US20070055223A1 - Methods and apparatus for hemostasis following arterial catheterization - Google Patents

Methods and apparatus for hemostasis following arterial catheterization Download PDF

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Publication number
US20070055223A1
US20070055223A1 US10/543,654 US54365404A US2007055223A1 US 20070055223 A1 US20070055223 A1 US 20070055223A1 US 54365404 A US54365404 A US 54365404A US 2007055223 A1 US2007055223 A1 US 2007055223A1
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Prior art keywords
hemostasis
balloon
hemostasis device
main shaft
location
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Abandoned
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US10/543,654
Inventor
Shimon Eckhouse
Hayim Lindenbaum
Noam Mizrahi
Izhack Fabian
Eran Levi
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Cardiodex Ltd
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Cardiodex Ltd
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Priority claimed from US10/358,130 external-priority patent/US7115127B2/en
Application filed by Cardiodex Ltd filed Critical Cardiodex Ltd
Priority to US10/543,654 priority Critical patent/US20070055223A1/en
Assigned to CARDIODEX LTD. reassignment CARDIODEX LTD. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ECKHOUSE, SHIMON, FABIAN, IZHACK, LEVIT, ERAN, LINDENBAUM, HAYIM, MIZRAHI, NOAM
Publication of US20070055223A1 publication Critical patent/US20070055223A1/en
Abandoned legal-status Critical Current

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14Probes or electrodes therefor
    • A61B18/1492Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/08Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by means of electrically-heated probes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/08Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by means of electrically-heated probes
    • A61B18/082Probes or electrodes therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00022Sensing or detecting at the treatment site
    • A61B2017/00026Conductivity or impedance, e.g. of tissue
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A61B2017/00575Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect for closure at remote site, e.g. closing atrial septum defects
    • A61B2017/00601Implements entirely comprised between the two sides of the opening
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A61B2017/00646Type of implements
    • A61B2017/00654Type of implements entirely comprised between the two sides of the opening
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053Mechanical features of the instrument of device
    • A61B2018/00214Expandable means emitting energy, e.g. by elements carried thereon
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053Mechanical features of the instrument of device
    • A61B2018/00214Expandable means emitting energy, e.g. by elements carried thereon
    • A61B2018/0022Balloons
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345Vascular system
    • A61B2018/00404Blood vessels other than those in or around the heart
    • A61B2018/00422Angioplasty
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00589Coagulation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00773Sensed parameters
    • A61B2018/00875Resistance or impedance
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636Sensing and controlling the application of energy
    • A61B2018/00898Alarms or notifications created in response to an abnormal condition

Definitions

  • the present invention relates to catheterization systems and methodologies generally and more particularly to post-catheterization closure.
  • the present invention seeks to provide improved systems and methodologies for post-catheterization closure.
  • a hemostasis device including a resistance heating element for accelerating hemostasis, a blood resistance sensor and a blood resistance indicator, operative to provide an indication of the resistance at the resistance sensor of blood undergoing hemostasis.
  • the hemostasis device also includes a power supply connected to the resistance heating element, the resistance sensor and the resistance indicator. Additionally, the power supply is operative to supply a relatively high level current to the resistance heating element. Alternatively, the power supply is operative to supply a relatively low level current to the resistance sensor.
  • a method for accelerating hemostasis of an artery of a patient having a puncture after arterial catheterization including the steps of following arterial catheterization, introducing a hemostasis device, such that a forward end of the hemostasis device lies exterior of the artery adjacent the puncture, accelerating hemostasis by heating tissue in the vicinity of the puncture, thereby shortening the time required for hemostasis and following hemostasis, removing the hemostasis device from the patient.
  • the method also includes inserting a catheter introducer into the artery prior to the arterial catheterization and wherein following the arterial catheterization, the hemostasis device is introduced through the catheter introducer.
  • the method also includes measuring the conductivity of blood in the vicinity of the puncture during hemostasis.
  • a method for monitoring the progress of hemostasis of an artery of a patient having a puncture after arterial catheterization including the steps of following arterial catheterization, introducing a hemostasis device, such that a forward end of the hemostasis device lies exterior of the artery adjacent the puncture, during hemostasis, measuring the heat conductivity of blood in the vicinity of the puncture, thereby to provide an output indication of the progress of hemostasis and following hemostasis, removing the hemostasis device from the patient.
  • the method also includes the step of inserting into an artery a catheter introducer prior to arterial catheterization and wherein following the arterial catheterization, the hemostasis device is introduced through the catheter introducer.
  • the method also includes inflating a balloon to block the puncture, prior to the hemostasis. Additionally, the method also includes deflating the balloon prior to removing the hemostasis device.
  • a hemostasis device including a main shaft, at least one balloon mounted on the main shaft and at least one electrode, mounted on the main shaft and being operable to supply an electric current suitable for causing hemostasis.
  • the at least one balloon includes at least one anchor balloon, disposed at an end of the main shaft and at least one peripheral balloon, disposed at a location along the main shaft exterior to a wall of the main shaft.
  • the at least one peripheral balloon and a wall of an artery are configured to delimit a region which is subject to hemostasis.
  • the hemostasis device also includes an electrical power source and a control module.
  • the power source is an RF power supply.
  • the RF power supply is operative to supply electrical power at RF frequencies within a range of 0.1-10 watts at up to 25 volts.
  • the control module is operative to measure at least one of electrical current, blood resistance and blood temperature. Additionally or alternatively, the control module is operative to adjust the power supplied by the power source based on at least one measurement.
  • the at least one electrode includes a pair of electrodes.
  • a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one electrode into the vicinity of the puncture, supplying an electric current to the at least one electrode, thereby heating a volume of blood in the vicinity of the puncture, causing hemostasis and subsequently removing the hemostasis device from the patient.
  • introducing includes introducing via a catheter introducer. Additionally or alternatively, the introducing also includes inflating an anchor balloon attached to an end of the hemostasis device. In accordance with another preferred embodiment of the present invention the introducing includes inflating a peripheral balloon. Additionally, the removing the hemostasis device includes deflating the peripheral balloon.
  • the introducing includes positioning the at least one electrode in close proximity to a volume of blood.
  • the supplying includes supplying electrical power at RF frequencies. Additionally, the electrical power includes electrical power in the range of 0.1-10 watts at up to 25 volts. Alternatively or additionally, the supplying also includes adjusting the electric current based on a feedback measurement.
  • a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at the end of the main shaft beyond the at least one balloon.
  • the hemostasis device also includes at least one heating assembly operative to provide heating at the location.
  • the at least one heating assembly includes at least one electrode disposed adjacent the location.
  • the at least one electrode is disposed interiorly of the at least one balloon.
  • the at least one electrode is disposed exteriorly of the at least one balloon.
  • the at least one heating assembly includes an electrical resistive heating element.
  • the electrical resistive heating element is disposed within the at least one balloon.
  • a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and at least one RF electrode located at a location at an end of the main shaft beyond the at least one balloon.
  • the hemostasis device also includes a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of the main shaft beyond the at least one balloon.
  • the at least one RF electrode is disposed interiorly of the at least one balloon.
  • the at least one RF electrode is disposed exteriorly of the at least one balloon.
  • a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and at least one resistive heating element located at a location at an end of the main shaft beyond the at least one balloon.
  • the hemostasis device also includes a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of the main shaft beyond the at least one balloon.
  • the at least one resistance heating element is disposed interiorly of the at least one balloon.
