011-10-27 | Sorin Group Italia Srl | CIRCUIT FOR EXTRACORPAL DIALYSIS WITH PERFECT TYPE CASSETTE |
US8651171B2 (en) * | 2008-11-17 | 2014-02-18 | Tai-Her Yang | Single flow circuit heat exchange device for periodic positive and reverse directional pumping |
JP5654466B2 (en) * | 2008-08-27 | 2015-01-14 | デカ・プロダクツ・リミテッド・パートナーシップ | Operation method of dialysis system |
DE102008039918A1 (en) * | 2008-08-27 | 2010-03-04 | Fresenius Medical Care Deutschland Gmbh | Heating a medical device, medical device with a heater, and method of upgrading a medical device |
EP2334234A4 (en) | 2008-09-19 | 2013-03-20 | Tandem Diabetes Care Inc | Solute concentration measurement device and related methods |
CN202222659U (en) * | 2008-09-23 | 2012-05-23 | 莱瑞达科学公司 | Air current applying device |
WO2010042667A2 (en) | 2008-10-07 | 2010-04-15 | Xcorporeal, Inc. | Thermal flow meter |
EP2334412B1 (en) | 2008-10-07 | 2019-08-21 | Fresenius Medical Care Holdings, Inc. | Priming system and method for dialysis systems |
EP2342003B1 (en) | 2008-10-30 | 2018-09-26 | Fresenius Medical Care Holdings, Inc. | Modular, portable dialysis system |
US8607854B2 (en) * | 2008-11-19 | 2013-12-17 | Tai-Her Yang | Fluid heat transfer device having plural counter flow circuits with periodic flow direction change therethrough |
US8192401B2 (en) | 2009-03-20 | 2012-06-05 | Fresenius Medical Care Holdings, Inc. | Medical fluid pump systems and related components and methods |
WO2011008858A1 (en) | 2009-07-15 | 2011-01-20 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
CA2921304C (en) | 2009-07-30 | 2018-06-05 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US9399091B2 (en) | 2009-09-30 | 2016-07-26 | Medtronic, Inc. | System and method to regulate ultrafiltration |
WO2011044329A2 (en) * | 2009-10-07 | 2011-04-14 | University Of Pittsburgh - Of The Commonwealth System Of Higher Education | Devices, systems and methods for cell modification |
CA2779296C (en) | 2009-10-30 | 2018-02-13 | Deka Products Limited Partnership | Apparatus and method for detecting disconnection of an intravascular access device |
USD669185S1 (en) * | 2009-11-12 | 2012-10-16 | Maquet Cardiopulmonary Ag | Medical device for extra-corporeal heart and/or lung support |
US8753515B2 (en) | 2009-12-05 | 2014-06-17 | Home Dialysis Plus, Ltd. | Dialysis system with ultrafiltration control |
CA2784209C (en) * | 2010-01-29 | 2018-10-30 | Kci Licensing, Inc. | Wound treatment apparatuses and methods for controlled delivery of fluids to a wound |
US8684705B2 (en) * | 2010-02-26 | 2014-04-01 | Entegris, Inc. | Method and system for controlling operation of a pump based on filter information in a filter information tag |
US8727744B2 (en) * | 2010-02-26 | 2014-05-20 | Entegris, Inc. | Method and system for optimizing operation of a pump |
WO2011112251A1 (en) | 2010-03-09 | 2011-09-15 | Profound Medical Inc. | Fluid circuits for temperature control in a thermal therapy system |
DE102010003642A1 (en) | 2010-03-15 | 2011-09-15 | Fresenius Medical Care Deutschland Gmbh | Cassette with a sensor for determining the difference between a first and a second liquid flow |
EP2567718B1 (en) * | 2010-04-20 | 2016-10-19 | Sorin Group Italia S.r.l. | Perfusion system with RFID |
US8734376B2 (en) | 2010-04-20 | 2014-05-27 | Sorin Group Italia S.R.L. | Perfusion system with RFID |
US9539374B2 (en) | 2010-05-12 | 2017-01-10 | Haemonetics Corporation | Donated blood collection kit |
US8501009B2 (en) | 2010-06-07 | 2013-08-06 | State Of Oregon Acting By And Through The State Board Of Higher Education On Behalf Of Oregon State University | Fluid purification system |
US20120081707A1 (en) * | 2010-07-02 | 2012-04-05 | Bengt Norden | Shear flow device and methods of use |
US9423803B2 (en) | 2010-07-15 | 2016-08-23 | Siemens Healthcare Diagnostics Inc. | Methods, systems, and apparatus providing temperature-controlled process fluid |
JP5539834B2 (en) * | 2010-09-30 | 2014-07-02 | テルモ株式会社 | Automatic peritoneal dialysis machine |
TWI563351B (en) * | 2010-10-20 | 2016-12-21 | Entegris Inc | Method and system for pump priming |
US8932031B2 (en) * | 2010-11-03 | 2015-01-13 | Xylem Ip Holdings Llc | Modular diaphragm pumping system |
US9072875B2 (en) | 2011-02-17 | 2015-07-07 | Yun Jin | Valve system for inflatable medical device |
EP2497507B2 (en) | 2011-03-09 | 2022-09-14 | B. Braun Avitum AG | Dialysis device |
US9624915B2 (en) | 2011-03-09 | 2017-04-18 | Fresenius Medical Care Holdings, Inc. | Medical fluid delivery sets and related systems and methods |
WO2013141896A1 (en) * | 2012-03-23 | 2013-09-26 | Nxstage Medical, Inc. | Peritoneal dialysis systems, devices, and methods |
US9861733B2 (en) | 2012-03-23 | 2018-01-09 | Nxstage Medical Inc. | Peritoneal dialysis systems, devices, and methods |
EP3542840B1 (en) | 2011-03-23 | 2023-04-26 | NxStage Medical, Inc. | Peritoneal dialysis systems |
FR2973707B1 (en) * | 2011-04-05 | 2013-03-29 | Sante Actions Innovation | INTERCHANGEABLE DEVICE FOR ADMINISTERING A CHEMOTHERAPY DRUG SOLUTION |
MX341315B (en) | 2011-04-21 | 2016-08-12 | Fresenius Medical Care Holdings Inc | Medical fluid pumping systems and related devices and methods. |
US8353870B2 (en) | 2011-04-26 | 2013-01-15 | Fresenius Medical Care Holdings, Inc. | Medical temperature sensors and related systems and methods |
US9750862B2 (en) | 2011-04-29 | 2017-09-05 | Medtronic, Inc. | Adaptive system for blood fluid removal |
US9848778B2 (en) | 2011-04-29 | 2017-12-26 | Medtronic, Inc. | Method and device to monitor patients with kidney disease |
US9456755B2 (en) | 2011-04-29 | 2016-10-04 | Medtronic, Inc. | Method and device to monitor patients with kidney disease |
CA3166031A1 (en) | 2011-05-24 | 2012-11-29 | Deka Products Limited Partnership | Hemodialysis system |
US9999717B2 (en) | 2011-05-24 | 2018-06-19 | Deka Products Limited Partnership | Systems and methods for detecting vascular access disconnection |
GB2504644A (en) | 2011-05-31 | 2014-02-05 | Nxstage Medical Inc | Pressure measurement devices, methods and systems |
US9284841B1 (en) * | 2011-07-14 | 2016-03-15 | Julie C. Vickers | Disposable heat exchanger assembly for sterile and aseptic biotechnology and pharmaceutical manufacturing applications |
EP3329953B1 (en) | 2011-07-15 | 2022-02-16 | Cardiac Assist, Inc. | Apparatus for rapidly cooling or heating the body temperature of a patient |
DE102011108784A1 (en) | 2011-07-29 | 2013-01-31 | Fresenius Medical Care Deutschland Gmbh | Method and devices for checking at least one function of a medical functional device |
EP2739325B1 (en) | 2011-08-02 | 2017-10-04 | Medtronic, Inc. | Hemodialysis system having a flow path with a controlled compliant volume |
US10857277B2 (en) | 2011-08-16 | 2020-12-08 | Medtronic, Inc. | Modular hemodialysis system |
WO2013052680A2 (en) | 2011-10-07 | 2013-04-11 | Home Dialysis Plus, Ltd. | Heat exchange fluid purification for dialysis system |
WO2013067359A2 (en) | 2011-11-04 | 2013-05-10 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
RU2624357C2 (en) | 2011-11-16 | 2017-07-03 | Конватек Текнолоджиз Инк. | Device for prevention of hold down barrel transfer in medical catheters and devices to maintain positive airway pressure |
WO2013103906A1 (en) | 2012-01-04 | 2013-07-11 | Medtronic, Inc. | Multi-staged filtration system for blood fluid removal |
US8894478B1 (en) | 2012-01-06 | 2014-11-25 | Woodrow Stillwagon | Environmental improvement system |
US9211381B2 (en) * | 2012-01-20 | 2015-12-15 | Medical Solutions, Inc. | Method and apparatus for controlling temperature of medical liquids |
WO2013121163A1 (en) | 2012-02-16 | 2013-08-22 | Quanta Fluid Solutions Limited | Blood pump |
US9144449B2 (en) | 2012-03-02 | 2015-09-29 | Csa Medical, Inc. | Cryosurgery system |
ES2670604T3 (en) * | 2012-03-12 | 2018-05-31 | Fresenius Medical Care Holdings, Inc. | Apparatus and method for discharging gas from a liquid related application |
US9574716B2 (en) | 2012-03-16 | 2017-02-21 | 1589549 Alberta Ltd. | Method of reducing leaks from a pipeline |
CA2875074A1 (en) * | 2012-03-17 | 2013-09-26 | Abbott Medical Optics Inc. | Surgical cassette |
US9180242B2 (en) | 2012-05-17 | 2015-11-10 | Tandem Diabetes Care, Inc. | Methods and devices for multiple fluid transfer |
US9364655B2 (en) | 2012-05-24 | 2016-06-14 | Deka Products Limited Partnership | Flexible tubing occlusion assembly |
US9555186B2 (en) | 2012-06-05 | 2017-01-31 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US9610392B2 (en) | 2012-06-08 | 2017-04-04 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
US9500188B2 (en) | 2012-06-11 | 2016-11-22 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
US20140052009A1 (en) * | 2012-08-15 | 2014-02-20 | Acist Medical Systems, Inc. | Monitoring blood pressure in a medical injection system |
US8888730B2 (en) | 2012-09-19 | 2014-11-18 | Sorin Group Italia S.R.L. | Perfusion system with RFID feature activation |
US10905816B2 (en) | 2012-12-10 | 2021-02-02 | Medtronic, Inc. | Sodium management system for hemodialysis |
US9201036B2 (en) | 2012-12-21 | 2015-12-01 | Fresenius Medical Care Holdings, Inc. | Method and system of monitoring electrolyte levels and composition using capacitance or induction |
US9157786B2 (en) | 2012-12-24 | 2015-10-13 | Fresenius Medical Care Holdings, Inc. | Load suspension and weighing system for a dialysis machine reservoir |
US9713666B2 (en) | 2013-01-09 | 2017-07-25 | Medtronic, Inc. | Recirculating dialysate fluid circuit for blood measurement |
US11154648B2 (en) | 2013-01-09 | 2021-10-26 | Medtronic, Inc. | Fluid circuits for sorbent cartridge with sensors |
US11565029B2 (en) | 2013-01-09 | 2023-01-31 | Medtronic, Inc. | Sorbent cartridge with electrodes |
US9707328B2 (en) | 2013-01-09 | 2017-07-18 | Medtronic, Inc. | Sorbent cartridge to measure solute concentrations |
US10543052B2 (en) | 2013-02-01 | 2020-01-28 | Medtronic, Inc. | Portable dialysis cabinet |
US9623164B2 (en) | 2013-02-01 | 2017-04-18 | Medtronic, Inc. | Systems and methods for multifunctional volumetric fluid control |
US10010663B2 (en) | 2013-02-01 | 2018-07-03 | Medtronic, Inc. | Fluid circuit for delivery of renal replacement therapies |
US10850016B2 (en) | 2013-02-01 | 2020-12-01 | Medtronic, Inc. | Modular fluid therapy system having jumpered flow paths and systems and methods for cleaning and disinfection |
US9526822B2 (en) | 2013-02-01 | 2016-12-27 | Medtronic, Inc. | Sodium and buffer source cartridges for use in a modular controlled compliant flow path |
GB201301816D0 (en) * | 2013-02-01 | 2013-03-20 | Univ Singapore | Prevention & Treatment of Neuropathy |
US9144640B2 (en) | 2013-02-02 | 2015-09-29 | Medtronic, Inc. | Sorbent cartridge configurations for improved dialysate regeneration |
US9827361B2 (en) | 2013-02-02 | 2017-11-28 | Medtronic, Inc. | pH buffer measurement system for hemodialysis systems |
EP2954504A4 (en) | 2013-02-11 | 2016-10-12 | Graco Minnesota Inc | Remote monitoring for fluid applicator system |
US10969805B2 (en) | 2013-02-11 | 2021-04-06 | Graco Minnesota Inc. | Paint sprayer distributed control and output volume monitoring architectures |
US9656029B2 (en) | 2013-02-15 | 2017-05-23 | Medical Solutions, Inc. | Plural medical item warming system and method for warming a plurality of medical items to desired temperatures |
US9561323B2 (en) | 2013-03-14 | 2017-02-07 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassette leak detection methods and devices |
US9173998B2 (en) | 2013-03-14 | 2015-11-03 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
US9180243B2 (en) | 2013-03-15 | 2015-11-10 | Tandem Diabetes Care, Inc. | Detection of infusion pump conditions |
US9421329B2 (en) | 2013-03-15 | 2016-08-23 | Tandem Diabetes Care, Inc. | Infusion device occlusion detection system |
WO2014144909A2 (en) * | 2013-03-15 | 2014-09-18 | Deka Products Limited Partnership | Blood treatment systems and methods |
MX2015013489A (en) * | 2013-03-28 | 2017-05-08 | Fresenius Medical Care Holdings Inc | Manifold diaphragms. |
WO2014189941A1 (en) | 2013-05-20 | 2014-11-27 | Stryker Corporation | Thermal control system |
US10350352B2 (en) * | 2013-05-23 | 2019-07-16 | Turnpoint Medical Devices, Inc. | Pneumatically coupled fluid control system and process with air detection and elimination |
WO2014197573A1 (en) | 2013-06-05 | 2014-12-11 | Haemonetics Corporation | Frangible rfid tag and method of producing same |
EP3666878A1 (en) * | 2013-06-06 | 2020-06-17 | Bend Research, Inc. | Aseptic sampling module and manifold |
EP3572346B1 (en) | 2013-06-18 | 2022-08-03 | Haemonetics Corporation | Rfid tag and method of securing same to object |
MX2016001196A (en) | 2013-08-01 | 2016-05-26 | Convatec Technologies Inc | Self-closing bag connector. |
US10117985B2 (en) | 2013-08-21 | 2018-11-06 | Fresenius Medical Care Holdings, Inc. | Determining a volume of medical fluid pumped into or out of a medical fluid cassette |
FR3009967A1 (en) * | 2013-09-05 | 2015-03-06 | Physio Assist | EQUIPMENT FOR TREATING AN OBSTRUCTIVE RESPIRATORY DISORDER |
EP3102107A4 (en) | 2013-11-04 | 2018-02-07 | Medtronic, Inc. | Method and device to manage fluid volumes in the body |
US9354640B2 (en) | 2013-11-11 | 2016-05-31 | Fresenius Medical Care Holdings, Inc. | Smart actuator for valve |
US10537875B2 (en) | 2013-11-26 | 2020-01-21 | Medtronic, Inc. | Precision recharging of sorbent materials using patient and session data |
US9884145B2 (en) | 2013-11-26 | 2018-02-06 | Medtronic, Inc. | Parallel modules for in-line recharging of sorbents using alternate duty cycles |
US10595775B2 (en) | 2013-11-27 | 2020-03-24 | Medtronic, Inc. | Precision dialysis monitoring and synchronization system |
US8960010B1 (en) | 2013-12-23 | 2015-02-24 | Fresenius Medical Care Holdings, Inc. | Automatic detection and adjustment of a pressure pod diaphragm |
US10292686B2 (en) * | 2013-12-30 | 2019-05-21 | General Electric Company | Damper for medical ultrasonic probe |
DE102014103507A1 (en) * | 2014-03-14 | 2015-09-17 | Fresenius Medical Care Deutschland Gmbh | Medical functional device with a valve seat for a remanentes check valve |
WO2015168280A1 (en) | 2014-04-29 | 2015-11-05 | Outset Medical, Inc. | Dialysis system and methods |
CA2951050A1 (en) * | 2014-06-04 | 2015-12-10 | Csa Medical, Inc. | Method and system for consistent, repeatable, and safe cryospray treatment of airway tissue |
EP3698826A1 (en) | 2014-06-05 | 2020-08-26 | DEKA Products Limited Partnership | System for calculating a change in fluid volume in a pumping chamber |
EP3160534A4 (en) | 2014-06-24 | 2018-03-07 | Medtronic Inc. | Stacked sorbent assembly |
US10172991B2 (en) | 2014-06-24 | 2019-01-08 | Medtronic, Inc. | Modular dialysate regeneration assembly |
CN106999347A (en) | 2014-08-08 | 2017-08-01 | 弗雷蒙科学公司 | The intelligent bag used in the physiology and/or physical parameter of bag of the sensing equipped with biological substance |
US9757505B2 (en) * | 2014-09-26 | 2017-09-12 | Fresenius Medical Care Holdings, Inc. | Pressure output device for extracorporeal hemodialysis machine |
US10729366B2 (en) * | 2014-12-02 | 2020-08-04 | Fenwal, Inc. | Spherical biomedical sampling and mixing container |
US9713665B2 (en) | 2014-12-10 | 2017-07-25 | Medtronic, Inc. | Degassing system for dialysis |
US10874787B2 (en) | 2014-12-10 | 2020-12-29 | Medtronic, Inc. | Degassing system for dialysis |
US9895479B2 (en) | 2014-12-10 | 2018-02-20 | Medtronic, Inc. | Water management system for use in dialysis |
US10098993B2 (en) | 2014-12-10 | 2018-10-16 | Medtronic, Inc. | Sensing and storage system for fluid balance |
US9829140B2 (en) * | 2015-01-08 | 2017-11-28 | Idex Health & Science Llc | Pulse dampener with automatic pressure-compensation |
US20160287432A1 (en) * | 2015-03-31 | 2016-10-06 | Zoll Circulation, Inc. | Serpentine heat exchange assembly for removable engagement with patient heat exchange system |
US10293520B1 (en) | 2015-04-06 | 2019-05-21 | The United States Of America As Represented By The Secretary Of The Air Force | Methods and apparatus for high temperature thermocouple installation |
US10576262B2 (en) | 2015-05-18 | 2020-03-03 | Convatec Technologies Inc. | Spring-loaded bag connector |
DE102015006601A1 (en) * | 2015-05-21 | 2016-11-24 | Fresenius Medical Care Deutschland Gmbh | Blood treatment device |
WO2016207109A1 (en) * | 2015-06-26 | 2016-12-29 | SEIRATHERM GmbH | Medical device and method for tempering infusion fluids in a rack-like structure |
WO2017055438A1 (en) * | 2015-09-30 | 2017-04-06 | SEIRATHERM GmbH | Temperature adjustment infusion system and method |
US10294450B2 (en) | 2015-10-09 | 2019-05-21 | Deka Products Limited Partnership | Fluid pumping and bioreactor system |
EP4043045A1 (en) | 2015-10-09 | 2022-08-17 | NxStage Medical Inc. | Body temperature measurement devices, methods, and systems |
EP3368136A4 (en) | 2015-10-29 | 2019-06-05 | ConvaTec Technologies Inc. | Valve system for inflatable devices |
WO2017078965A1 (en) | 2015-11-06 | 2017-05-11 | Medtronic, Inc | Dialysis prescription optimization for decreased arrhythmias |
EP3708835A1 (en) * | 2015-11-10 | 2020-09-16 | Repligen Corporation | Disposable alternating tangential flow filtration units |
CN105371882B (en) * | 2015-12-09 | 2017-10-17 | 中国工程物理研究院总体工程研究所 | A kind of high dynamic gondola |
US9889244B2 (en) | 2015-12-17 | 2018-02-13 | Fresenius Medical Care Holdings, Inc. | System and method for controlling venous air recovery in a portable dialysis system |
US10617809B2 (en) | 2015-12-29 | 2020-04-14 | Fresenius Medical Care Holdings, Inc. | Electrical sensor for fluids |
US10406269B2 (en) | 2015-12-29 | 2019-09-10 | Fresenius Medical Care Holdings, Inc. | Electrical sensor for fluids |
CN115054759A (en) | 2016-03-08 | 2022-09-16 | 费森尤斯医疗保健控股公司 | Method and system for generating rapidly changing pressure amplitudes in a fluid circuit in a dialysis treatment system |
EP3426320B1 (en) | 2016-03-08 | 2022-12-14 | Fresenius Medical Care Holdings, Inc. | Systems for detecting an occlusion in a blood circuit of a dialysis system |
US10578092B2 (en) | 2016-03-18 | 2020-03-03 | Deka Products Limited Partnership | Pressure control gaskets for operating pump cassette membranes |
US10994064B2 (en) | 2016-08-10 | 2021-05-04 | Medtronic, Inc. | Peritoneal dialysate flow path sensing |
US10874790B2 (en) | 2016-08-10 | 2020-12-29 | Medtronic, Inc. | Peritoneal dialysis intracycle osmotic agent adjustment |
US11202559B2 (en) | 2016-04-27 | 2021-12-21 | Csa Medical, Inc. | Vision preservation system for medical devices |
WO2017193073A1 (en) * | 2016-05-06 | 2017-11-09 | Gambro Lundia Ab | Systems and methods for peritoneal dialysis having point of use dialysis fluid preparation including mixing and heating therefore |
US11871977B2 (en) | 2016-05-19 | 2024-01-16 | Csa Medical, Inc. | Catheter extension control |
CN107411818B (en) * | 2016-05-23 | 2020-11-03 | 波士顿科学医学有限公司 | Fluidic devices, methods, and systems |
US20180003572A1 (en) * | 2016-07-01 | 2018-01-04 | Exotag Inc. | Sensor-Based Systems and Methods for Monitoring Temperature Sensitive Products |
EP3500317B1 (en) | 2016-08-19 | 2022-02-23 | Outset Medical, Inc. | Peritoneal dialysis system and methods |
US11013843B2 (en) | 2016-09-09 | 2021-05-25 | Medtronic, Inc. | Peritoneal dialysis fluid testing system |
WO2018051982A1 (en) * | 2016-09-14 | 2018-03-22 | Terumo Kabushiki Kaisha | Blood component sampling cassette, blood sampling circuit set, and blood component sampling system |
BR102016022713A2 (en) * | 2016-09-29 | 2018-05-02 | Zammi Instrumental Ltda | MEMBRANE FOR FLUID MOVEMENT CHAMBER, CAMERA AND PUMP FOR ARTIFICIAL CIRCULATORY ASSISTANCE AND PUMPING SYSTEM |
US11058572B2 (en) | 2016-10-11 | 2021-07-13 | Stryker Corporation | Thermal control system |
US20180119691A1 (en) * | 2016-10-28 | 2018-05-03 | Graco Minnesota Inc. | Flow regulating pump, system and method |
US10286343B2 (en) | 2016-10-28 | 2019-05-14 | Pall Corporation | Filter including RFID tag |
US11299705B2 (en) | 2016-11-07 | 2022-04-12 | Deka Products Limited Partnership | System and method for creating tissue |
US10981148B2 (en) | 2016-11-29 | 2021-04-20 | Medtronic, Inc. | Zirconium oxide module conditioning |
CN106441456A (en) * | 2016-12-02 | 2017-02-22 | 山西省晋城市质量技术监督检验测试所 | Coalbed methane sampling and analysis joint device |
DE102016015207A1 (en) * | 2016-12-21 | 2018-06-21 | Fresenius Medical Care Deutschland Gmbh | Actuating device and method for operating an actuating device and diaphragm pump with an actuating device and a diaphragm pump device and a blood treatment device with a diaphragm pump |
CN110088473B (en) * | 2016-12-21 | 2022-04-19 | 费森尤斯医疗护理德国有限责任公司 | Diaphragm pump device and diaphragm pump with diaphragm pump device and operating device |
DE102016125403A1 (en) * | 2016-12-22 | 2018-06-28 | Endress + Hauser Wetzer Gmbh + Co Kg | temperature sensor |
DE102017000495A1 (en) * | 2017-01-20 | 2018-07-26 | Fresenius Medical Care Deutschland Gmbh | DlALYSATKONZENTRATlON-MESSSENSORDlAGNOSE |
US10561778B2 (en) | 2017-03-02 | 2020-02-18 | Fresenius Medical Care Holdings, Inc. | Split reservoir bags and method of using split reservoir bags to improve the heating and generation of dialysate |
US11566614B2 (en) * | 2017-03-24 | 2023-01-31 | Fresenius Kabi Usa, Llc | Fluid flow control and delivery via multiple fluid pumps |
US11542936B2 (en) | 2017-03-24 | 2023-01-03 | Fresenius Kabi Usa, Llc | Fluid flow control and delivery via multiple fluid pumps |
US11110214B2 (en) | 2017-04-07 | 2021-09-07 | Fresenius Medical Care Holdings, Inc. | Methods and systems for measuring and heating dialysate |
IT201700045260A1 (en) * | 2017-04-26 | 2018-10-26 | Argal S R L | UNIT AND METHOD FOR CONTROL OF THE FUNCTIONING OF A PNEUMATIC MEMBRANE PUMP |
EP3410079B1 (en) * | 2017-06-02 | 2021-06-02 | MEAS France | Fluid sensor protection assembly |
US10960381B2 (en) | 2017-06-15 | 2021-03-30 | Medtronic, Inc. | Zirconium phosphate disinfection recharging and conditioning |
WO2018236485A1 (en) * | 2017-06-22 | 2018-12-27 | Cryterion Medical, Inc. | Fluid injection line contamination inhibitor for intravascular catheter system |
US10774297B2 (en) | 2017-08-03 | 2020-09-15 | Repligen Corporation | Method of actuation of an alternating tangential flow diaphragm pump |
KR101943968B1 (en) * | 2017-09-25 | 2019-01-30 | (주)아모레퍼시픽 | Apparatus for manufacturing hydrogel pack for skin care and contorl method thereof |
AU2018345627A1 (en) * | 2017-10-03 | 2020-04-23 | Baxter Healthcare Sa | Modular medical fluid management assemblies and associated machines and methods |
US10722635B2 (en) | 2017-10-03 | 2020-07-28 | Baxter International Inc. | Modular medical fluid management assemblies and associated machines and methods |
US10729839B2 (en) | 2017-10-03 | 2020-08-04 | Baxter International Inc. | Modular medical fluid management assemblies, machines and methods |
GB201717652D0 (en) | 2017-10-26 | 2017-12-13 | Ge Healthcare Bio Sciences Ab | Bioprocess System |
EP3717041A4 (en) * | 2017-11-29 | 2021-06-09 | Serenno Medical | A dual active valve fluid pressure operated positive displacement pump |
US11278654B2 (en) | 2017-12-07 | 2022-03-22 | Medtronic, Inc. | Pneumatic manifold for a dialysis system |
US11033667B2 (en) | 2018-02-02 | 2021-06-15 | Medtronic, Inc. | Sorbent manifold for a dialysis system |
EP3749392A4 (en) * | 2018-02-06 | 2021-11-10 | Becton, Dickinson and Company | Systems, apparatuses and methods for occlusion detection using pump operation measurement |
US20210213199A1 (en) * | 2018-02-06 | 2021-07-15 | Becton, Dickinson And Company | Systems, apparatuses and methods for occlusion detection using pump operation measurement |
US11110215B2 (en) | 2018-02-23 | 2021-09-07 | Medtronic, Inc. | Degasser and vent manifolds for dialysis |
WO2019169081A2 (en) | 2018-02-28 | 2019-09-06 | Nxstage Medical, Inc. | Fluid preparation and treatment devices, methods, and systems |
BR112020019993A2 (en) | 2018-03-30 | 2021-01-26 | Deka Products Limited Partnership | liquid pumping cassettes and associated pressure distribution manifold and related methods |
WO2019204195A1 (en) | 2018-04-17 | 2019-10-24 | Deka Products Limited Partnership | Peritoneal dialysis cassette with pneumatic pump |