  • a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon.
  • the method also includes providing heating at the location.
  • the providing heating includes locating at least one electrode adjacent the location. Additionally, the at least one electrode is disposed interiorly of the at least one balloon. Alternatively, the at least one electrode is disposed exteriorly of the at least one balloon.
  • the providing heating includes providing electrical resistive heating.
  • a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and operating at least one RF electrode at the location at the end of the main shaft beyond the at least one balloon.
  • the method also includes supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon.
  • the at least one RF electrode is disposed interiorly of the at least one balloon.
  • the at least one RF electrode is disposed exteriorly of the at least one balloon.
  • a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and operating at least one resistance heating element at the location at an end of the shaft beyond the at least one balloon.
  • the method also includes supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon.
  • the at least one resistance heating element is disposed interiorly of the at least one balloon.
  • FIGS. 1A and 1B are simplified pictorial illustrations of respective first and second modes of operation of a hemostasis device constructed and operative in accordance with a preferred embodiment of the present invention
  • FIG. 2 is a simplified pictorial illustration of the hemostasis device of FIGS. 1A and 1B during hemostasis;
  • FIGS. 3A and 3B are graphs illustrating the typical conductivity levels measured by the hemostasis device when used in the operating modes shown in FIGS. 1A and 1B , respectively;
  • FIG. 4 is a simplified illustration of a hemostasis device constructed and operative in accordance with a preferred embodiment of the present invention
  • FIGS. 5A, 5B , 5 C, 5 D, 5 E, 5 F, 5 G, 5 H and 5 I are simplified illustrations of the operation of the apparatus of FIG. 4 in a patient treatment context;
  • FIG. 6 is a simplified illustration of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention.
  • FIGS. 7A, 7B , 7 C, 7 D, 7 E, 7 F, 7 G, 7 H, 7 I and 7 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 8A, 8B , 8 C and 8 D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 7A-7J ;
  • FIGS. 9A, 9B , 9 C, 9 D, 9 E, 9 F, 9 G, 9 H, 9 I and 9 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 10A, 10B , 10 C and 10 D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 9A-9J ;
  • FIGS. 11A, 11B , 11 C, 11 D, 11 E, 11 F, 11 G, 11 H, 11 I and 11 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 12A, 12B , 12 C and 12 D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 11A-11J ;
  • FIGS. 13A, 13B , 13 C, 13 D, 13 E, 13 F, 13 G, 13 H, 13 I and 13 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 14A, 14B , 14 C and 14 D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 13A-13J ;
  • FIGS. 15A, 15B , 15 C, 15 D, 15 E, 15 F, 15 G, 15 H, 15 I and 15 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 16A, 16B , 16 C and 16 D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 15A-15J .
  • FIGS. 1A and 1B are simplified pictorial illustrations of a preferred embodiment of a hemostasis device in respective first and second modes of operation.
  • a hemostasis device 10 is inserted into a catheter introducer 11 , following arterial catheterization and withdrawal of a catheter (not shown), such that a forward end 12 of the hemostasis device 10 lies adjacent to and outside a puncture 14 in an artery 16 .
  • At least one external balloon 18 is preferably disposed adjacent catheter introducer 11 and is shown in an inflated orientation, wherein the balloon 18 forms a skirt surrounding and sealing puncture 14 from the tissue external thereto.
  • blood normally fills artery 16 as well as puncture 14 , as well as the annular volume 20 surrounded by balloon 18 adjacent puncture 14 and forward end 12 .
  • the at least one balloon 18 need not be provided.
  • a resistance element 22 is disposed at a forward edge 24 of the forward end 12 , and is coupled in series with an external power supply 26 via conductors 28 , which typically extend along the length of the hemostasis device 10 .
  • the series connection includes a resistance indicator 30 , which provides an indication of the resistance at a resistance sensor 32 .
  • a low level current is provided by external power supply 26 to enable the resistance indicator 30 to monitor the progress of hemostasis, to allow for timely removal of catheter introducer 11 and hemostasis device 10 from the patient.
  • the heat conductivity of the blood in liquid form is measurably different from that of a blood clot formed during hemostasis, as will be described hereinbelow with reference to FIGS. 3A and 3B .
  • FIG. 1B illustrates the hemostasis device of FIG. 1A in a second preferred mode of operation.
  • a high level electrical current typically greater than 0.1 ampere
  • the provision of this current causes heating of the blood adjacent to the resistance element 22 and provides for accelerated hemostasis.
  • resistance indicator 30 connected to resistance sensor 32 , enables the monitoring of the progress of the accelerated hemostasis, to allow for regulation of the current provided to resistance element 22 over time, and to allow timely removal of catheter introducer 11 and hemostasis device 10 from the patient.
  • the heat conductivity of the blood in liquid form is measurably different from that of a blood clot formed during hemostasis, as will be described hereinbelow with reference to FIGS. 3A and 3B .
  • FIG. 2 is a simplified pictorial illustration of hemostasis device 10 of FIGS. 1A and 1B during hemostasis.
  • FIG. 2 shows the hemostasis device 10 of FIGS. 1A and 1B and illustrates the different heat conductivity of the blood during the various stages of hemostasis.
  • the blood flowing through the artery 16 and adjacent the puncture 14 in the artery is in liquid form, where its heat conductivity is greater than that of the blood 40 which has begun to coagulate.
  • Blood 40 is in a viscous form, which has a heat conductivity greater than that of the blood 42 , which has already begun to solidify into a blood clot.
  • Resistance sensor 32 is thus able to measure the process of coagulation by measuring the heat conductivity of the adjacent blood.
  • FIGS. 3A and 3B are graphs illustrating the typical conductivity levels measured by the catheter introducer assembly when used in the operating modes shown in FIGS. 1A and 1B , respectively.
  • FIG. 3A shows the heat conductivity of the blood over time, in the mode of operation illustrated in FIG. 1A , where the blood is in a liquid form at time T 0 , with relatively high heat conductivity, where the heat conductivity decreases gradually over time as the blood forms a clot at time T H .
  • FIG. 3B shows the heat conductivity of the blood over time, in the mode of operation illustrated in FIG. 1B , where the blood is heated to accelerate clotting.
  • the heat conductivity begins at time T 0 in a liquid form with relatively high heat conductivity, which decreases rapidly as the blood is heated and the clotting occurs at an accelerated rate.
  • FIG. 3B also shows the heat conductivity curve over time shown in FIG. 3A , which clearly illustrates the accelerated hemostasis described in reference to FIG. 1B hereinabove, where T HA is the accelerated hemostasis time and T H is the non-accelerated hemostasis time.
  • FIG. 4 is a simplified illustration of a hemostasis device 100 for producing hemostasis following arterial catheterization, in accordance with a preferred embodiment of the present invention.
  • the hemostasis device 100 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 100 comprises a main shaft 102 , which has an outer wall 104 and preferably includes at least three bores.
  • a first bore designated generally by reference numeral 110 , extends along the main shaft 102 to an anchor balloon inflation location 112 .
  • a second bore 120 extends along the shaft 102 to a peripheral balloon inflation location 122 .
  • a third bore designated generally by reference number 130 , contains an electrocoagulation heating device 132 connected to an electrical power source and control module 134 by a connector 136 .
  • Anchor balloon 140 Disposed at an end of main shaft 102 at anchor balloon inflation location 112 is an anchor balloon 140 .