US10732083B2 (en) | 2018-05-07 | 2020-08-04 | Fremon Scientific, Inc. | Thawing biological substances |
PL3569274T3 (en) * | 2018-05-14 | 2022-11-07 | Gambro Lundia Ab | Fluid temperature control device for an extracorporeal blood treatment apparatus and extracorporeal blood treatment apparatus |
JP6637107B2 (en) * | 2018-05-16 | 2020-01-29 | 日機装株式会社 | Pressure detector |
JP6637108B2 (en) | 2018-05-16 | 2020-01-29 | 日機装株式会社 | Pressure detector |
JP6639559B2 (en) | 2018-05-16 | 2020-02-05 | 日機装株式会社 | Pressure detector |
JP6694475B2 (en) | 2018-06-22 | 2020-05-13 | 日機装株式会社 | Medical device manufacturing method and manufacturing apparatus |
JP6564914B1 (en) * | 2018-06-22 | 2019-08-21 | 日機装株式会社 | Medical device and manufacturing method thereof |
US11213616B2 (en) | 2018-08-24 | 2022-01-04 | Medtronic, Inc. | Recharge solution for zirconium phosphate |
EP3637218A1 (en) * | 2018-10-10 | 2020-04-15 | Gambro Lundia AB | Fluid warming device for an extracorporeal blood treatment apparatus and method for detecting a fluid temperature at an outlet of a fluid warming device for an extracorporeal blood treatment apparatus |
US11806457B2 (en) | 2018-11-16 | 2023-11-07 | Mozarc Medical Us Llc | Peritoneal dialysis adequacy meaurements |
US11806456B2 (en) | 2018-12-10 | 2023-11-07 | Mozarc Medical Us Llc | Precision peritoneal dialysis therapy based on dialysis adequacy measurements |
JP2022524774A (en) | 2019-03-08 | 2022-05-10 | サマコア, インコーポレイテッド | Positive displacement shuttle pump heart and VAD |
MX2021011442A (en) | 2019-03-19 | 2021-10-13 | Deka Products Lp | Medical treatment systems, methods, and apparatuses using a plurality of fluid lines. |
EP3952955A4 (en) * | 2019-04-09 | 2022-12-07 | NxStage Medical, Inc. | Disposable medical flow-regulating device and system |
US11839708B2 (en) | 2019-10-19 | 2023-12-12 | SummaCor, Inc. | Linear cardiac assist pulsatile pump |
CN110939559B (en) * | 2019-11-08 | 2021-09-28 | 陕西航天动力高科技股份有限公司 | Diaphragm pump buffer system |
EP4058088A1 (en) | 2019-11-12 | 2022-09-21 | Fresenius Medical Care Deutschland GmbH | Blood treatment systems |
CA3160853A1 (en) | 2019-11-12 | 2021-05-20 | Fresenius Medical Care Deutschland Gmbh | Blood treatment systems |
EP4058093A1 (en) | 2019-11-12 | 2022-09-21 | Fresenius Medical Care Deutschland GmbH | Blood treatment systems |
CN114728116A (en) | 2019-11-12 | 2022-07-08 | 费森尤斯医疗护理德国有限责任公司 | Blood treatment system |
JP7033578B2 (en) * | 2019-12-24 | 2022-03-10 | 日機装株式会社 | Pressure detector |
US20210197142A1 (en) * | 2019-12-31 | 2021-07-01 | Pall Corporation | Buffer management system with manifold for bioprocessing system |
USD979071S1 (en) * | 2020-01-24 | 2023-02-21 | Hubiomed Inc. | Hemostasis valve |
DE102020105008A1 (en) * | 2020-02-26 | 2021-08-26 | Fresenius Medical Care Deutschland Gmbh | Medical diaphragm pump and diaphragm pump system |
US20210340486A1 (en) | 2020-05-01 | 2021-11-04 | Deka Products Limited Partnership | System and Method for Centralized Fluid Management and Culture Control |
CN116964457A (en) * | 2020-12-24 | 2023-10-27 | 英维沃斯珂瑞股份有限公司 | Chemical treatment system and apparatus |
WO2022178324A1 (en) * | 2021-02-22 | 2022-08-25 | SummaCor, Inc. | Linear cardiac assist pulsatile pump |
US11547846B2 (en) * | 2021-02-23 | 2023-01-10 | Ventriflo, Inc. | Pump-valving assembly for a pulsatile fluid pump |
IT202100020096A1 (en) | 2021-07-28 | 2021-10-28 | Dadone Silvio | SYSTEM FOR DRIVING A CONTINUOUS FLUID BY MEANS OF TWO SYNCHRONOUS CONTAINERS DISPENSING ALTERNATIVELY AND DRIVE ASSEMBLY OF SUCH A SYSTEM FOR DRIVING A FLUID |
US11850344B2 (en) | 2021-08-11 | 2023-12-26 | Mozarc Medical Us Llc | Gas bubble sensor |
US11965763B2 (en) | 2021-11-12 | 2024-04-23 | Mozarc Medical Us Llc | Determining fluid flow across rotary pump |
US11944733B2 (en) | 2021-11-18 | 2024-04-02 | Mozarc Medical Us Llc | Sodium and bicarbonate control |
WO2024036195A1 (en) * | 2022-08-09 | 2024-02-15 | Massachusetts Institute Of Technology | Smooth flow control systems for embedded micropumps on microfluidic cell culture devices |
Family Cites Families (542)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US356997A (en) * | 1887-02-01 | Simeon gil | ||
US1693526A (en) | 1927-06-15 | 1928-11-27 | Charles S Owens | Hinge |
US2203859A (en) * | 1936-05-28 | 1940-06-11 | Brendlin Adolf | High pressure membrane |
US2339876A (en) | 1941-01-13 | 1944-01-25 | Pesco Products Co | Accumulator |
US2313551A (en) | 1941-09-23 | 1943-03-09 | Eastman Kodak Co | Metering pump |
US2529028A (en) * | 1947-07-31 | 1950-11-07 | Landon Standard Pools | Chemical feeder |
US2703055A (en) | 1950-07-21 | 1955-03-01 | Shell Dev | Diaphragm-type mud pump |
US2741099A (en) | 1953-02-11 | 1956-04-10 | Brewer Titchener Corp | Apparatus for indicating and controlling the temperature of products within predetermined limits |
US2843050A (en) | 1954-02-15 | 1958-07-15 | Lyndus E Harper | Diaphragm sludge or chemical pump |
US2816514A (en) | 1954-09-17 | 1957-12-17 | Designers For Industry Inc | Vibratory pump |
US3080820A (en) | 1958-12-19 | 1963-03-12 | Scott & Williams Inc | Pumping system |
US3016563A (en) | 1959-03-04 | 1962-01-16 | Jong George Edward De | Combined hinge and catch |
US3083943A (en) | 1959-07-06 | 1963-04-02 | Anbrey P Stewart Jr | Diaphragm-type valve |
US3048121A (en) | 1960-04-14 | 1962-08-07 | John M Sheesley | Hydraulic actuated pump |
US3111125A (en) | 1961-11-06 | 1963-11-19 | Rudolf R Schulte | Drainage device |
US3200648A (en) | 1963-02-04 | 1965-08-17 | William H Waggaman | Method and apparatus for comparing smoking properties of various cigarettes |
US3508656A (en) | 1968-04-10 | 1970-04-28 | Milton Roy Co | Portable dialysate supply system |
US3539081A (en) | 1968-07-05 | 1970-11-10 | Jet Spray Cooler Inc | Valve for beverage dispensers |
US3568214A (en) | 1968-07-24 | 1971-03-09 | Univ Utah | Artificial heart system and method of pumping blood by electromagnetically pulsed fluid |
GB1311901A (en) * | 1970-04-15 | 1973-03-28 | Bertil Nystroem Ernst Holger | Membrane pump |
US3656873A (en) | 1970-11-06 | 1972-04-18 | Peter Schiff | Pulsatile by-pass blood pump |
US3759483A (en) | 1971-05-14 | 1973-09-18 | T Baxter | Fluid actuated control valve |
US3814548A (en) | 1971-08-05 | 1974-06-04 | Rupp Co Warren | Diaphragm pump apparatus |
USRE27849E (en) | 1971-11-30 | 1973-12-25 | Dynamic action valveless artifjcial heart utilizing dual fluid oscillator | |
US3827561A (en) | 1972-09-20 | 1974-08-06 | Milton Roy Co | Deaerator for dialysis system |
US3882861A (en) | 1973-09-24 | 1975-05-13 | Vital Assists | Auxiliary control for a blood pump |
US3936729A (en) * | 1974-02-28 | 1976-02-03 | Petrolite Corporation | Conductivity measurement probe |
US3951147A (en) | 1975-04-07 | 1976-04-20 | Metal Bellows Company | Implantable infusate pump |
FR2326235A1 (en) * | 1975-10-01 | 1977-04-29 | Renault | VARIABLE FLOW ELASTIC NOZZLE |
AT344309B (en) | 1975-11-27 | 1978-07-10 | Felix Dr Med Unger | ARTIFICIAL CHAMBER OF HEART |
CA1119971A (en) | 1976-09-07 | 1982-03-16 | James T. Hutchisson | Hemodialysis system with modular dialysate manifold assembly |
US4133312A (en) | 1976-10-13 | 1979-01-09 | Cordis Dow Corp. | Connector for attachment of blood tubing to external arteriovenous shunts and fistulas |
US4155852A (en) | 1976-11-19 | 1979-05-22 | Halbert Fischel | Low leakage current medical instrument |
US4096859A (en) | 1977-04-04 | 1978-06-27 | Agarwal Mahesh C | Apparatus for peritoneal dialysis |
US4161264A (en) * | 1977-06-17 | 1979-07-17 | Johnson Bryan E | Fluid metering and mixing device having inlet and outlet valves |
IT1117080B (en) | 1977-09-21 | 1986-02-10 | Bosio Roberto | PUMP SUITABLE TO CREATE AN ARTIFICIAL BLOOD CIRCULATION |
FR2405610A1 (en) * | 1977-10-07 | 1979-05-04 | Leboeuf Lola | ELECTRIC HEATING PLATE DEVICE FOR BLOOD TRANSFUSION DEVICE |
US4222127A (en) | 1978-06-02 | 1980-09-16 | Donachy And Pierce | Blood pump and method of pumping blood |
DE2838414C2 (en) | 1978-09-02 | 1984-10-31 | Fresenius AG, 6380 Bad Homburg | Device for hemodialysis and for withdrawing ultrafiltrate |
DE2843756B2 (en) | 1978-10-06 | 1981-07-09 | Hense GmbH & Co, 4930 Detmold | Device for generating an aerosol |
US4266814A (en) | 1979-03-23 | 1981-05-12 | Vfp Corporation | Plastic tube adapter |
US4362156A (en) | 1979-04-18 | 1982-12-07 | Riverain Corporation | Intravenous infusion assembly |
US4305702A (en) * | 1979-09-17 | 1981-12-15 | Hartley E Dale | Pump with expandable chamber |
US4282099A (en) | 1979-12-10 | 1981-08-04 | Jones John L | Integral partitioned hemodialysis unit |
US4490254A (en) | 1980-02-25 | 1984-12-25 | Bentley Laboratories, Inc. | Blood filter |
IT1127433B (en) * | 1980-04-08 | 1986-05-21 | Gd Spa | CIGARETTE PACKAGING MACHINE |
FR2487679B1 (en) | 1980-08-01 | 1985-07-12 | Hospal Sodip | ARTIFICIAL KIDNEY - REGULATION OF THE PRESSURE OF THE DIALYSIS LIQUID |
US4439188A (en) | 1980-09-15 | 1984-03-27 | Baxter Travenol Laboratories, Inc. | Tube connector |
US5033513A (en) | 1980-10-29 | 1991-07-23 | Proprietary Technology, Inc. | Swivelable quick connector assembly |
US5782508A (en) | 1980-10-29 | 1998-07-21 | Proprietary Technologies, Inc. | Swivelable quick connector assembly |
US4398908A (en) | 1980-11-28 | 1983-08-16 | Siposs George G | Insulin delivery system |
US4322054A (en) | 1980-12-29 | 1982-03-30 | Red Valve Company, Inc. | Pinch valve |
US4369781A (en) | 1981-02-11 | 1983-01-25 | Sherwood Medical Industries Inc. | Luer connector |
US4731072A (en) | 1981-05-11 | 1988-03-15 | Mcneilab, Inc. | Apparatus for heating or cooling fluids |
US4574876A (en) * | 1981-05-11 | 1986-03-11 | Extracorporeal Medical Specialties, Inc. | Container with tapered walls for heating or cooling fluids |
FR2507481B1 (en) | 1981-06-16 | 1985-06-14 | Hospal Sodip | ARTIFICIAL KIDNEY WITH INTEGRATED CIRCUITS |
IL64001A0 (en) | 1981-10-06 | 1982-01-31 | Elmar Medical Systems Ltd | Blood treatment system |
DE3139925A1 (en) * | 1981-10-08 | 1983-07-14 | Hewlett-Packard GmbH, 7030 Böblingen | HIGH PRESSURE DOSING PUMP |
US4517081A (en) | 1981-11-17 | 1985-05-14 | Renal Systems, Inc. | Dialyzer reuse machine |
US4411783A (en) | 1981-12-23 | 1983-10-25 | Shiley Incorporated | Arterial blood filter with improved gas venting |
US4441357A (en) | 1982-03-04 | 1984-04-10 | Meadox Instruments, Inc. | Pressure monitoring and leak detection method and apparatus |
JPS58169462A (en) | 1982-03-30 | 1983-10-05 | アイシン精機株式会社 | Artificial heart drive apparatus |
US4479762A (en) | 1982-12-28 | 1984-10-30 | Baxter Travenol Laboratories, Inc. | Prepackaged fluid processing module having pump and valve elements operable in response to applied pressures |
WO1984002473A1 (en) | 1982-12-28 | 1984-07-05 | Baxter Travenol Lab | Prepackaged fluid processing module having pump and valve elements operable in response to applied pressures |
US4479760A (en) | 1982-12-28 | 1984-10-30 | Baxter Travenol Laboratories, Inc. | Actuator apparatus for a prepackaged fluid processing module having pump and valve elements operable in response to applied pressures |
US4479761A (en) | 1982-12-28 | 1984-10-30 | Baxter Travenol Laboratories, Inc. | Actuator apparatus for a prepackaged fluid processing module having pump and valve elements operable in response to externally applied pressures |
US4492258A (en) | 1983-02-18 | 1985-01-08 | Whitman Medical Corporation | Sterile urine specimen collection |
US4623334A (en) | 1983-03-07 | 1986-11-18 | Vanderbilt University | Intravenous drug infusion apparatus |
US4501405A (en) | 1983-06-21 | 1985-02-26 | Bunnell Life Systems, Inc. | Frictionless valve/pump |
JPS6030489A (en) | 1983-07-30 | 1985-02-16 | Iwaki:Kk | Diaphragm of pump |
DE3328744A1 (en) | 1983-08-09 | 1985-02-28 | Fresenius AG, 6380 Bad Homburg | Haemodialysis device |
JPS6077782U (en) * | 1983-11-01 | 1985-05-30 | 山田油機製造株式会社 | diaphragm |
US4583920A (en) * | 1983-12-28 | 1986-04-22 | M&T Chemicals Inc. | Positive displacement diaphragm pumps employing displacer valves |