  • Anchor balloon 140 is selectably inflated at anchor balloon inflation location 112 , as shown in FIG. 5C , via a stopcock 142 and associated conduit 144 in fluid communication with main shaft 102 via a passageway 146 formed in a head element 150 .
  • Head element 150 is fixed to main shaft 102 at an end thereof opposite the end at which anchor balloon 140 is located.
  • Peripheral balloon 160 is selectably inflated at peripheral balloon inflation location 112 , as shown in FIG. 5E , via second bore 120 , via a stopcock 162 and associated conduit 164 that communicate with second bore 120 via a passageway 166 formed in head element 150 .
  • electrocoagulation heating device 132 comprises an electrical conductor 170 connected to an electrocoagulation electrode 176 at an extreme end 178 of third bore 130 .
  • a pair of electrical cables 180 and 182 extends from electrical power source and control module 134 .
  • electrical cable 180 serves as a power supply cable and is connected to electrocoagulation heating device 132 by connector 136 .
  • Electrical cable 182 serves as a return current cable and is preferably connected to an electrode 184 attached to a body of a patient.
  • Electrical power source and control module 134 preferably comprises a power supply, preferably an RF power supply source 186 , including a feedback measurement circuit 188 .
  • the feedback measurement circuit 188 is preferably operative to measure current, blood resistance or blood temperature and thereby determine progress of hemostasis.
  • the electrical power source and control module 134 also preferably includes a microprocessor 190 , operative to adjust the power supplied to hemostasis device 100 according to the blood temperature or other feedback measurement received from feedback measurement circuit 188 , in order to achieve optimal coagulation of the blood.
  • an operator actuation switch 192 is connected along electrical cable 180 .
  • switch 192 may be obviated and electrical cable 180 connected directly to connector 136 .
  • FIGS. 5A-5I illustrate various steps in a preferred mode of operation of the apparatus of FIG. 4 .
  • FIG. 5A illustrates the hemostasis device 100 about to be inserted into an artery 200 via a conventional catheter introducer assembly 202 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 202 .
  • the catheter introducer assembly 202 conventionally includes a catheter introducer sheath 204 .
  • FIG. 5B shows the hemostasis device 100 inserted into the catheter introducer assembly 202 such that the outer end of the main shaft 102 extends into the artery 200 well beyond the end of catheter introducer sheath 204 .
  • both anchor balloon 140 and peripheral balloon 160 are deflated.
  • FIG. 5C shows initial inflation of the anchor balloon 140 , preferably by use of a syringe 220 , communicating with first bore 110 via the interior of head element 150 , stopcock 142 and associated conduit 144 .
  • the inflated anchor balloon 140 preferably has a cusp-type configuration as seen with particularity in FIG. 5C .
  • the catheter introducer assembly 202 and the hemostasis device 100 are both withdrawn, such that the catheter introducer sheath 204 is removed from artery 200 only when the anchor balloon 140 already engages the interior wall of artery 200 in sealing engagement with the aperture in the artery 200 through which the catheter introducer sheath 204 is withdrawn and through which the main shaft 102 presently extends. This stage is shown in FIG. 5D .
  • initial inflation of the peripheral balloon 160 is effected, preferably by use of a syringe 240 communicating with second bore 120 via head element 150 , stopcock 162 and associated conduit 164 .
  • the anchor balloon 140 is deflated, preferably by operation of syringe 220 , communicating with first bore 110 via the interior of head element 150 , stopcock 142 and associated conduit 144 , and the peripheral balloon 160 is inflated, which preferably causes the extreme end of the main shaft 102 to be withdrawn from the artery 200 to a location lying just outside the artery wall.
  • peripheral balloon 160 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 140 is deflated. This volume of blood is located in a region, indicated by reference numeral 250 , delimited by the engagement of peripheral balloon 160 with the artery wall.
  • electric power is supplied to the electrode 176 to provide heating of the blood in region 250 , causing coagulation thereof, as seen in FIG. 5G .
  • the electric power is provided by actuation of switch 192 .
  • switch 192 is obviated, and the electric power is provided by connecting electrical cable 180 ( FIG. 4 ) directly to connector 136 .
  • the amount of electrical power supplied along electrical cable 180 ( FIG. 4 ) from electrical power source and control module 134 to the electrocoagulation electrode 176 is between 0.1-10 watts at up to 25 volts at RF frequencies.
  • the peripheral balloon 160 is deflated, as shown in FIG. 5H , preferably by operation of syringe 240 communicating with second bore 120 via head element 150 , stopcock 162 and associated conduit 164 .
  • the hemostasis device 100 is entirely withdrawn from the patient, leaving a region 260 of hemostasis outside of artery 200 , as shown in FIG. 5I .
  • FIG. 6 is a simplified illustration of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention.
  • the embodiment of FIG. 6 is similar to that of FIG. 4 , except as described hereinbelow. Elements that occur in both embodiments are identified by the same reference numerals.
  • electrocoagulation heating device 132 comprises a pair of separate electrical conductors 300 extending along third bore 130 connecting electrical power source and control module 134 to a pair of electrocoagulation electrodes 302 at end 178 of third bore 130 .
  • Electrical cables 180 and 182 are both connected to electrocoagulation heating device 132 by connector 136 .
  • the illustrated embodiment shows connector 136 directly connected to electrical cables 180 and 182 .
  • the electrodes 302 may be arranged in mutual coaxial arrangement or in mutual side-by-side arrangement or in any other suitable arrangement.
  • FIGS. 7A, 7B , 7 C, 7 D, 7 E, 7 F, 7 G, 7 H, 7 I and 7 J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context
  • FIGS. 8A, 8B , 8 C and 8 D are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 7A shows a hemostasis device 400 for producing hemostasis following arterial catheterization in accordance with another preferred embodiment of the present invention.
  • the hemostasis device 400 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 400 comprises a main shaft 402 , which has first and second lumens 404 and 406 .
  • First lumen 404 extends along the main shaft 402 to an anchor balloon inflation location 412 .
  • Second lumen 406 extends along the shaft 402 to a peripheral balloon inflation location 422 .
  • Anchor balloon 440 Disposed at an end of main shaft 402 at anchor balloon inflation location 412 is an anchor balloon 440 .
  • Anchor balloon 440 is selectably inflated, as shown in FIGS. 8A-8D , via a stopcock 442 and associated conduit 444 in fluid communication with main shaft 402 via a passageway 446 formed in a head element 450 .
  • Head element 450 is fixed to main shaft 402 at an end thereof opposite the end at which anchor balloon 440 is located.
  • peripheral balloon 460 Disposed adjacent the end of main shaft 402 , in fluid communication with peripheral balloon inflation location 422 , exterior of an outer wall 452 thereof, is a peripheral balloon 460 .
  • Peripheral balloon 460 is selectably inflated, as shown in FIGS. 8A-8D , via second lumen 406 , via a stopcock 462 and associated conduit 464 that communicate with second lumen 406 via a passageway 466 formed in head element 450 .
  • a coagulant agent supply conduit 470 extends through the first lumen 404 and through a bore 472 formed along the length of head element 450 .
  • Coagulant agent supply conduit 470 communicates at one end thereof with a volume defined by inflation of the peripheral balloon 460 , between the balloon 460 and the outer surface of an adjacent artery (not shown).
  • conduit 470 communicates with a supply of coagulant agent (not shown) via a stopcock 474 and associated conduit 476 .
  • FIGS. 7B-7J illustrate various steps in a preferred mode of operation of the apparatus of FIG. 7A .