CA1233363A (en) | 1984-06-01 | 1988-03-01 | Robert E. Fischell | Single valve diaphragm pump with decreased sensitivity to ambient conditions |
US4664891A (en) | 1984-07-23 | 1987-05-12 | Renal Systems, Inc. | Dialysis solution preparation from prepackaged dry chemicals |
US4585442A (en) | 1984-07-26 | 1986-04-29 | Ivy Medical, Inc. | Miniature intravenous infusion rate controller |
US4680445A (en) * | 1984-09-06 | 1987-07-14 | Genshiro Ogawa | Electronically-controlled heating device for infusion liquids |
US4718022A (en) | 1985-02-21 | 1988-01-05 | Cochran Michael J | Dialysis machine which anticipates concentration changes |
JPS61167492U (en) * | 1985-04-05 | 1986-10-17 | ||
US4695385A (en) | 1985-04-29 | 1987-09-22 | Colorado Medical, Inc. | Dialyzer reuse system |
US4666598A (en) | 1985-06-25 | 1987-05-19 | Cobe Laboratories, Inc. | Apparatus for use with fluid flow transfer device |
US5575310A (en) | 1986-03-04 | 1996-11-19 | Deka Products Limited Partnership | Flow control system with volume-measuring system using a resonatable mass |
US4976162A (en) | 1987-09-03 | 1990-12-11 | Kamen Dean L | Enhanced pressure measurement flow control system |
US5178182A (en) | 1986-03-04 | 1993-01-12 | Deka Products Limited Partnership | Valve system with removable fluid interface |
US4826482A (en) | 1986-03-04 | 1989-05-02 | Kamen Dean L | Enhanced pressure measurement flow control system |
US4778451A (en) * | 1986-03-04 | 1988-10-18 | Kamen Dean L | Flow control system using boyle's law |
US5088515A (en) * | 1989-05-01 | 1992-02-18 | Kamen Dean L | Valve system with removable fluid interface |
US4828543A (en) | 1986-04-03 | 1989-05-09 | Weiss Paul I | Extracorporeal circulation apparatus |
US5160325A (en) | 1986-10-06 | 1992-11-03 | C. R. Bard, Inc. | Catheter with novel lumens shapes |
US4784495A (en) | 1987-02-06 | 1988-11-15 | Gambro Ab | System for preparing a fluid intended for a medical procedure by mixing at least one concentrate in powder form with water |
EP0288145A1 (en) | 1987-03-17 | 1988-10-26 | Kenneth Arthur Logan | Disposable pump element for dialysis pump |
US4927411A (en) | 1987-05-01 | 1990-05-22 | Abbott Laboratories | Drive mechanism for disposable fluid infusion pumping cassette |
NL8701233A (en) * | 1987-05-22 | 1988-12-16 | Medistad Holland | BLOOD HEATER. |
IL83259A (en) | 1987-07-20 | 1992-05-25 | D F Lab Ltd | Disposable cell and diaphragm pump for use of same |
JP2513243B2 (en) | 1987-07-24 | 1996-07-03 | 東洋紡績株式会社 | Blood pump |
US4822343A (en) | 1987-09-21 | 1989-04-18 | Louise Beiser | Blood collection device with ejectable tips |
US4781535A (en) * | 1987-11-13 | 1988-11-01 | Pulsafeeder, Inc. | Apparatus and method for sensing diaphragm failures in reciprocating pumps |
US4833329A (en) | 1987-11-20 | 1989-05-23 | Mallinckrodt, Inc. | System for generating and containerizing radioisotopes |
EP0544653B1 (en) | 1988-01-25 | 1996-06-05 | Baxter International Inc. | Injection site |
SE465404B (en) | 1988-03-03 | 1991-09-09 | Gambro Ab | DIALYSIS SYSTEM |
US4863461A (en) * | 1988-03-21 | 1989-09-05 | Symbion, Inc. | Artificial ventricle |
DE3882519T2 (en) | 1988-04-13 | 1993-11-11 | Med Tech Inc | Method for controlling water withdrawal by ultrafiltration and control device for controlling water withdrawal by ultrafiltration during hemodialysis. |
US4950235A (en) | 1988-05-10 | 1990-08-21 | Pacesetter Infusion, Ltd. | Container-side occlusion detection system for a medication infusion system |
US4976729A (en) * | 1988-08-15 | 1990-12-11 | University Of Utah Research Foundation | Elliptical artificial heart |
US5110447A (en) | 1988-09-12 | 1992-05-05 | Kasten, Eadie Technology Ltd. | Process and apparatus for partial upgrading of a heavy oil feedstock |
DE3837498A1 (en) | 1988-11-04 | 1990-05-17 | Fresenius Ag | METHOD AND DEVICE FOR ULTRAFILTRATION IN HAEMODIALYSIS |
US5074838A (en) | 1988-11-07 | 1991-12-24 | Kr Phi Yer Karl K K | Extracorporal thermo-therapy device and method for curing diseases using penetrants |
JP2975105B2 (en) * | 1988-12-29 | 1999-11-10 | アン・ルイス・チヤング | Diaphragm pump |
US5061241A (en) | 1989-01-19 | 1991-10-29 | Stephens Jr Harry W | Rapid infusion device |
DE3907735A1 (en) * | 1989-03-10 | 1990-09-20 | Bran & Luebbe | DIAPHRAGM PUMP WITH FREE-SWINGING METAL DIAPHRAGM |
IE72466B1 (en) | 1989-03-17 | 1997-04-09 | Baxter Int | Blunt-ended cannula device |
US5167837A (en) * | 1989-03-28 | 1992-12-01 | Fas-Technologies, Inc. | Filtering and dispensing system with independently activated pumps in series |
US5000664A (en) | 1989-06-07 | 1991-03-19 | Abbott Laboratories | Apparatus and method to test for valve leakage in a pump assembly |
US5702371A (en) * | 1989-07-24 | 1997-12-30 | Venetec International, Inc. | Tube fitting anchoring system |
US5242384A (en) | 1989-11-13 | 1993-09-07 | Davol, Inc. | Blood pumping and processing system |
DE3938662A1 (en) | 1989-11-21 | 1991-07-18 | Fresenius Ag | METHOD FOR IN VIVO DETERMINING PARAMETERS OF HAEMODIALYSIS |
US5062774A (en) | 1989-12-01 | 1991-11-05 | Abbott Laboratories | Solution pumping system including disposable pump cassette |
US5125069A (en) * | 1989-12-22 | 1992-06-23 | Netherlands Health Sciences | Blood warmer |
US5110477A (en) | 1990-02-13 | 1992-05-05 | Howard David B | Dialyzer clearance check system |
US5278072A (en) | 1990-04-26 | 1994-01-11 | Minnesota Mining And Manufacturing Company | Calibration system and housing |
SE9002051L (en) | 1990-06-07 | 1992-01-07 | Astra Tech Ab | VALVE DEVICE AND SUPPLY PUMP |
CN1057786A (en) | 1990-07-06 | 1992-01-15 | 张任谦 | Membrane pump |
US5351686A (en) | 1990-10-06 | 1994-10-04 | In-Line Diagnostics Corporation | Disposable extracorporeal conduit for blood constituent monitoring |
US5105981A (en) | 1990-11-19 | 1992-04-21 | Thomas Gehman | Selectively shakeable freestanding particulate matter reservoir |
US5098262A (en) | 1990-12-28 | 1992-03-24 | Abbott Laboratories | Solution pumping system with compressible pump cassette |
US5308320A (en) | 1990-12-28 | 1994-05-03 | University Of Pittsburgh Of The Commonwealth System Of Higher Education | Portable and modular cardiopulmonary bypass apparatus and associated aortic balloon catheter and associated method |
DK8391A (en) | 1991-01-18 | 1992-07-19 | Uno Plast As | Suction pump for use in extraction of body fluids from the body cavity |
US5116316A (en) | 1991-02-25 | 1992-05-26 | Baxter International Inc. | Automatic in-line reconstitution system |
US5381510A (en) * | 1991-03-15 | 1995-01-10 | In-Touch Products Co. | In-line fluid heating apparatus with gradation of heat energy from inlet to outlet |
US5245693A (en) | 1991-03-15 | 1993-09-14 | In-Touch Products Co. | Parenteral fluid warmer apparatus and disposable cassette utilizing thin, flexible heat-exchange membrane |
US5247434A (en) | 1991-04-19 | 1993-09-21 | Althin Medical, Inc. | Method and apparatus for kidney dialysis |
US5326476A (en) | 1991-04-19 | 1994-07-05 | Althin Medical, Inc. | Method and apparatus for kidney dialysis using machine with programmable memory |
US5486286A (en) | 1991-04-19 | 1996-01-23 | Althin Medical, Inc. | Apparatus for performing a self-test of kidney dialysis membrane |
US5192269A (en) | 1991-07-24 | 1993-03-09 | Abbott Laboratories | Multi-valve manifold for drug infusion systems |
JPH0531184A (en) | 1991-08-02 | 1993-02-09 | Asahi Medical Co Ltd | Blood detector |
US5336165A (en) | 1991-08-21 | 1994-08-09 | Twardowski Zbylut J | Artificial kidney for frequent (daily) Hemodialysis |
US5902476A (en) | 1991-08-21 | 1999-05-11 | Twardowski; Zbylut J. | Artificial kidney for frequent (daily) hemodialysis |
US5290239A (en) | 1991-09-26 | 1994-03-01 | Baxter International, Inc. | Intravenous tube safety apparatus |
US5755683A (en) | 1995-06-07 | 1998-05-26 | Deka Products Limited Partnership | Stopcock valve |
US5275724A (en) | 1991-12-10 | 1994-01-04 | Millipore Corporation | Connector apparatus and system |
WO1993012825A1 (en) | 1991-12-20 | 1993-07-08 | Abbott Laboratories | Automated drug infusion system with autopriming |
IT1250558B (en) | 1991-12-30 | 1995-04-20 | Hospal Dasco Spa | DIALYSIS MACHINE WITH SAFETY CONTROL AND RELATED SAFETY CONTROL METHOD. |
US5267956A (en) | 1992-02-05 | 1993-12-07 | Alcon Surgical, Inc. | Surgical cassette |
US5277820A (en) | 1992-02-06 | 1994-01-11 | Hemocleanse, Inc. | Device and method for extracorporeal blood treatment |
US5431634A (en) | 1992-03-06 | 1995-07-11 | Baxter International Inc. | Ambulatory pump |
US5423738A (en) * | 1992-03-13 | 1995-06-13 | Robinson; Thomas C. | Blood pumping and processing system |
IE930532A1 (en) | 1993-07-19 | 1995-01-25 | Elan Med Tech | Liquid material dispenser and valve |
US5411472A (en) | 1992-07-30 | 1995-05-02 | Galen Medical, Inc. | Low trauma blood recovery system |
US5476368A (en) * | 1992-08-20 | 1995-12-19 | Ryder International Corporation | Sterile fluid pump diaphragm construction |
US5476444A (en) | 1992-09-04 | 1995-12-19 | Idt, Inc. | Specialized perfusion protocol for whole-body hyperthermia |
SE505801C2 (en) | 1992-09-25 | 1997-10-13 | Atlas Copco Tools Ab | Cabinets for holding electronic equipment connectable to machines or power tools |
JP3549883B2 (en) | 1992-10-01 | 2004-08-04 | アメリカン ステリライザー カンパニー | Liquid dispensing system and dispensing method based on accumulator |
US5279504A (en) | 1992-11-02 | 1994-01-18 | Williams James F | Multi-diaphragm metering pump |
CA2149246C (en) | 1992-11-12 | 2001-08-28 | Jeffrey B. Grogan | Method and apparatus for kidney dialysis |
DE4336336A1 (en) * | 1992-11-23 | 1994-05-26 | Lang Volker | Cassette infusion system |
DE4239937C2 (en) | 1992-11-27 | 1995-08-24 | Fresenius Ag | Method for determining the functionality of a partial device of a hemodialysis machine and device for carrying out this method |
US5306242A (en) | 1992-12-15 | 1994-04-26 | Abbott Laboratories | Recirculation through plural pump cassettes for a solution compounding apparatus |
GB2273533B (en) * | 1992-12-18 | 1996-09-25 | Minnesota Mining & Mfg | Pumping cassette with integral manifold |
JPH08504916A (en) | 1992-12-18 | 1996-05-28 | アボツト・ラボラトリーズ | Solution pumping system for maximum output while minimizing pumping pressure |
WO1994016226A1 (en) | 1992-12-30 | 1994-07-21 | Abbott Laboratories | Diaphragm for solution pumping system |
JPH06207845A (en) | 1993-01-11 | 1994-07-26 | Sugino Mach Ltd | Method and device for measuring volume of piston combustion chamber |
US5441636A (en) | 1993-02-12 | 1995-08-15 | Cobe Laboratories, Inc. | Integrated blood treatment fluid module |
JPH06237988A (en) * | 1993-02-19 | 1994-08-30 | Aisin Seiki Co Ltd | Artificial heart pump device |
USD350823S (en) | 1993-02-24 | 1994-09-20 | Deka Products Limited Partnership | Rigid portion of disposable parenteral-fluid cassette |
US5324422A (en) * | 1993-03-03 | 1994-06-28 | Baxter International Inc. | User interface for automated peritoneal dialysis systems |
US5474683A (en) | 1993-03-03 | 1995-12-12 | Deka Products Limited Partnership | Peritoneal dialysis systems and methods employing pneumatic pressure and temperature-corrected liquid volume measurements |
US5431626A (en) * | 1993-03-03 | 1995-07-11 | Deka Products Limited Partnership | Liquid pumping mechanisms for peritoneal dialysis systems employing fluid pressure |
WO1994020154A1 (en) * | 1993-03-03 | 1994-09-15 | Deka Products Limited Partnership | Peritoneal dialysis systems and methods employing a liquid distribution and pump cassette with self-contained air isolation and removal |
US5350357A (en) * | 1993-03-03 | 1994-09-27 | Deka Products Limited Partnership | Peritoneal dialysis systems employing a liquid distribution and pumping cassette that emulates gravity flow |
US5438510A (en) | 1993-03-03 | 1995-08-01 | Deka Products Limited Partnership | User interface and monitoring functions for automated peritoneal dialysis systems |
US5413566A (en) | 1993-03-16 | 1995-05-09 | Micropump Corporation | Line clamp |
USD350850S (en) | 1993-04-20 | 1994-09-27 | Paolo Maniglio | Jewelry case |
US5410255A (en) | 1993-05-07 | 1995-04-25 | Perma-Pipe, Inc. | Method and apparatus for detecting and distinguishing leaks using reflectometry and conductivity tests |