  • FIG. 7B illustrates the hemostasis device 400 about to be inserted into an artery 500 via a conventional catheter introducer assembly 502 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 502 .
  • the catheter introducer assembly 502 conventionally includes a catheter introducer sheath 504 .
  • FIG. 7C shows the hemostasis device 400 inserted into the catheter introducer assembly 502 such that the outer end of the main shaft 402 extends into the artery 500 well beyond the end of catheter introducer sheath 504 .
  • both anchor balloon 440 and peripheral balloon 460 are deflated, as seen clearly in FIG. 8A .
  • FIG. 7D shows initial inflation of the anchor balloon 440 , preferably by use of a syringe 520 , communicating with first lumen 404 via passageway 446 extending through the interior of head element 450 , stopcock 442 and associated conduit 444 .
  • the inflated anchor balloon 440 preferably has a cusp-type configuration as seen with particularity in FIGS. 7D and 8B .
  • the catheter introducer assembly 502 and the hemostasis device 400 are both withdrawn, such that the catheter introducer sheath 504 is removed from artery 500 only when the anchor balloon 440 already engages the interior wall of artery 500 in sealing engagement with the aperture in the artery 500 through which the catheter introducer sheath 504 is withdrawn and through which the main shaft 402 presently extends. This stage is shown in FIG. 7E .
  • initial inflation of the peripheral balloon 460 is effected, preferably by use of a syringe 540 communicating with second lumen 406 via passageway 466 in head element 450 , stopcock 462 and associated conduit 464 .
  • the anchor balloon 440 is deflated, preferably by operation of syringe 520 , communicating with first lumen 404 via passageway 446 in head element 450 , stopcock 442 and associated conduit 444 , and the peripheral balloon 460 remains fully inflated, which preferably causes the extreme end of the main shaft 402 to be withdrawn from the artery 500 to a location lying just outside the artery wall.
  • peripheral balloon 460 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 440 is deflated. This volume of blood is located in a region, indicated by reference numeral 550 , delimited by the engagement of peripheral balloon 460 with the artery wall.
  • a coagulant agent is preferably supplied to the volume of blood at region 550 , between the balloon 460 and the outer surface of artery 500 .
  • the coagulant agent is supplied to region 550 by conduit 470 from a supply of coagulant agent 552 via stopcock 474 and associated conduit 476 , as shown in FIG. 7H .
  • the peripheral balloon 460 is deflated, as shown in FIGS. 7I and 8A , preferably by operation of syringe 540 , communicating with second lumen 406 via passageway 466 in head element 450 , stopcock 462 and associated conduit 464 .
  • the hemostasis device 400 is entirely withdrawn from the patient, leaving a region 560 of hemostasis outside of artery 500 , as shown in FIG. 7J .
  • FIGS. 9A, 9B , 9 C, 9 D, 9 E, 9 F, 9 G, 9 H, 9 I and 9 J are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context
  • FIGS. 10A, 10B , 10 C and 10 D are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 9A shows a hemostasis device 600 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention.
  • the hemostasis device 600 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 600 comprises a main shaft 602 , which has first and second lumens 604 and 606 .
  • First lumen 604 extends along the main shaft 602 to an anchor balloon inflation location 612 .
  • Second lumen 606 extends along the shaft 602 to a peripheral balloon inflation location 622 .
  • Anchor balloon 640 Disposed at an end of main shaft 602 at anchor balloon inflation location 612 is an anchor balloon 640 .
  • Anchor balloon 640 is selectably inflated, as shown in FIGS. 10A-10D , via a stopcock 642 and associated conduit 644 in fluid communication with main shaft 602 via a passageway 646 formed in a head element 650 .
  • Head element 650 is fixed to main shaft 602 at an end thereof opposite the end at which anchor balloon 640 is located.
  • Peripheral balloon 660 Disposed adjacent the end of main shaft 602 in fluid communication with peripheral balloon inflation location 622 , exterior of an outer wall 652 thereof, is a peripheral balloon 660 .
  • Peripheral balloon 660 is selectably inflated, as shown in FIGS. 10A-10D , via second lumen 606 , via a stopcock 662 and associated conduit 664 that communicate with second lumen 606 via a passageway 666 formed in head element 650 .
  • an electrical resistance heating element 680 is disposed interiorly of the anchor balloon 640 .
  • the resistance heating element 680 is formed of a foil or a wire which is electrically coupled at opposite ends thereof to electrical conductors which extend through the main shaft 602 .
  • a first conductor 682 is attached to a first end 684 of resistance heating element 680 and preferably extends through the first lumen 604
  • a second conductor 686 is attached to a second end 688 of resistance heating element 680 and extends through the second lumen 606 .
  • Resistance heating element 680 Electrical power is supplied to resistance heating element 680 via a switch 690 , which couples first conductor 682 and second conductor 686 to a source of electrical power. Heating of resistance heating element 680 enhances hemostasis at the aperture in the artery.
  • FIG. 9B illustrates the hemostasis device 600 about to be inserted into an artery 700 via a conventional catheter introducer assembly 702 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 702 .
  • the catheter introducer assembly 702 conventionally includes a catheter introducer sheath 704 .
  • FIG. 9C shows the hemostasis device 600 inserted into the catheter introducer assembly 702 such that the outer end of the main shaft 602 extends into the artery 700 well beyond the end of catheter introducer sheath 704 .
  • both anchor balloon 640 and peripheral balloon 660 are deflated, as seen clearly in FIG. 10A .
  • FIG. 9D shows initial inflation of the anchor balloon 640 , preferably by use of a syringe 720 , communicating with first lumen 604 via passageway 646 extending through the interior of head element 650 , stopcock 642 and associated conduit 644 .
  • the inflated anchor balloon 640 preferably has a cusp-type configuration as seen with particularity in FIGS. 9D and 10B .
  • the catheter introducer assembly 702 and the hemostasis device 600 are both withdrawn, such that the catheter introducer sheath 704 is removed from artery 700 only when the anchor balloon 640 already engages the interior wall of artery 700 in sealing engagement with the aperture in the artery 700 through which the catheter introducer sheath 704 is withdrawn and through which the main shaft 602 presently extends. This stage is shown in FIG. 9E .
  • initial inflation of the peripheral balloon 660 is effected, preferably by use of a syringe 740 communicating with second lumen 606 via passageway 666 in head element 650 , stopcock 662 and associated conduit 664 .
  • the anchor balloon 640 is deflated, preferably by operation of syringe 720 , communicating with first lumen 604 via passageway 646 in head element 650 , stopcock 642 and associated conduit 644 , and the peripheral balloon 660 remains fully inflated, which preferably causes the extreme end of the main shaft 602 to be withdrawn from the artery 700 to a location lying just outside the artery wall.
  • peripheral balloon 660 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 640 is deflated. This volume of blood is located in a region, indicated by reference numeral 750 , delimited by the engagement of peripheral balloon 660 with the artery wall.
  • heating of the electrical resistance heating element 680 is effected, preferably by an operator closing switch 690 , as shown in FIG. 9H .
  • This heating preferably continues for less than five minutes.
  • the peripheral balloon 660 is deflated, as shown in FIGS. 9I and 10A , preferably by operation of syringe 740 , communicating with second lumen 606 via passageway 666 in head element 650 , stopcock 662 and associated conduit 664 .
  • the hemostasis device 600 is entirely withdrawn from the patient, leaving a region 760 of hemostasis outside of artery 700 , as shown in FIG. 9J .
  • FIGS. 11A, 11B , 11 C, 11 D, 11 E, 11 F, 11 G, 11 H, 11 I and 11 J are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 12A, 12B , 12 C and 12 D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 11A shows a hemostasis device 800 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention.
  • the hemostasis device 800 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 800 comprises a main shaft 802 , which has first and second lumens 804 and 806 .
  • First lumen 804 extends along the main shaft 802 to an anchor balloon inflation location 812 .
  • Second lumen 806 extends along the shaft 802 to a peripheral balloon inflation location 822 .
  • Anchor balloon 840 Disposed at an end of main shaft 802 at anchor balloon inflation location 812 is an anchor balloon 840 .
  • Anchor balloon 840 is selectably inflated, as shown in FIGS. 12A-12D , via a stopcock 842 and associated conduit 844 in fluid communication with main shaft 802 via a passageway 846 formed in a head element 850 .
  • Head element 850 is fixed to main shaft 802 at an end thereof opposite the end at which anchor balloon 840 is located.
  • peripheral balloon 860 Disposed adjacent the end of main shaft 802 in fluid communication with peripheral balloon inflation location 822 , exterior of an outer wall 852 thereof, is a peripheral balloon 860 .
  • Peripheral balloon 860 is selectably inflated, as shown in FIGS. 12A-12D , via second lumen 806 , via a stopcock 862 and associated conduit 864 that communicate with second lumen 806 via a passageway 866 formed in head element 850 .
  • a pair of mutually spaced electrodes 880 is disposed interiorly of the anchor balloon 840 .
  • electrodes 880 are disposed exteriorly of anchor balloon 840 .
  • the electrodes 880 are each formed to have a configuration of a ball or knob and are each electrically coupled to a corresponding electrical conductor which extend through the main shaft 802 .
  • a first conductor 882 which preferably extends through the first lumen 804 , is attached to a first electrode 880 and a second conductor 884 is attached to a second electrode 880 and extends through the second lumen 806 .
  • Electrodes 880 Electrical power is supplied to electrodes 880 via a switch, which couples first conductor 882 and second conductor 884 to an RF power source 890 . Heating of electrodes 880 enhances hemostasis at the aperture in the artery.
  • Electrodes 880 may be employed. If only a single electrode 880 is provided, a suitable reference electrode (not shown) is preferably associated with a patient's body, such as underlying the patient.
  • FIG. 11B illustrates the hemostasis device 800 about to be inserted into an artery 900 via a conventional catheter introducer assembly 902 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 902 .
  • the catheter introducer assembly 902 conventionally includes a catheter introducer sheath 904 .
  • FIG. 11C shows the hemostasis device 800 inserted into the catheter introducer assembly 902 such that the outer end of the main shaft 802 extends into the artery 900 well beyond the end of catheter introducer sheath 904 .
  • both anchor balloon 840 and peripheral balloon 860 are deflated, as seen clearly in FIG. 12A .
  • FIG. 11D shows initial inflation of the anchor balloon 840 , preferably by use of a syringe 920 , communicating with first lumen 804 via passageway 846 extending through the interior of head element 850 , stopcock 842 and associated conduit 844 .
  • the inflated anchor balloon 840 preferably has a cusp-type configuration as seen with particularity in FIGS. 11D and 12B .
  • the catheter introducer assembly 902 and the hemostasis device 800 are both withdrawn, such that the catheter introducer sheath 904 is removed from artery 900 only when the anchor balloon 840 already engages the interior wall of artery 900 in sealing engagement with the aperture in the artery 900 through which the catheter introducer sheath 904 is withdrawn and through which the main shaft 802 presently extends.
  • This stage is shown in FIG. 11E .
  • initial inflation of the peripheral balloon 860 is effected, preferably by use of a syringe 940 communicating with second lumen 806 via passageway 866 in head element 850 , stopcock 862 and associated conduit 864 .
  • the anchor balloon 840 is deflated, preferably by operation of syringe 920 , communicating with first lumen 804 via passageway 846 in head element 850 , stopcock 842 and associated conduit 844 , and the peripheral balloon 860 remains fully inflated, which preferably causes the extreme end of the main shaft 802 to be withdrawn from the artery 900 to a location lying just outside the artery wall.
  • peripheral balloon 860 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 840 is deflated. This volume of blood is located in a region, indicated by reference numeral 950 , delimited by the engagement of peripheral balloon 860 with the artery wall.
  • heating of the electrode or electrodes 880 is effected, preferably by an operator closing the switch coupling the first conductor 882 and the second conductor 884 to RF power source 890 , as seen in FIG. 11H .
  • This heating preferably continues for less than five minutes.
  • the peripheral balloon 860 is deflated, as shown in FIGS. 11I and 12A , preferably by operation of syringe 940 , communicating with second lumen 806 via passageway 866 in head element 850 , stopcock 862 and associated conduit 864 .
  • the hemostasis device 800 is entirely withdrawn from the patient, leaving a region 960 of hemostasis outside of artery 900 , as shown in FIG. 11J .
  • FIGS. 13A, 13B , 13 C, 13 D, 13 E, 13 F, 13 G, 13 H, 13 I and 13 J are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 14A, 14B , 14 C and 14 D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 13A shows a hemostasis device 1000 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention.
  • the hemostasis device 1000 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 1000 comprises a main shaft 1002 , which has first and second lumens 1004 and 1006 .
  • First lumen 1004 extends along the main shaft 1002 to an anchor balloon inflation location 1012 .
  • Second lumen 1006 extends along the shaft 1002 to a peripheral balloon inflation location 1022 .
  • Anchor balloon 1040 Disposed at an end of main shaft 1002 at anchor balloon inflation location 1012 is an anchor balloon 1040 .
  • Anchor balloon 1040 is selectably inflated, as shown in FIGS. 14A-14D , via a stopcock 1042 and associated conduit 1044 in fluid communication with main shaft 1002 via a passageway 1046 formed in a head element 1050 .
  • Head element 1050 is fixed to main shaft 1002 at an end thereof opposite the end at which anchor balloon 1040 is located.
  • peripheral balloon 1060 Disposed adjacent the end of main shaft 1002 in fluid communication with peripheral balloon inflation location 1022 , exterior of an outer wall 1052 thereof, is a peripheral balloon 1060 .
  • Peripheral balloon 1060 is selectably inflated, as shown in FIGS. 14A-14D , via second lumen 1006 , via a stopcock 1062 and associated conduit 1064 that communicate with second lumen 1006 via a passageway 1066 formed in head element 1050 .
  • a coagulant agent supply conduit 1070 extends through the first lumen 1004 and through a bore 1072 formed along the length of head element 1050 .
  • Coagulant agent supply conduit 1070 communicates at one end thereof with a volume defined by inflation of the peripheral balloon 1060 , between the balloon 1060 and the outer surface of an adjacent artery (not shown).
  • conduit 1070 communicates with a supply of coagulant agent (not shown) via a stopcock 1074 and associated conduit 1076 .
  • an electrical resistance heating element 1080 is disposed interiorly of the anchor balloon 1040 .
  • the resistance heating element 1080 is formed of a foil or a wire which is electrically coupled at opposite ends thereof to electrical conductors which extend through the main shaft 1002 .