US5385540A (en) | 1993-05-26 | 1995-01-31 | Quest Medical, Inc. | Cardioplegia delivery system |
US5645531A (en) | 1993-05-26 | 1997-07-08 | Quest Medical, Inc. | Constant pressure blood mixture delivery system and method |
JP2576760B2 (en) | 1993-06-08 | 1997-01-29 | 日本電気株式会社 | Micro field emission cold cathode and manufacturing method thereof |
US5349896A (en) * | 1993-06-14 | 1994-09-27 | W. L. Gore & Associates, Inc. | Pump diaphragm |
US5398851A (en) | 1993-08-06 | 1995-03-21 | River Medical, Inc. | Liquid delivery device |
US5395316A (en) | 1993-08-11 | 1995-03-07 | Med-Pro Design, Inc. | Triple lumen catheter |
US5441343A (en) * | 1993-09-27 | 1995-08-15 | Topometrix Corporation | Thermal sensing scanning probe microscope and method for measurement of thermal parameters of a specimen |
GB9325591D0 (en) | 1993-12-14 | 1994-02-16 | Somerset Technical Lab Ltd | Leakage detection |
US5420962A (en) | 1993-10-25 | 1995-05-30 | Bakke; Allan P. | Convection blood warming system with disposable flattened tube envelope having vent incorporating a hydrophobic filter |
US5431627A (en) | 1993-11-12 | 1995-07-11 | Abbott Laboratories | Cassette identification system for use with a multi-program drug infusion pump |
US5499909A (en) * | 1993-11-17 | 1996-03-19 | Aisin Seiki Kabushiki Kaisha Of Kariya | Pneumatically driven micro-pump |
US5482440A (en) | 1993-12-22 | 1996-01-09 | Baxter Int | Blood processing systems using a peristaltic pump module with valve and sensing station for operating a peristaltic pump tube cassette |
US5462416A (en) | 1993-12-22 | 1995-10-31 | Baxter International Inc. | Peristaltic pump tube cassette for blood processing systems |
US5480294A (en) | 1993-12-22 | 1996-01-02 | Baxter International Inc. | Peristaltic pump module having jaws for gripping a peristaltic pump tube cassett |
US5460619A (en) | 1994-04-04 | 1995-10-24 | Esrock; Bernard S. | Disposable tubular device and method |
JP3677045B2 (en) | 1994-04-06 | 2005-07-27 | バクスター、インターナショナル、インコーポレイテッド | Apparatus for tidal vibration pulse peritoneal dialysis |
US5441231A (en) | 1994-05-17 | 1995-08-15 | Payne; Barrett M. M. | Valve closing actuator |
DE4421126A1 (en) | 1994-06-16 | 1995-12-21 | Fresenius Ag | Peritoneal dialysis machine |
US5564576A (en) * | 1994-06-13 | 1996-10-15 | Usui Kokusai Sangyo Kaisha Ltd. | Clamp for and method of storing/transporting high-pressure fuel injection pipes |
US5632894A (en) | 1994-06-24 | 1997-05-27 | Gish Biomedical, Inc. | Arterial blood filter with upwardly inclining delivery inlet conduit |
US5541344A (en) | 1994-06-30 | 1996-07-30 | G. D. Searle & Co. | Intermediates useful in a process for the preparation of azanoradamantane benzamides |
FR2723002B1 (en) | 1994-07-26 | 1996-09-06 | Hospal Ind | DEVICE AND METHOD FOR PREPARING A FILTRATION PROCESSING LIQUID |
JPH08108048A (en) | 1994-10-12 | 1996-04-30 | Toray Ind Inc | Reverse osmosis separator and reverse osmosis separating method |
US5581687A (en) * | 1994-11-10 | 1996-12-03 | Baxter International Inc. | Interactive control systems for medical processing devices |
US5593290A (en) * | 1994-12-22 | 1997-01-14 | Eastman Kodak Company | Micro dispensing positive displacement pump |
US5755275A (en) | 1995-01-25 | 1998-05-26 | Delta Temax Inc. | Tubed lamination heat transfer articles and method of manufacture |
US5932110A (en) | 1995-02-13 | 1999-08-03 | Aksys, Ltd. | Dialysate conductivity adjustment in a batch dialysate preparation system |
US6153102A (en) | 1995-02-13 | 2000-11-28 | Aksys, Ltd. | Disinfection of dead-ended lines in medical instruments |
US5788851A (en) | 1995-02-13 | 1998-08-04 | Aksys, Ltd. | User interface and method for control of medical instruments, such as dialysis machines |
US5932103A (en) | 1995-02-13 | 1999-08-03 | Aksys, Ltd. | Withdrawal of priming fluid from extracorporeal circuit of hemodialysis machines or the like |
US5591344A (en) | 1995-02-13 | 1997-01-07 | Aksys, Ltd. | Hot water disinfection of dialysis machines, including the extracorporeal circuit thereof |
SE9500557D0 (en) | 1995-02-15 | 1995-02-15 | Astra Ab | Pump chamber and valve for a pump chamber |
US6044868A (en) | 1995-02-24 | 2000-04-04 | Arlington Industries, Inc. | Watertight fitting for flexible non-metallic conduit |
US5586438A (en) | 1995-03-27 | 1996-12-24 | Organ, Inc. | Portable device for preserving organs by static storage or perfusion |
US5578012A (en) | 1995-04-24 | 1996-11-26 | Deka Products Limited Partnership | Medical fluid pump |
US5651765A (en) | 1995-04-27 | 1997-07-29 | Avecor Cardiovascular Inc. | Blood filter with concentric pleats and method of use |
US5839715A (en) | 1995-05-16 | 1998-11-24 | Alaris Medical Systems, Inc. | Medical adapter having needleless valve and sharpened cannula |
ES2094700B1 (en) | 1995-05-30 | 1997-08-01 | Serv Reg Salud Com Madrid | DEVICE FOR TUBULAR BLOOD PUMPING, WITH ACTIVE VALVES GOVERNED BY VACUUM AND APPLICATION OF THE SAME. |
US6709417B1 (en) | 1995-06-07 | 2004-03-23 | Deka Products Limited Partnership | Valve for intravenous-line flow-control system |
US6139819A (en) | 1995-06-07 | 2000-10-31 | Imarx Pharmaceutical Corp. | Targeted contrast agents for diagnostic and therapeutic use |
US5650071A (en) | 1995-06-07 | 1997-07-22 | Cobe Laboratories, Inc. | Technique for priming and recirculating fluid through a dialysis machine to prepare the machine for use |
US6165154A (en) * | 1995-06-07 | 2000-12-26 | Deka Products Limited Partnership | Cassette for intravenous-line flow-control system |
US5685835A (en) | 1995-06-07 | 1997-11-11 | Cobe Laboratories, Inc. | Technique for using a dialysis machine to disinfect a blood tubing set |
US5795317A (en) | 1995-06-07 | 1998-08-18 | Cobe Laboratories, Inc. | Extracorporeal blood processing methods and apparatus |
US5676644A (en) | 1995-06-07 | 1997-10-14 | Cobe Laboratories, Inc. | Extracorporeal blood processing methods and apparatus |
US5729653A (en) * | 1995-06-07 | 1998-03-17 | Urosurge, Inc. | Fluid warming system |
US5772624A (en) | 1995-07-20 | 1998-06-30 | Medisystems Technology Corporation | Reusable blood lines |
US5776098A (en) | 1995-08-03 | 1998-07-07 | Medela, Incorporated | Diaphragm pump and pump mounted in a carrying case useful in breast pumping |
US5730720A (en) * | 1995-08-18 | 1998-03-24 | Ip Scientific, Inc. | Perfusion hyperthermia treatment system and method |
US5674190A (en) | 1995-08-28 | 1997-10-07 | Organetics, Ltd. | Extracorporeal whole body hyperthermia using alpha-stat regulation of blood pH and pCO2 |
US5938634A (en) | 1995-09-08 | 1999-08-17 | Baxter International Inc. | Peritoneal dialysis system with variable pressure drive |
US5674109A (en) | 1995-09-13 | 1997-10-07 | Ebara Corporation | Apparatus and method for polishing workpiece |
DE19534417A1 (en) | 1995-09-16 | 1997-03-20 | Fresenius Ag | Method for checking at least one filter arranged in the dialysis fluid system of a device for extracorporeal blood treatment |
US6331778B1 (en) * | 1995-09-27 | 2001-12-18 | Leak Location Services, Inc. | Methods for detecting and locating leaks in containment facilities using electrical potential data and electrical resistance tomographic imaging techniques |
JPH0999060A (en) * | 1995-10-04 | 1997-04-15 | Terumo Corp | Pulsatile blood pump |
US5638737A (en) | 1995-11-27 | 1997-06-17 | Quest Medical, Inc. | Spline pumping assembly |
DE19546028C2 (en) | 1995-12-09 | 2000-04-27 | Fresenius Ag | Balancing disposable for balancing liquids for a medical treatment device and a medical treatment device with a system insert for receiving such a balancing disposable |
US5692729A (en) | 1996-02-16 | 1997-12-02 | Vision-Sciences, Inc. | Pressure equalized flow control apparatus and method for endoscope channels |
JPH09287441A (en) | 1996-04-25 | 1997-11-04 | Tenetsukusu:Kk | Control valve of secondary air for disposal of exhaust gas of engine |
US5788858A (en) | 1996-05-03 | 1998-08-04 | Terra Group, Inc. | Mobile water purification unit with modular dechlorination input stage |
US6146354A (en) | 1996-05-24 | 2000-11-14 | Horizon Medical Products | Asymmetrical multi-lumen apheresis catheter with balanced flow rates |
US6783328B2 (en) | 1996-09-30 | 2004-08-31 | Terumo Cardiovascular Systems Corporation | Method and apparatus for controlling fluid pumps |
US6047108A (en) | 1996-10-01 | 2000-04-04 | Baxter International Inc. | Blood warming apparatus |
US5875282A (en) * | 1996-10-21 | 1999-02-23 | Gaymar Industries, Inc. | Medical apparatus for warming patient fluids |
US5952168A (en) | 1996-11-07 | 1999-09-14 | 21St Century Medicine, Inc. | Method for vitrification of biological materials using alkoxylated compounds |
WO1998022165A1 (en) | 1996-11-22 | 1998-05-28 | Therakos, Inc. | Integrated cassette for controlling fluid having an integral filter |
US5882047A (en) | 1996-12-20 | 1999-03-16 | Itt Automotive, Inc. | Quick connector fluid coupling |
JPH10196814A (en) | 1997-01-17 | 1998-07-31 | Aisan Ind Co Ltd | Diaphragm-operated flow control valve |
US6579253B1 (en) * | 1997-02-14 | 2003-06-17 | Nxstage Medical, Inc. | Fluid processing systems and methods using extracorporeal fluid flow panels oriented within a cartridge |
US6638478B1 (en) | 1997-02-14 | 2003-10-28 | Nxstage Medical, Inc. | Synchronized volumetric fluid balancing systems and methods |
US6673314B1 (en) | 1997-02-14 | 2004-01-06 | Nxstage Medical, Inc. | Interactive systems and methods for supporting hemofiltration therapies |
US6852090B2 (en) | 1997-02-14 | 2005-02-08 | Nxstage Medical, Inc. | Fluid processing systems and methods using extracorporeal fluid flow panels oriented within a cartridge |
US6419462B1 (en) | 1997-02-24 | 2002-07-16 | Ebara Corporation | Positive displacement type liquid-delivery apparatus |
JP2001513675A (en) * | 1997-02-27 | 2001-09-04 | ミネソタ マイニング アンド マニュファクチャリング カンパニー | Cassette for measuring blood parameters |
DE19708391C1 (en) | 1997-03-01 | 1998-10-22 | Fresenius Medical Care De Gmbh | Method and device for ultrafiltration in hemodialysis |
US5899873A (en) * | 1997-03-24 | 1999-05-04 | Quest Medical, Inc. | Biological fluid delivery system |
US6660974B2 (en) * | 1997-04-07 | 2003-12-09 | Medical Solutions, Inc. | Warming system and method for heating various items utilized in surgical procedures |
US6768085B2 (en) | 2001-07-02 | 2004-07-27 | Medical Solutions, Inc. | Medical solution warming system and method of heating and maintaining medical solutions at desired temperatures |
JP3580661B2 (en) | 1997-04-08 | 2004-10-27 | 愛三工業株式会社 | Pressure control valve |
DE69839047T2 (en) * | 1997-05-20 | 2009-01-15 | Zymequest, Inc., Beverly | Fluid monitoring system |
US6261262B1 (en) | 1997-06-12 | 2001-07-17 | Abbott Laboratories | Pump with anti-free flow feature |
US5965821A (en) | 1997-07-03 | 1999-10-12 | Mks Instruments, Inc. | Pressure sensor |
US6070761A (en) | 1997-08-22 | 2000-06-06 | Deka Products Limited Partnership | Vial loading method and apparatus for intelligent admixture and delivery of intravenous drugs |
EP1003579B1 (en) * | 1997-08-22 | 2005-01-12 | Deka Products Limited Partnership | System and cassette for mixing and delivering intravenous drugs |
US5972216A (en) | 1997-10-24 | 1999-10-26 | Terra Group, Inc. | Portable multi-functional modular water filtration unit |
US6159192A (en) | 1997-12-04 | 2000-12-12 | Fowles; Thomas A. | Sliding reconstitution device with seal |
US6109881A (en) | 1998-01-09 | 2000-08-29 | Snodgrass; Ocie T. | Gas driven pump for the dispensing and filtering of process fluid |
JPH11210633A (en) * | 1998-01-30 | 1999-08-03 | Matsushita Electric Works Ltd | Suction device |
US6142164A (en) | 1998-03-09 | 2000-11-07 | Ultra Clean Technology Systems & Service, Inc. | Method and apparatus for removing leaking gas in an integrated gas panel system |
US6325159B1 (en) * | 1998-03-27 | 2001-12-04 | Hydril Company | Offshore drilling system |
DE19814695C2 (en) | 1998-04-01 | 2001-09-13 | Fresenius Medical Care De Gmbh | Cassette for conveying liquids, in particular dialysis liquids, dialysis machine and method for conveying, balancing, dosing and heating a medical fluid |