  • a first conductor, attached to a first end 1084 of resistance heating element 1080 is defined by or on the coagulant agent supply conduit 1070 , which preferably extends through the first lumen 1004
  • a second conductor 1086 is attached to a second end 1088 of resistance heating element 1080 and extends through the second lumen 1006 .
  • Resistance heating element 1080 Electrical power is supplied to resistance heating element 1080 via a switch 1090 , which couples the first conductor, defined by conduit 1070 , and second conductor 1086 to a source of electrical power. Heating of resistance heating element 1080 enhances hemostasis at the aperture in the artery.
  • the operation of the resistance heating element 1080 as aforesaid is advantageously combined in this embodiment with the provision of a coagulation agent as described hereinabove.
  • FIG. 13B illustrates the hemostasis device 1000 about to be inserted into an artery 1100 via a conventional catheter introducer assembly 1102 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 1102 .
  • the catheter introducer assembly 1102 conventionally includes a catheter introducer sheath 1104 .
  • FIG. 13C shows the hemostasis device 1000 inserted into the catheter introducer assembly 1102 such that the outer end of the main shaft 1002 extends into the artery 1100 well beyond the end of catheter introducer sheath 1104 .
  • both anchor balloon 1040 and peripheral balloon 1060 are deflated, as seen clearly in FIG. 14A .
  • FIG. 13D shows initial inflation of the anchor balloon 1040 , preferably by use of a syringe 1120 , communicating with first lumen 1004 via passageway 1046 extending through the interior of head element 1050 , stopcock 1042 and associated conduit 1044 .
  • the inflated anchor balloon 1040 preferably has a cusp-type configuration as seen with particularity in FIGS. 13D and 14B .
  • the catheter introducer assembly 1102 and the hemostasis device 1000 are both withdrawn, such that the catheter introducer sheath 1104 is removed from artery 1100 only when the anchor balloon 1040 already engages the interior wall of artery 1100 in sealing engagement with the aperture in the artery 1100 through which the catheter introducer sheath 1104 is withdrawn and through which the main shaft 1002 presently extends. This stage is shown in FIG. 13E .
  • initial inflation of the peripheral balloon 1060 is effected, preferably by use of a syringe 1140 communicating with second lumen 1006 via passageway 1066 in head element 1050 , stopcock 1062 and associated conduit 1064 .
  • the anchor balloon 1040 is deflated, preferably by operation of syringe 1120 , communicating with first lumen 1004 via passageway 1046 in head element 1050 , stopcock 1042 and associated conduit 1044 , and the peripheral balloon 1060 remains fully inflated, which preferably causes the extreme end of the main shaft 1002 to be withdrawn from the artery 1100 to a location lying just outside the artery wall.
  • peripheral balloon 1060 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 1040 is deflated. This volume of blood is located in a region, indicated by reference numeral 1150 , delimited by the engagement of peripheral balloon 1060 with the artery wall.
  • a coagulant agent is preferably supplied to the volume of blood at region 1150 , between the balloon 1060 and the outer surface of artery 1100 .
  • the coagulant agent is supplied to region 1150 by conduit 1070 from a supply of coagulant agent 1152 via stopcock 1074 and associated conduit 1076 , as shown in FIG. 13H .
  • heating of the electrical resistance heating element 1080 is effected, preferably by an operator closing switch 1090 .
  • This heating preferably continues for less than five minutes.
  • the peripheral balloon 1060 is deflated, as shown in FIGS. 13I and 14A , preferably by operation of syringe 1140 , communicating with second lumen 1006 via passageway 1066 in head element 1050 , stopcock 1062 and associated conduit 1064 .
  • the hemostasis device 1000 is entirely withdrawn from the patient, leaving a region 1160 of hemostasis outside of artery 1100 , as shown in FIG. 13J .
  • FIGS. 15A, 15B , 15 C, 15 D, 15 E, 15 F, 15 G, 15 H, 15 I and 15 J are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 16A, 16B , 16 C and 16 D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 15A shows a hemostasis device 1200 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention.
  • the hemostasis device 1200 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • hemostasis device 1200 comprises a main shaft 1202 , which has first and second lumens 1204 and 1206 .
  • First lumen 1204 extends along the main shaft 1202 to an anchor balloon inflation location 1212 .
  • Second lumen 1206 extends along the shaft 1202 to a peripheral balloon inflation location 1222 .
  • Anchor balloon 1240 Disposed at an end of main shaft 1202 at anchor balloon inflation location 1212 is an anchor balloon 1240 .
  • Anchor balloon 1240 is selectably inflated, as shown in FIGS. 16A-16D , via a stopcock 1242 and associated conduit 1244 in fluid communication with main shaft 1202 via a passageway 1246 formed in a head element 1250 .
  • Head element 1250 is fixed to main shaft 1202 at an end thereof opposite the end at which anchor balloon 1240 is located.
  • peripheral balloon 1260 Disposed adjacent the end of main shaft 1202 in fluid communication with peripheral balloon inflation location 1222 , exterior of an outer wall 1252 thereof, is a peripheral balloon 1260 .
  • Peripheral balloon 1260 is selectably inflated, as shown in FIGS. 16A-16D , via second lumen 1206 , via a stopcock 1262 and associated conduit 1264 that communicate with second lumen 1206 via a passageway 1266 formed in head element 1250 .
  • a coagulant agent supply conduit 1270 extends through the first lumen 1204 and through a bore 1272 formed in head element 1250 .
  • Coagulant agent supply conduit 1270 communicates at one end thereof, via a coagulant agent aperture 1273 , with a volume defined by inflation of the peripheral balloon 1260 , between the balloon 1260 and the outer surface of an adjacent artery (not shown).
  • conduit 1270 communicates with a supply of coagulant agent (not shown) via a stopcock 1274 and associated conduit 1276 .
  • Coagulant agent aperture 1273 is clearly shown in FIGS. 16A-16D .
  • a pair of mutually spaced electrodes 1280 is disposed interiorly of the anchor balloon 1240 .
  • electrodes 1280 are disposed exteriorly of anchor balloon 1240 .
  • the electrodes 1280 are each formed to have a configuration of a ball or knob and are each electrically coupled to a corresponding electrical conductor which extend through the main shaft 1202 .
  • a first conductor, attached to a first electrode 1280 is defined by or on the coagulant agent supply conduit 1270 , which preferably extends through the first lumen 1204
  • a second conductor 1286 is attached to a second electrode 1280 and extends through the second lumen 1206 .
  • Electrodes 1280 Electrical power is supplied to electrodes 1280 via a switch, which couples the first conductor and the second conductor 1286 to an RF power source 1290 . Heating of electrodes 1280 enhances hemostasis at the aperture in the artery.
  • the operation of the electrodes 1280 as aforesaid is advantageously combined in this embodiment with the provision of a coagulation agent as described hereinabove.
  • Electrodes 1280 may be employed. If only a single electrode 1280 is provided, a suitable reference electrode (not shown) is preferably associated with a patient's body, such as underlying the patient.
  • FIGS. 15B-15J illustrate various steps in a preferred mode of operation of the apparatus of FIG. 15A .
  • FIG. 15B illustrates the hemostasis device 1200 about to be inserted into an artery 1300 via a conventional catheter introducer assembly 1302 , following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 1302 .
  • the catheter introducer assembly 1302 conventionally includes a catheter introducer sheath 1304 .
  • FIG. 15C shows the hemostasis device 1200 inserted into the catheter introducer assembly 1302 such that the outer end of the main shaft 1202 extends into the artery 1300 well beyond the end of catheter introducer sheath 1304 .