FR2779964B1 (en) | 1998-06-17 | 2000-09-15 | Internova International Innova | DIALYSIS MACHINE, PARTICULARLY FOR HOME USE |
US6343614B1 (en) * | 1998-07-01 | 2002-02-05 | Deka Products Limited Partnership | System for measuring change in fluid flow rate within a line |
US6041801A (en) | 1998-07-01 | 2000-03-28 | Deka Products Limited Partnership | System and method for measuring when fluid has stopped flowing within a line |
US6175688B1 (en) | 1998-07-10 | 2001-01-16 | Belmont Instrument Corporation | Wearable intravenous fluid heater |
US6228255B1 (en) | 1998-07-24 | 2001-05-08 | Dialysis Systems, Inc. | Portable water treatment facility |
GB9818254D0 (en) * | 1998-08-21 | 1998-10-14 | Blueground Res Ltd | Methods of and apparatus for tyre pressure measurement |
SE513522C2 (en) | 1998-09-10 | 2000-09-25 | Gambro Ab | Device for monitoring a fluid tube |
JP2000107283A (en) | 1998-10-07 | 2000-04-18 | Nissho Corp | Dialysis apparatus and washing priming method |
JP4638986B2 (en) | 1998-10-16 | 2011-02-23 | テルモ メディカル コーポレイション | Blood processing equipment |
US6223130B1 (en) | 1998-11-16 | 2001-04-24 | Deka Products Limited Partnership | Apparatus and method for detection of a leak in a membrane of a fluid flow control system |
JP3997630B2 (en) | 1998-12-03 | 2007-10-24 | ニプロ株式会社 | Medical pumping cassette and medical pumping device |
CN2374187Y (en) | 1999-01-29 | 2000-04-19 | 暨南大学 | Blood dialyser |
DE19906317C1 (en) | 1999-02-16 | 2000-10-19 | Knf Flodos Ag Sursee | Diaphragm pump |
EP1159019B1 (en) | 1999-03-09 | 2002-11-06 | Augustine Medical, Inc. | Iv fluid warming system with detection of presence and alignment of cassette |
SE9901165D0 (en) | 1999-03-30 | 1999-03-30 | Gambro Lundia Ab | Method, apparatus and components of dialysis systems |
US6579496B1 (en) | 1999-05-25 | 2003-06-17 | Viacirq, Inc. | Apparatus for implementing hyperthermia |
US6321597B1 (en) | 1999-05-28 | 2001-11-27 | Deka Products Limited Partnership | System and method for measuring volume of liquid in a chamber |
DE19925297C1 (en) | 1999-06-02 | 2000-07-13 | Braun Melsungen Ag | Dialysis machine filter cartridge holder uses radial tensioner elements to seal onto cartridge connections when positioned using keyhole holder connections taking cartridge connection grooves. |
US6336911B1 (en) * | 1999-06-16 | 2002-01-08 | First Circle Medical, Inc. | Thermal sensor for hyperthermia system |
US6406452B1 (en) * | 1999-06-16 | 2002-06-18 | First Circle Medical, Inc. | Bladder catheter for hyperthermia system |
DE19928407C1 (en) | 1999-06-22 | 2000-10-26 | Fresenius Medical Care De Gmbh | Determining dialyser performance in dialysis device involves determining clearance and dialysance based on values for given blood/dialysis liquid flow rates and/or ultrafiltration rate |
JP2001009025A (en) | 1999-06-30 | 2001-01-16 | Shibuya Kogyo Co Ltd | Personal dialysis apparatus |
US6176904B1 (en) | 1999-07-02 | 2001-01-23 | Brij M. Gupta | Blood filter |
US6416293B1 (en) | 1999-07-20 | 2002-07-09 | Deka Products Limited Partnership | Pumping cartridge including a bypass valve and method for directing flow in a pumping cartridge |
US6877713B1 (en) | 1999-07-20 | 2005-04-12 | Deka Products Limited Partnership | Tube occluder and method for occluding collapsible tubes |
US6604908B1 (en) * | 1999-07-20 | 2003-08-12 | Deka Products Limited Partnership | Methods and systems for pulsed delivery of fluids from a pump |
US6302653B1 (en) | 1999-07-20 | 2001-10-16 | Deka Products Limited Partnership | Methods and systems for detecting the presence of a gas in a pump and preventing a gas from being pumped from a pump |
US6382923B1 (en) | 1999-07-20 | 2002-05-07 | Deka Products Ltd. Partnership | Pump chamber having at least one spacer for inhibiting the pumping of a gas |
US6905479B1 (en) | 1999-07-20 | 2005-06-14 | Deka Products Limited Partnership | Pumping cartridge having an integrated filter and method for filtering a fluid with the cartridge |
US6171261B1 (en) | 1999-08-06 | 2001-01-09 | Becton Dickinson And Company | Specimen collection device and method of delivering fluid specimens to test tubes |
US6949079B1 (en) | 1999-09-03 | 2005-09-27 | Baxter International Inc. | Programmable, fluid pressure actuated blood processing systems and methods |
US6284142B1 (en) | 1999-09-03 | 2001-09-04 | Baxter International Inc. | Sensing systems and methods for differentiating between different cellular blood species during extracorporeal blood separation or processing |
US6481980B1 (en) | 1999-09-03 | 2002-11-19 | Baxter International Inc. | Fluid flow cassette with pressure actuated pump and valve stations |
US6261065B1 (en) | 1999-09-03 | 2001-07-17 | Baxter International Inc. | System and methods for control of pumps employing electrical field sensing |
US7041076B1 (en) | 1999-09-03 | 2006-05-09 | Baxter International Inc. | Blood separation systems and methods using a multiple function pump station to perform different on-line processing tasks |
US6723062B1 (en) | 1999-09-03 | 2004-04-20 | Baxter International Inc. | Fluid pressure actuated blood pumping systems and methods with continuous inflow and pulsatile outflow conditions |
US20060178612A9 (en) | 1999-09-03 | 2006-08-10 | Baxter International Inc. | Blood processing systems with fluid flow cassette with a pressure actuated pump chamber and in-line air trap |
JP3806859B2 (en) * | 1999-09-24 | 2006-08-09 | 応研精工株式会社 | Diaphragm pump |
US6464666B1 (en) | 1999-10-08 | 2002-10-15 | Augustine Medical, Inc. | Intravenous fluid warming cassette with stiffening member and integral handle |
US6295918B1 (en) | 1999-10-15 | 2001-10-02 | John M. Simmons | Suspended diaphragm |
JP2001123958A (en) * | 1999-10-27 | 2001-05-08 | Mikuni Adec Corp | Diaphragm type fuel pump |
US6406426B1 (en) | 1999-11-03 | 2002-06-18 | Criticare Systems | Medical monitoring and alert system for use with therapeutic devices |
US7780619B2 (en) | 1999-11-29 | 2010-08-24 | Nxstage Medical, Inc. | Blood treatment apparatus |
US6423053B1 (en) | 2000-01-12 | 2002-07-23 | Han-Pin Lee | Releasable tube assembly |
US6347633B1 (en) * | 2000-01-14 | 2002-02-19 | First Circle Medical, Inc. | Treatment of hepatitis C using hyperthermia |
US6139534A (en) | 2000-01-24 | 2000-10-31 | Bracco Diagnostics, Inc. | Vial access adapter |
US6497676B1 (en) | 2000-02-10 | 2002-12-24 | Baxter International | Method and apparatus for monitoring and controlling peritoneal dialysis therapy |
WO2001060428A1 (en) | 2000-02-16 | 2001-08-23 | Teijin Limited | Dialyzing fluid preparing device and powdery dialyzing fluid preparing chemical |
CA2724266C (en) * | 2000-02-29 | 2012-12-04 | Gen-Probe Incorporated | Fluid dispense and liquid surface verification system and method |
US7168334B1 (en) | 2000-05-30 | 2007-01-30 | Gambro Lundia Ab | Arrangement for measuring a property of a fluid present in a tube |
US6752599B2 (en) | 2000-06-09 | 2004-06-22 | Alink M, Inc. | Apparatus for photoresist delivery |
US6595944B2 (en) * | 2000-06-17 | 2003-07-22 | Fresenius Medical Care Deutschland Gmbh | Dialysis machine and method of operating a dialysis machine |
US6517510B1 (en) | 2000-06-26 | 2003-02-11 | Gaymar Industries, Inc. | Automatic patient control device |
US6293108B1 (en) | 2000-06-30 | 2001-09-25 | Vortex Aircon | Regenerative refrigeration system with mixed refrigerants |
US6415797B1 (en) * | 2000-07-07 | 2002-07-09 | First Circle Medical, Inc. | Treatment of human herpesviruses using hyperthermia |
AU2001265253A1 (en) | 2000-07-07 | 2002-01-21 | First Circle Medical, Inc. | Treatment of hiv using hyperthermia |
US6503062B1 (en) | 2000-07-10 | 2003-01-07 | Deka Products Limited Partnership | Method for regulating fluid pump pressure |
US6561655B2 (en) | 2000-07-12 | 2003-05-13 | Minolta Co., Ltd. | Projector |
US6543814B2 (en) | 2000-08-10 | 2003-04-08 | John M. Bartholomew | Quick connector |
US6788885B2 (en) | 2000-09-01 | 2004-09-07 | Michael Mitsunaga | System for heating instillation or transfusion liquids |
US6336003B1 (en) | 2000-09-01 | 2002-01-01 | Automatic Medical Technologies, Inc. | Max one I.V. warmer |
US20020031836A1 (en) | 2000-09-11 | 2002-03-14 | Feldstein Mark J. | Fluidics system |
DE10046651A1 (en) | 2000-09-20 | 2002-04-04 | Fresenius Medical Care De Gmbh | Valve |
IT1320264B1 (en) | 2000-09-29 | 2003-11-26 | Gambro Dasco Spa | DIALYSIS EQUIPMENT AND METHOD OF VERIFICATION OF THE FUNCTIONALITY OF A DIALYSIS EQUIPMENT. |
US6785934B2 (en) | 2000-10-02 | 2004-09-07 | Cornice Technologies Inc | Universal vacuum extension kit |
EP1258260A3 (en) | 2000-10-04 | 2003-11-26 | Terumo Kabushiki Kaisha | Peritoneal dialysis apparatus |
JP4643815B2 (en) | 2000-10-04 | 2011-03-02 | テルモ株式会社 | Peritoneal dialysis machine |
EP2044965B1 (en) | 2000-10-12 | 2012-12-19 | Renal Solutions, Inc. | Apparatus for body fluid flow control in extracorporeal fluid treatments |
DE10053441B4 (en) | 2000-10-27 | 2004-04-15 | Fresenius Medical Care Deutschland Gmbh | Disposable cassette with sealing membrane and valve actuator therefor |
US6689083B1 (en) * | 2000-11-27 | 2004-02-10 | Chf Solutions, Inc. | Controller for ultrafiltration blood circuit which prevents hypotension by monitoring osmotic pressure in blood |
JP4405664B2 (en) | 2000-12-28 | 2010-01-27 | 株式会社ミクニ | Diaphragm fuel pump |
US6814718B2 (en) | 2001-01-09 | 2004-11-09 | Rex Medical, L.P | Dialysis catheter |
US6529775B2 (en) * | 2001-01-16 | 2003-03-04 | Alsius Corporation | System and method employing indwelling RF catheter for systemic patient warming by application of dielectric heating |
US6539172B2 (en) | 2001-01-31 | 2003-03-25 | Kabushiki Kaisha Sanko | Fluid heating device and cartridge for the same |
JPWO2002094359A1 (en) | 2001-05-23 | 2004-09-02 | 株式会社メトラン | Measuring device for inspiratory temperature in breathing circuit |
DE10126134B4 (en) | 2001-05-29 | 2004-02-26 | W.E.T. Automotive Systems Ag | Flat heating element |
US6527758B2 (en) | 2001-06-11 | 2003-03-04 | Kam Ko | Vial docking station for sliding reconstitution with diluent container |
US7641864B2 (en) | 2001-06-15 | 2010-01-05 | Avure Technologies Incorporated | Thermal sensor connector for pressure vessel |
JP2003000706A (en) | 2001-06-19 | 2003-01-07 | Terumo Corp | Peritoneal dialyzing circuit |
EP1453592B1 (en) | 2001-07-16 | 2009-12-23 | Miox Corporation | Dual head pump driven membrane system |
US6905314B2 (en) | 2001-10-16 | 2005-06-14 | Baxter International Inc. | Pump having flexible liner and compounding apparatus having such a pump |
US6722865B2 (en) | 2001-09-07 | 2004-04-20 | Terumorcardiovascular Systems Corporation | Universal tube clamp assembly |
US6868309B1 (en) | 2001-09-24 | 2005-03-15 | Aksys, Ltd. | Dialysis machine with symmetric multi-processing (SMP) control system and method of operation |
US7241272B2 (en) | 2001-11-13 | 2007-07-10 | Baxter International Inc. | Method and composition for removing uremic toxins in dialysis processes |
US7645253B2 (en) | 2001-11-16 | 2010-01-12 | National Quality Care, Inc. | Wearable ultrafiltration device |
SE525132C2 (en) | 2001-11-23 | 2004-12-07 | Gambro Lundia Ab | Method of operation of dialysis device |
US6608968B2 (en) | 2001-11-23 | 2003-08-19 | Allan P Bakke | Convection blood warming system with disposable flattened tube envelope incorporating paperboard “needle” for inserting envelope between heating plates and employing active and passive insulation of outlet flow path to provide normothermic fluid at zero to 600 milliliters per minute |
DE10157924C1 (en) | 2001-11-26 | 2003-06-26 | Fresenius Medical Care De Gmbh | Medical fluid treatment device |
US8226605B2 (en) | 2001-12-17 | 2012-07-24 | Medical Solutions, Inc. | Method and apparatus for heating solutions within intravenous lines to desired temperatures during infusion |
ITMI20012829A1 (en) * | 2001-12-28 | 2003-06-28 | Gambro Dasco Spa | APPARATUS AND METHOD OF CONTROL IN A BLOOD EXTRACORPOREAL CIRCUIT |
US7122210B2 (en) | 2002-01-11 | 2006-10-17 | Baxter International Inc. | Bicarbonate-based solutions for dialysis therapies |