  • both anchor balloon 1240 and peripheral balloon 1260 are deflated, as seen clearly in FIG. 16A .
  • FIG. 15D shows initial inflation of the anchor balloon 1240 , preferably by use of a syringe 1320 , communicating with first lumen 1204 via passageway 1246 extending through the interior of head element 1250 , stopcock 1242 and associated conduit 1244 .
  • the inflated anchor balloon 1240 preferably has a cusp-type configuration as seen with particularity in FIGS. 15D and 16B .
  • the catheter introducer assembly 1302 and the hemostasis device 1200 are both withdrawn, such that the catheter introducer sheath 1304 is removed from artery 1300 only when the anchor balloon 1240 already engages the interior wall of artery 1300 in sealing engagement with the aperture in the artery 1300 through which the catheter introducer sheath 1304 is withdrawn and through which the main shaft 1202 presently extends.
  • This stage is shown in FIG. 15E .
  • initial inflation of the peripheral balloon 1260 is effected, preferably by use of a syringe 1340 communicating with second lumen 1206 via passageway 1266 in head element 1250 , stopcock 1262 and associated conduit 1264 .
  • the anchor balloon 1240 is deflated, preferably by operation of syringe 1320 , communicating with first lumen 1204 via passageway 1246 in head element 1250 , stopcock 1242 and associated conduit 1244 , and the peripheral balloon 1260 remains fully inflated, which preferably causes the extreme end of the main shaft 1202 to be withdrawn from the artery 1300 to a location lying just outside the artery wall.
  • peripheral balloon 1260 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 1240 is deflated. This volume of blood is located in a region, indicated by reference numeral 1350 , delimited by the engagement of peripheral balloon 1260 with the artery wall.
  • a coagulant agent is preferably supplied to the volume of blood at region 1350 , between the balloon 1260 and the outer surface of artery 1300 .
  • the coagulant agent is supplied to region 1350 by conduit 1270 , via coagulant agent aperture 1273 from a supply of coagulant agent 1352 via stopcock 1274 and associated conduit 1276 , as shown in FIG. 15H .
  • heating of the electrode or electrodes 1280 is effected, preferably by an operator closing the switch coupling the first conductor and the second conductor 1286 to RF power source 1290 , as seen in FIG. 15H .
  • This heating preferably continues for less than five minutes.
  • the peripheral balloon 1260 is deflated, as shown in FIGS. 15I and 16A , preferably by operation of syringe 1340 , communicating with second lumen 1206 via passageway 1266 in head element 1250 , stopcock 1262 and associated conduit 1264 .
  • the hemostasis device 1200 is entirely withdrawn from the patient, leaving a region 1360 of hemostasis outside of artery 1300 , as shown in FIG. 15J .

Abstract

A hemostasis device including a resistance heating element for accelerating hemostasis, a blood resistance sensor and a blood resistance indicator, operative to provide an indication of the resistance at the resistance sensor of blood undergoing hemostasis.

Description

    CROSS REFERENCE TO RELATED APPLICATIONS
  • This application claims the priority of U.S. application Ser. No. 10/358,130, filed Feb. 4, 2003, titled “METHODS AND APPARATUS FOR HEMOSTASIS FOLLOWING ARTERIAL CATHETERIZATION”, and U.S. application Ser. No. 10/616,887, filed Jul. 10, 2003, titled “METHODS AND APPARATUS FOR HEMOSTASIS FOLLOWING ARTERIAL CATHETERIZATION”.
  • FIELD OF THE INVENTION
  • The present invention relates to catheterization systems and methodologies generally and more particularly to post-catheterization closure.
  • BACKGROUND OF THE INVENTION
  • Various techniques are known for arterial catheterization. Following arterial catheterization, it is necessary to promote hemostasis quickly and without undue hardship for the patient.
  • Applicant's U.S. Pat. Nos. 5,728,134 and 6,048,358, and Published PCT Patent Applications WO 98/11830 and WO 00/02488 describe methods and apparatus for hemostasis that greatly simplify hemostasis and thus greatly reduce patient discomfort following arterial catheterization. These patent documents, the disclosures of which are hereby incorporated by reference, and the prior art referenced therein are considered to represent the state of the art.
  • SUMMARY OF THE INVENTION
  • The present invention seeks to provide improved systems and methodologies for post-catheterization closure.
  • There is thus provided in accordance with a preferred embodiment of the present invention a hemostasis device including a resistance heating element for accelerating hemostasis, a blood resistance sensor and a blood resistance indicator, operative to provide an indication of the resistance at the resistance sensor of blood undergoing hemostasis.
  • In accordance with another preferred embodiment of the present invention the hemostasis device also includes a power supply connected to the resistance heating element, the resistance sensor and the resistance indicator. Additionally, the power supply is operative to supply a relatively high level current to the resistance heating element. Alternatively, the power supply is operative to supply a relatively low level current to the resistance sensor.
  • There is also provided in accordance with another preferred embodiment of the present invention a method for accelerating hemostasis of an artery of a patient having a puncture after arterial catheterization, the method including the steps of following arterial catheterization, introducing a hemostasis device, such that a forward end of the hemostasis device lies exterior of the artery adjacent the puncture, accelerating hemostasis by heating tissue in the vicinity of the puncture, thereby shortening the time required for hemostasis and following hemostasis, removing the hemostasis device from the patient.
  • In accordance with another preferred embodiment of the present invention the method also includes inserting a catheter introducer into the artery prior to the arterial catheterization and wherein following the arterial catheterization, the hemostasis device is introduced through the catheter introducer. In accordance with yet another preferred embodiment of the present invention the method also includes measuring the conductivity of blood in the vicinity of the puncture during hemostasis.
  • There is further provided in accordance with another preferred embodiment of the present invention a method for monitoring the progress of hemostasis of an artery of a patient having a puncture after arterial catheterization, the method including the steps of following arterial catheterization, introducing a hemostasis device, such that a forward end of the hemostasis device lies exterior of the artery adjacent the puncture, during hemostasis, measuring the heat conductivity of blood in the vicinity of the puncture, thereby to provide an output indication of the progress of hemostasis and following hemostasis, removing the hemostasis device from the patient.
  • In accordance with another preferred embodiment of the present invention the method also includes the step of inserting into an artery a catheter introducer prior to arterial catheterization and wherein following the arterial catheterization, the hemostasis device is introduced through the catheter introducer.
  • In accordance with yet another preferred embodiment of the present invention the method also includes inflating a balloon to block the puncture, prior to the hemostasis. Additionally, the method also includes deflating the balloon prior to removing the hemostasis device.
  • There is still further provided in accordance with another preferred embodiment of the present invention a hemostasis device including a main shaft, at least one balloon mounted on the main shaft and at least one electrode, mounted on the main shaft and being operable to supply an electric current suitable for causing hemostasis.
  • In accordance with another preferred embodiment of the present invention the at least one balloon includes at least one anchor balloon, disposed at an end of the main shaft and at least one peripheral balloon, disposed at a location along the main shaft exterior to a wall of the main shaft. In accordance with still another preferred embodiment of the present invention the at least one peripheral balloon and a wall of an artery are configured to delimit a region which is subject to hemostasis.