US7107837B2 (en) | 2002-01-22 | 2006-09-19 | Baxter International Inc. | Capacitance fluid volume measurement |
US6692457B2 (en) * | 2002-03-01 | 2004-02-17 | Insulet Corporation | Flow condition sensor assembly for patient infusion device |
SE520340C2 (en) | 2002-03-14 | 2003-06-24 | Billy Nilson | Ambulatory diaphragm pump |
JP2003265599A (en) | 2002-03-15 | 2003-09-24 | Nextier:Kk | Hemocatharsis system |
DE10212247C1 (en) | 2002-03-19 | 2003-12-18 | Fresenius Medical Care De Gmbh | Method for determining a treatment parameter on a hemofiltration device and hemofiltration device for using the method |
US7073825B2 (en) * | 2002-04-10 | 2006-07-11 | Smc Corporation | One-operation piping-installation fluid pressure apparatus |
US7052480B2 (en) | 2002-04-10 | 2006-05-30 | Baxter International Inc. | Access disconnection systems and methods |
US7138088B2 (en) | 2002-04-10 | 2006-11-21 | Baxter International Inc. | Access disconnection system and methods |
AU2003230862A1 (en) | 2002-04-11 | 2003-10-27 | Deka Products Limited Partnership | System and method for delivering a target volume of fluid |
DE10216146A1 (en) * | 2002-04-12 | 2003-10-30 | Bayer Ag | diaphragm pump |
US20040109769A1 (en) | 2002-04-12 | 2004-06-10 | Bayer Aktiengesellschaft | Diaphragm pump |
US20040136843A1 (en) | 2002-04-12 | 2004-07-15 | Bayer Aktiengesellschaft | Diaphragm pump |
ITMI20021028A1 (en) * | 2002-05-14 | 2003-11-14 | Dideco Spa | PUMPING UNIT OF FLUID IN PARTICULAR BLOOD |
US6939111B2 (en) | 2002-05-24 | 2005-09-06 | Baxter International Inc. | Method and apparatus for controlling medical fluid pressure |
US20030220607A1 (en) | 2002-05-24 | 2003-11-27 | Don Busby | Peritoneal dialysis apparatus |
US7115228B2 (en) | 2002-05-24 | 2006-10-03 | Baxter International Inc. | One-piece tip protector and organizer |
US6929751B2 (en) | 2002-05-24 | 2005-08-16 | Baxter International Inc. | Vented medical fluid tip protector methods |
US7175606B2 (en) * | 2002-05-24 | 2007-02-13 | Baxter International Inc. | Disposable medical fluid unit having rigid frame |
US7153286B2 (en) | 2002-05-24 | 2006-12-26 | Baxter International Inc. | Automated dialysis system |
JP4902117B2 (en) | 2002-05-24 | 2012-03-21 | バクスター・インターナショナル・インコーポレイテッド | Automated dialysis system |
DE10224750A1 (en) | 2002-06-04 | 2003-12-24 | Fresenius Medical Care De Gmbh | Device for the treatment of a medical fluid |
US20040009096A1 (en) | 2002-06-08 | 2004-01-15 | Wellman Parris S. | Substantially inertia free hemodialysis |
DE10227193B4 (en) * | 2002-06-18 | 2007-05-10 | Ulman Dichtungstechnik Gmbh | Composite membrane for diaphragm pumps |
DE10227192B4 (en) * | 2002-06-18 | 2009-08-06 | Ulman Dichtungstechnik Gmbh | Composite membrane for diaphragm pumps |
MXPA05000816A (en) | 2002-07-19 | 2005-04-28 | Baxter Int | Systems and methods for performing peritoneal dialysis. |
US7238164B2 (en) * | 2002-07-19 | 2007-07-03 | Baxter International Inc. | Systems, methods and apparatuses for pumping cassette-based therapies |
EP1394366B1 (en) | 2002-09-02 | 2007-03-07 | BorgWarner Inc. | Turbomachine housing |
US7175397B2 (en) | 2002-09-27 | 2007-02-13 | Pulsafeeder, Inc. | Effervescent gas bleeder apparatus |
US20040138607A1 (en) | 2002-10-08 | 2004-07-15 | Burbank Jeffrey H. | Cartridge-based medical fluid processing system |
JP2004147721A (en) | 2002-10-29 | 2004-05-27 | Aisin Seiki Co Ltd | Blood pump driver |
AU2003287486A1 (en) | 2002-11-01 | 2004-06-07 | Nxstage Medical, Inc. | Functional isolation of upgradeable components to reduce risk in medical treatment devices |
DE10256923B4 (en) | 2002-12-05 | 2013-10-24 | Liebherr-France S.A. | Method and device for motion damping of hydraulic cylinders of mobile machines |
ITMI20030214A1 (en) | 2003-02-07 | 2004-08-08 | Gambro Lundia Ab | SUPPORT ELEMENT FOR AN INTEGRATED MODULE |
US7247146B2 (en) | 2003-02-07 | 2007-07-24 | Gambro Lundia Ab | Support element for an integrated blood treatment module, integrated blood treatment module and extracorporeal blood treatment apparatus equipped with said integrated module |
US7232418B2 (en) | 2003-02-07 | 2007-06-19 | Gambro Lundia Ab | Support element, an integrated module for extracorporeal blood treatment comprising the support element, an apparatus for extracorporeal blood treatment equipped with the integrated module, and an assembly process for an integrated module for extracorporeal blood treatment |
US7488448B2 (en) | 2004-03-01 | 2009-02-10 | Indian Wells Medical, Inc. | Method and apparatus for removal of gas bubbles from blood |
US7169303B2 (en) * | 2003-05-28 | 2007-01-30 | Hemocleanse Technologies, Llc | Sorbent reactor for extracorporeal blood treatment systems, peritoneal dialysis systems, and other body fluid treatment systems |
JP4286073B2 (en) | 2003-06-18 | 2009-06-24 | ニプロ株式会社 | Coupler for dialyzer connection |
JP4041018B2 (en) | 2003-06-25 | 2008-01-30 | Tdk株式会社 | Temperature sensor |
JP2005013502A (en) * | 2003-06-26 | 2005-01-20 | Aisin Seiki Co Ltd | Blood pump drive unit |
KR20060019576A (en) | 2003-07-04 | 2006-03-03 | 마쯔시다덴기산교 가부시키가이샤 | Vacuum thermal insulation material and equipment using the same |
US20050049539A1 (en) | 2003-09-03 | 2005-03-03 | O'hara Gerald P. | Control system for driving fluids through an extracorporeal blood circuit |
JP4732726B2 (en) | 2003-09-09 | 2011-07-27 | セイコーインスツル株式会社 | Manufacturing method of semiconductor device |
US7364563B2 (en) | 2003-10-02 | 2008-04-29 | Minnetronix, Inc. | Continuous volume detection for a flexible venous reservoir in a cardiopulmonary bypass circuit |
US6826948B1 (en) | 2003-10-09 | 2004-12-07 | Delphi Technologies, Inc. | Leak detection apparatus for a liquid circulation cooling system |
SE0302698L (en) | 2003-10-13 | 2005-04-14 | Gambro Lundia Ab | Device for performing a peritoneal dialysis treatment |
US7029456B2 (en) | 2003-10-15 | 2006-04-18 | Baxter International Inc. | Medical fluid therapy flow balancing and synchronization system |
EP1680155B2 (en) | 2003-10-28 | 2015-11-04 | Baxter International Inc. | Dialysis machine with improved integrity test |
US20050095152A1 (en) | 2003-10-30 | 2005-05-05 | Deka Products Limited Partnership | Door locking mechanism |
US8803044B2 (en) | 2003-11-05 | 2014-08-12 | Baxter International Inc. | Dialysis fluid heating systems |
US7776006B2 (en) | 2003-11-05 | 2010-08-17 | Baxter International Inc. | Medical fluid pumping system having real time volume determination |
US8029454B2 (en) | 2003-11-05 | 2011-10-04 | Baxter International Inc. | High convection home hemodialysis/hemofiltration and sorbent system |
US8038639B2 (en) | 2004-11-04 | 2011-10-18 | Baxter International Inc. | Medical fluid system with flexible sheeting disposable unit |
US7744553B2 (en) | 2003-12-16 | 2010-06-29 | Baxter International Inc. | Medical fluid therapy flow control systems and methods |
US8672875B2 (en) * | 2003-12-31 | 2014-03-18 | Carefusion 303, Inc. | Medication safety enhancement for secondary infusion |
DE602005006748D1 (en) | 2004-01-21 | 2008-06-26 | Imi Vision Ltd | FLUID DOSING WITH PUMP UNIT WITH DISPOSABLE MEMBRANE |
JP4265820B2 (en) * | 2004-02-27 | 2009-05-20 | シーケーディ株式会社 | Chemical supply system |
US7899508B2 (en) | 2004-03-11 | 2011-03-01 | Board Of Regents, The University Of Texas System | Intracorporeal impedance and leak monitoring device |
JP2005261558A (en) | 2004-03-17 | 2005-09-29 | Toray Medical Co Ltd | Removal blood pressure measuring system for hemodialyzer |
NZ531822A (en) * | 2004-03-18 | 2007-08-31 | Prec Dispensing Systems Ltd | A membrane pump |
US7303540B2 (en) | 2004-04-26 | 2007-12-04 | Chf Solutions, Inc. | User interface for blood treatment device |
US7776210B2 (en) | 2004-06-09 | 2010-08-17 | Renal Solutions, Inc. | Dialysis system |
US7124996B2 (en) | 2004-07-16 | 2006-10-24 | Cardinal Health 303, Inc. | Automatic clamp apparatus for IV infusion sets used in pump devices |
US7129828B2 (en) * | 2004-07-20 | 2006-10-31 | Honeywell International Inc. | Encapsulated surface acoustic wave sensor |
JP2006198141A (en) | 2005-01-20 | 2006-08-03 | Toray Medical Co Ltd | Abnormality detecting system in blood extracorporeal circulation apparatus |
JP2006204343A (en) * | 2005-01-25 | 2006-08-10 | Hiroshima Univ | Auxiliary artificial heart |
US20060189926A1 (en) | 2005-02-14 | 2006-08-24 | Hall W D | Apparatus and methods for analyzing body fluid samples |
SE532147C2 (en) | 2005-02-16 | 2009-11-03 | Triomed Ab | Portable dialysis system |
US20060195064A1 (en) | 2005-02-28 | 2006-08-31 | Fresenius Medical Care Holdings, Inc. | Portable apparatus for peritoneal dialysis therapy |
US7935074B2 (en) * | 2005-02-28 | 2011-05-03 | Fresenius Medical Care Holdings, Inc. | Cassette system for peritoneal dialysis machine |
US8734404B2 (en) | 2005-03-17 | 2014-05-27 | Patented Medical Solutions, Llc | Lay flat tubing |
CA2968816C (en) | 2005-03-17 | 2019-12-03 | Nox Ii, Ltd. | Reducing mercury emissions from the burning of coal |
WO2006120415A1 (en) | 2005-05-06 | 2006-11-16 | Imi Vision Limited | Dialysis machine |
DE102005024363B4 (en) * | 2005-05-27 | 2012-09-20 | Fresenius Medical Care Deutschland Gmbh | Apparatus and method for conveying liquids |
US7717682B2 (en) * | 2005-07-13 | 2010-05-18 | Purity Solutions Llc | Double diaphragm pump and related methods |
US8197231B2 (en) | 2005-07-13 | 2012-06-12 | Purity Solutions Llc | Diaphragm pump and related methods |
JP2007035582A (en) | 2005-07-29 | 2007-02-08 | Time Engineering Co Ltd | Flow control apparatus and fuel cell system |
EP1919550B1 (en) | 2005-08-05 | 2013-07-03 | Fresenius Medical Care Holdings, Inc. | Dual-channel pump for dialysis use |
JP4118293B2 (en) | 2005-10-03 | 2008-07-16 | 独立行政法人科学技術振興機構 | Body fluid purification cassette molding method |
US7857506B2 (en) | 2005-12-05 | 2010-12-28 | Sencal Llc | Disposable, pre-calibrated, pre-validated sensors for use in bio-processing applications |
US20070179436A1 (en) * | 2005-12-21 | 2007-08-02 | Braig James R | Analyte detection system with periodic sample draw and laboratory-grade analyzer |
WO2007092637A2 (en) | 2006-02-09 | 2007-08-16 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
US8469331B2 (en) | 2006-04-07 | 2013-06-25 | Nxstage Medical, Inc. | Filtration system for preparation of fluids for medical applications |
CN100460026C (en) | 2006-04-12 | 2009-02-11 | 重庆山外山科技有限公司 | Medical hemodialysis filter |
CA3123166A1 (en) | 2006-04-14 | 2007-10-25 | Deka Products Limited Partnership | Systems, devices and methods for fluid pumping, heat exchange, thermal sensing, and conductivity sensing |
US20140199193A1 (en) | 2007-02-27 | 2014-07-17 | Deka Products Limited Partnership | Blood treatment systems and methods |
US8366316B2 (en) | 2006-04-14 | 2013-02-05 | Deka Products Limited Partnership | Sensor apparatus systems, devices and methods |
US10537671B2 (en) | 2006-04-14 | 2020-01-21 | Deka Products Limited Partnership | Automated control mechanisms in a hemodialysis apparatus |
US20080240929A1 (en) | 2007-03-30 | 2008-10-02 | Deka Products Limited Partnership | Pumping Cassette |
EP2012848B1 (en) | 2006-04-27 | 2019-07-24 | Gambro Lundia AB | Remote controlled medical apparatus |
ITRM20060232A1 (en) | 2006-04-28 | 2007-10-29 | Blue Magic S R L | DISPENSER DEVICE FOR HYDRAULIC SYSTEMS |
US8048047B2 (en) | 2006-06-23 | 2011-11-01 | Novartis Ag | Surgical cassette with improved air filtering |
US20080287854A1 (en) | 2006-06-24 | 2008-11-20 | Jiandong Sun | Emergency-Disengagement Device for Patients Undergoing Hemodialysis |
US20080015515A1 (en) | 2006-06-29 | 2008-01-17 | Mark Alan Hopkins | Top and bottom clamping for a surgical cassette |
EP2046416B1 (en) | 2006-07-14 | 2015-09-16 | Gambro Lundia AB | Blood processing apparatus |
US20080058712A1 (en) | 2006-08-31 | 2008-03-06 | Plahey Kulwinder S | Peritoneal dialysis machine with dual voltage heater circuit and method of operation |
US8926550B2 (en) | 2006-08-31 | 2015-01-06 | Fresenius Medical Care Holdings, Inc. | Data communication system for peritoneal dialysis machine |
US8870811B2 (en) | 2006-08-31 | 2014-10-28 | Fresenius Medical Care Holdings, Inc. | Peritoneal dialysis systems and related methods |
DE102006042336A1 (en) | 2006-09-08 | 2008-03-27 | Fresenius Medical Care Deutschland Gmbh | Device and method for monitoring access to a patient, in particular a vascular access in an extracorporeal blood treatment |
FR2907259A1 (en) | 2006-10-13 | 2008-04-18 | St Microelectronics Sa | REALIZING A METAL BARRIER IN AN INTEGRATED ELECTRONIC CIRCUIT |
JP2008104737A (en) | 2006-10-26 | 2008-05-08 | Terumo Corp | Peritoneal dialyzer |
WO2008053259A1 (en) | 2006-10-30 | 2008-05-08 | Gambro Lundia Ab | Hemo(dia)filtration apparatus |
CN101206517B (en) | 2006-12-22 | 2011-06-22 | 群康科技(深圳)有限公司 | Computer |
US20080161751A1 (en) * | 2006-12-29 | 2008-07-03 | Plahey Kulwinder S | Peritoneal dialysis therapy validation |
US8529761B2 (en) | 2007-02-13 | 2013-09-10 | Fluid Equipment Development Company, Llc | Central pumping and energy recovery in a reverse osmosis system |
US8226293B2 (en) * | 2007-02-22 | 2012-07-24 | Medical Solutions, Inc. | Method and apparatus for measurement and control of temperature for infused liquids |
US8393690B2 (en) | 2007-02-27 | 2013-03-12 | Deka Products Limited Partnership | Enclosure for a portable hemodialysis system |
US8491184B2 (en) | 2007-02-27 | 2013-07-23 | Deka Products Limited Partnership | Sensor apparatus systems, devices and methods |
KR101385448B1 (en) | 2007-02-27 | 2014-04-15 | 삼성디스플레이 주식회사 | Circuit for driving source wire and display device having the same |
US20090107335A1 (en) | 2007-02-27 | 2009-04-30 | Deka Products Limited Partnership | Air trap for a medical infusion device |
US8409441B2 (en) | 2007-02-27 | 2013-04-02 | Deka Products Limited Partnership | Blood treatment systems and methods |
US8317492B2 (en) | 2007-02-27 | 2012-11-27 | Deka Products Limited Partnership | Pumping cassette |
US8562834B2 (en) | 2007-02-27 | 2013-10-22 | Deka Products Limited Partnership | Modular assembly for a portable hemodialysis system |
US9028691B2 (en) | 2007-02-27 | 2015-05-12 | Deka Products Limited Partnership | Blood circuit assembly for a hemodialysis system |
US10463774B2 (en) | 2007-02-27 | 2019-11-05 | Deka Products Limited Partnership | Control systems and methods for blood or fluid handling medical devices |
CA2681912C (en) | 2007-02-27 | 2015-09-29 | Deka Products Limited Partnership | Hemodialysis systems and methods |
US9517295B2 (en) | 2007-02-27 | 2016-12-13 | Deka Products Limited Partnership | Blood treatment systems and methods |
US8042563B2 (en) | 2007-02-27 | 2011-10-25 | Deka Products Limited Partnership | Cassette system integrated apparatus |
WO2008106452A1 (en) | 2007-02-27 | 2008-09-04 | Deka Products Limited Partnership | Peritoneal dialysis sensor apparatus systems, devices and methods |
US8357298B2 (en) | 2007-02-27 | 2013-01-22 | Deka Products Limited Partnership | Hemodialysis systems and methods |
US8425471B2 (en) | 2007-02-27 | 2013-04-23 | Deka Products Limited Partnership | Reagent supply for a hemodialysis system |
WO2008129084A1 (en) | 2007-04-23 | 2008-10-30 | Fundación Para La Investigación Biomédica Del Hospital Gregorio Marañon | Haemodialfiltration method and apparatus |
JP4513824B2 (en) | 2007-04-26 | 2010-07-28 | 株式会社ジェイ・エム・エス | Liquid automatic supply / discharge device for peritoneal dialysis device and automatic peritoneal dialysis device using the device |
EP2002855B1 (en) | 2007-06-14 | 2012-07-11 | RenApta B.V. | Artificial kidney |
US7790103B2 (en) | 2007-07-05 | 2010-09-07 | Baxter International Inc. | Extended use dialysis system |
US8330579B2 (en) | 2007-07-05 | 2012-12-11 | Baxter International Inc. | Radio-frequency auto-identification system for dialysis systems |
US20090007642A1 (en) | 2007-07-05 | 2009-01-08 | Baxter International Inc. | Dialysis fluid measurement method and apparatus using conductive contacts |
US7955295B2 (en) | 2007-07-05 | 2011-06-07 | Baxter International Inc. | Fluid delivery system with autoconnect features |
US8057423B2 (en) | 2007-07-05 | 2011-11-15 | Baxter International Inc. | Dialysis system having disposable cassette |
US7901376B2 (en) | 2007-07-05 | 2011-03-08 | Baxter International Inc. | Dialysis cassette having multiple outlet valve |
US7957927B2 (en) * | 2007-07-05 | 2011-06-07 | Baxter International Inc. | Temperature compensation for pneumatic pumping system |
US7909795B2 (en) * | 2007-07-05 | 2011-03-22 | Baxter International Inc. | Dialysis system having disposable cassette and interface therefore |
US8496609B2 (en) * | 2007-07-05 | 2013-07-30 | Baxter International Inc. | Fluid delivery system with spiked cassette |
US7905855B2 (en) * | 2007-07-05 | 2011-03-15 | Baxter International Inc. | Dialysis system having non-invasive temperature sensing |
US7736328B2 (en) | 2007-07-05 | 2010-06-15 | Baxter International Inc. | Dialysis system having supply container autoconnection |
US8105266B2 (en) * | 2007-07-05 | 2012-01-31 | Baxter International Inc. | Mobile dialysis system having supply container detection |
US8764702B2 (en) * | 2007-07-05 | 2014-07-01 | Baxter International Inc. | Dialysis system having dual patient line connection and prime |
US8287724B2 (en) | 2007-07-05 | 2012-10-16 | Baxter International Inc. | Dialysis fluid measurement systems using conductive contacts |
US8512553B2 (en) | 2007-07-05 | 2013-08-20 | Baxter International Inc. | Extracorporeal dialysis ready peritoneal dialysis machine |
US8715235B2 (en) | 2007-07-05 | 2014-05-06 | Baxter International Inc. | Dialysis system having disposable cassette and heated cassette interface |
US8597505B2 (en) | 2007-09-13 | 2013-12-03 | Fresenius Medical Care Holdings, Inc. | Portable dialysis machine |
US20090076434A1 (en) * | 2007-09-13 | 2009-03-19 | Mischelevich David J | Method and System for Achieving Volumetric Accuracy in Hemodialysis Systems |
EP3150238B1 (en) | 2007-09-19 | 2018-03-14 | Fresenius Medical Care Holdings, Inc. | Dialysis systems and related components |
US7892197B2 (en) | 2007-09-19 | 2011-02-22 | Fresenius Medical Care Holdings, Inc. | Automatic prime of an extracorporeal blood circuit |
US7892331B2 (en) | 2007-10-01 | 2011-02-22 | Baxter International Inc. | Dialysis systems having air separation chambers with internal structures to enhance air removal |
US7938792B2 (en) | 2007-10-01 | 2011-05-10 | Baxter International Inc. | Adaptive algorithm for access disconnect detection |
US8444587B2 (en) | 2007-10-01 | 2013-05-21 | Baxter International Inc. | Fluid and air handling in blood and dialysis circuits |
US8863772B2 (en) | 2008-08-27 | 2014-10-21 | Deka Products Limited Partnership | Occluder for a medical infusion system |
US20100056975A1 (en) | 2008-08-27 | 2010-03-04 | Deka Products Limited Partnership | Blood line connector for a medical infusion device |
CA2702385C (en) | 2007-10-12 | 2017-07-18 | Deka Products Limited Partnership | Apparatus and methods for hemodialysis |
EP2246080B1 (en) | 2007-10-12 | 2016-02-10 | DEKA Products Limited Partnership | An extracorporeal blood flow system |
US8771508B2 (en) | 2008-08-27 | 2014-07-08 | Deka Products Limited Partnership | Dialyzer cartridge mounting arrangement for a hemodialysis system |
US7887495B2 (en) | 2007-10-18 | 2011-02-15 | Boyd Lawrence M | Protective and cosmetic covering for external fixators |
US8858787B2 (en) | 2007-10-22 | 2014-10-14 | Baxter International Inc. | Dialysis system having non-invasive fluid velocity sensing |
US8114276B2 (en) * | 2007-10-24 | 2012-02-14 | Baxter International Inc. | Personal hemodialysis system |
US7905853B2 (en) * | 2007-10-30 | 2011-03-15 | Baxter International Inc. | Dialysis system having integrated pneumatic manifold |
US20090113335A1 (en) * | 2007-10-30 | 2009-04-30 | Baxter International Inc. | Dialysis system user interface |
US9415150B2 (en) | 2007-11-09 | 2016-08-16 | Baxter Healthcare S.A. | Balanced flow dialysis machine |
US8038640B2 (en) | 2007-11-26 | 2011-10-18 | Purity Solutions Llc | Diaphragm pump and related systems and methods |
CA2960103C (en) | 2007-11-29 | 2020-03-10 | Fredenius Medical Care Holdings, Inc. | System and method for conducting hemodialysis and hemofiltration |
US9248225B2 (en) | 2008-01-23 | 2016-02-02 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US8708950B2 (en) | 2010-07-07 | 2014-04-29 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US10201647B2 (en) | 2008-01-23 | 2019-02-12 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
EP2113266A1 (en) | 2008-04-30 | 2009-11-04 | Gambro Lundia AB | Degassing device |
US20090294359A1 (en) | 2008-06-03 | 2009-12-03 | Baxter International Inc. | Priming system and method using pumping and gravity |
JP5654466B2 (en) | 2008-08-27 | 2015-01-14 | デカ・プロダクツ・リミテッド・パートナーシップ | Operation method of dialysis system |
EP2334412B1 (en) | 2008-10-07 | 2019-08-21 | Fresenius Medical Care Holdings, Inc. | Priming system and method for dialysis systems |
WO2010141326A1 (en) | 2009-06-02 | 2010-12-09 | Integenx Inc. | Fluidic devices with diaphragm valves |
WO2010139918A1 (en) | 2009-06-03 | 2010-12-09 | The Technology Partnership Plc | Pump with disc-shaped cavity |
CA2779296C (en) | 2009-10-30 | 2018-02-13 | Deka Products Limited Partnership | Apparatus and method for detecting disconnection of an intravascular access device |
EP2759311B1 (en) | 2009-12-24 | 2017-02-22 | VR Medical Technology Co., Ltd. | Automated peritoneal dialysis cycler and methods of use |
EP3542840B1 (en) | 2011-03-23 | 2023-04-26 | NxStage Medical, Inc. | Peritoneal dialysis systems |
US9999717B2 (en) | 2011-05-24 | 2018-06-19 | Deka Products Limited Partnership | Systems and methods for detecting vascular access disconnection |
CA3166031A1 (en) | 2011-05-24 | 2012-11-29 | Deka Products Limited Partnership | Hemodialysis system |
WO2013067359A2 (en) | 2011-11-04 | 2013-05-10 | Deka Products Limited Partnership | Medical treatment system and methods using a plurality of fluid lines |
US9364655B2 (en) | 2012-05-24 | 2016-06-14 | Deka Products Limited Partnership | Flexible tubing occlusion assembly |
GB201210082D0 (en) | 2012-06-07 | 2012-07-25 | Consort Medical Plc | Improved syringe |
EP2712639B1 (en) | 2012-09-28 | 2015-06-24 | Gambro Lundia AB | An apparatus for extracorporeal blood treatment and a control method therefor |
EP2712638B1 (en) | 2012-09-28 | 2015-06-24 | Gambro Lundia AB | An apparatus and a method of controlling an extracorporeal blood treatment |
WO2014144909A2 (en) | 2013-03-15 | 2014-09-18 | Deka Products Limited Partnership | Blood treatment systems and methods |
JP6429267B2 (en) | 2014-04-28 | 2018-11-28 | Jsr株式会社 | Polymer |
EP3148607B1 (en) | 2014-05-27 | 2019-07-10 | DEKA Products Limited Partnership | Control systems for blood or fluid handling medical devices |
EP3524291B1 (en) | 2014-05-27 | 2023-11-29 | DEKA Products Limited Partnership | System for detecting replacement of blood by dialysate solution |
EP3698826A1 (en) | 2014-06-05 | 2020-08-26 | DEKA Products Limited Partnership | System for calculating a change in fluid volume in a pumping chamber |
CN107532584B (en) | 2015-05-08 | 2019-12-27 | 株式会社村田制作所 | Pump and fluid control device |
CN108884823B (en) | 2016-07-29 | 2020-01-24 | 株式会社村田制作所 | Valve, gas control device, and sphygmomanometer |
BR112020019993A2 (en) | 2018-03-30 | 2021-01-26 | Deka Products Limited Partnership | liquid pumping cassettes and associated pressure distribution manifold and related methods |
-
2007
- 2007-04-13 CA CA3123166A patent/CA3123166A1/en active Pending
- 2007-04-13 US US11/787,213 patent/US20080058697A1/en not_active Abandoned
- 2007-04-13 JP JP2009505495A patent/JP2009533154A/en active Pending
- 2007-04-13 EP EP13184795.6A patent/EP2724736B1/en active Active
- 2007-04-13 MX MX2008013266A patent/MX2008013266A/en active IP Right Grant
- 2007-04-13 EP EP13150786.5A patent/EP2586472B1/en active Active
- 2007-04-13 WO PCT/US2007/009107 patent/WO2007120812A2/en active Application Filing
- 2007-04-13 EP EP22160534.8A patent/EP4074353A1/en active Pending
- 2007-04-13 CA CA3099207A patent/CA3099207C/en active Active
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