  • In accordance with yet another preferred embodiment of the present invention the hemostasis device also includes an electrical power source and a control module. In accordance with another preferred embodiment of the present invention the power source is an RF power supply. Preferably, the RF power supply is operative to supply electrical power at RF frequencies within a range of 0.1-10 watts at up to 25 volts. In accordance with another preferred embodiment of the present invention the control module is operative to measure at least one of electrical current, blood resistance and blood temperature. Additionally or alternatively, the control module is operative to adjust the power supplied by the power source based on at least one measurement.
  • In accordance with still another preferred embodiment of the present invention the at least one electrode includes a pair of electrodes.
  • There is even further provided in accordance with another preferred embodiment of the present invention a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one electrode into the vicinity of the puncture, supplying an electric current to the at least one electrode, thereby heating a volume of blood in the vicinity of the puncture, causing hemostasis and subsequently removing the hemostasis device from the patient.
  • In accordance with another preferred embodiment of the present invention introducing includes introducing via a catheter introducer. Additionally or alternatively, the introducing also includes inflating an anchor balloon attached to an end of the hemostasis device. In accordance with another preferred embodiment of the present invention the introducing includes inflating a peripheral balloon. Additionally, the removing the hemostasis device includes deflating the peripheral balloon.
  • In accordance with still another preferred embodiment of the present invention the introducing includes positioning the at least one electrode in close proximity to a volume of blood.
  • In accordance with another preferred embodiment of the present invention the supplying includes supplying electrical power at RF frequencies. Additionally, the electrical power includes electrical power in the range of 0.1-10 watts at up to 25 volts. Alternatively or additionally, the supplying also includes adjusting the electric current based on a feedback measurement.
  • There is also provided in accordance with yet another preferred embodiment of the present invention a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at the end of the main shaft beyond the at least one balloon.
  • In accordance with another preferred embodiment of the present invention the hemostasis device also includes at least one heating assembly operative to provide heating at the location. In accordance with still another preferred embodiment of the present invention the at least one heating assembly includes at least one electrode disposed adjacent the location. In accordance with another preferred embodiment of the present invention the at least one electrode is disposed interiorly of the at least one balloon. Alternatively, the at least one electrode is disposed exteriorly of the at least one balloon. In accordance with yet another preferred embodiment of the present invention the at least one heating assembly includes an electrical resistive heating element. In accordance with still another preferred embodiment of the present invention the electrical resistive heating element is disposed within the at least one balloon.
  • There is further provided in accordance with still another preferred embodiment of the present invention a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and at least one RF electrode located at a location at an end of the main shaft beyond the at least one balloon.
  • In accordance with another preferred embodiment of the present invention the hemostasis device also includes a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of the main shaft beyond the at least one balloon.
  • In accordance with yet another preferred embodiment of the present invention the at least one RF electrode is disposed interiorly of the at least one balloon. Alternatively, the at least one RF electrode is disposed exteriorly of the at least one balloon.
  • There is even further provided in accordance with yet another preferred embodiment of the present invention a hemostasis device including a main shaft, at least one balloon mounted on the main shaft adjacent an end thereof and at least one resistive heating element located at a location at an end of the main shaft beyond the at least one balloon.
  • In accordance with another preferred embodiment of the present invention the hemostasis device also includes a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of the main shaft beyond the at least one balloon.
  • In accordance with yet another preferred embodiment of the present invention the at least one resistance heating element is disposed interiorly of the at least one balloon.
  • There is still further provided in accordance with another preferred embodiment of the present invention a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon.
  • In accordance with still another preferred embodiment of the present invention the method also includes providing heating at the location. In accordance with another preferred embodiment of the present invention the providing heating includes locating at least one electrode adjacent the location. Additionally, the at least one electrode is disposed interiorly of the at least one balloon. Alternatively, the at least one electrode is disposed exteriorly of the at least one balloon. In accordance with yet another preferred embodiment of the present invention the providing heating includes providing electrical resistive heating.
  • There is also provided in accordance with another preferred embodiment of the present invention a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and operating at least one RF electrode at the location at the end of the main shaft beyond the at least one balloon.
  • In accordance with another preferred embodiment of the present invention the method also includes supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon. In accordance with yet another preferred embodiment of the present invention the at least one RF electrode is disposed interiorly of the at least one balloon. Alternatively, the at least one RF electrode is disposed exteriorly of the at least one balloon.
  • There is further provided in accordance with yet another preferred embodiment of the present invention a method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization including introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of the puncture and operating at least one resistance heating element at the location at an end of the shaft beyond the at least one balloon.
  • In accordance with another preferred embodiment of the present invention the method also includes supplying a hemostasis agent to the location at the end of the shaft beyond the at least one balloon.
  • In accordance with still another preferred embodiment of the present invention the at least one resistance heating element is disposed interiorly of the at least one balloon.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • The present invention will be understood and appreciated more fully from the following detailed description, taken in conjunction with the drawings in which:
  • FIGS. 1A and 1B are simplified pictorial illustrations of respective first and second modes of operation of a hemostasis device constructed and operative in accordance with a preferred embodiment of the present invention;
  • FIG. 2 is a simplified pictorial illustration of the hemostasis device of FIGS. 1A and 1B during hemostasis;
  • FIGS. 3A and 3B are graphs illustrating the typical conductivity levels measured by the hemostasis device when used in the operating modes shown in FIGS. 1A and 1B, respectively;
  • FIG. 4 is a simplified illustration of a hemostasis device constructed and operative in accordance with a preferred embodiment of the present invention;
  • FIGS. 5A, 5B, 5C, 5D, 5E, 5F, 5G, 5H and 5I are simplified illustrations of the operation of the apparatus of FIG. 4 in a patient treatment context;
  • FIG. 6 is a simplified illustration of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention;
  • FIGS. 7A, 7B, 7C, 7D, 7E, 7F, 7G, 7H, 7I and 7J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 8A, 8B, 8C and 8D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 7A-7J;
  • FIGS. 9A, 9B, 9C, 9D, 9E, 9F, 9G, 9H, 9I and 9J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 10A, 10B, 10C and 10D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 9A-9J;
  • FIGS. 11A, 11B, 11C, 11D, 11E, 11F, 11G, 11H, 11I and 11J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 12A, 12B, 12C and 12D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 11A-11J;
  • FIGS. 13A, 13B, 13C, 13D, 13E, 13F, 13G, 13H, 13I and 13J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context;
  • FIGS. 14A, 14B, 14C and 14D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 13A-13J;
  • FIGS. 15A, 15B, 15C, 15D, 15E, 15F, 15G, 15H, 15I and 15J are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context; and
  • FIGS. 16A, 16B, 16C and 16D are simplified illustrations of four different states of inflation of the hemostasis device of FIGS. 15A-15J.
  • DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
  • Reference is now made to FIGS. 1A and 1B, which are simplified pictorial illustrations of a preferred embodiment of a hemostasis device in respective first and second modes of operation.
  • As seen in FIG. 1A, a hemostasis device 10 is inserted into a catheter introducer 11, following arterial catheterization and withdrawal of a catheter (not shown), such that a forward end 12 of the hemostasis device 10 lies adjacent to and outside a puncture 14 in an artery 16. At least one external balloon 18 is preferably disposed adjacent catheter introducer 11 and is shown in an inflated orientation, wherein the balloon 18 forms a skirt surrounding and sealing puncture 14 from the tissue external thereto. At this stage blood normally fills artery 16 as well as puncture 14, as well as the annular volume 20 surrounded by balloon 18 adjacent puncture 14 and forward end 12.
  • In accordance with another preferred embodiment of the present invention, the at least one balloon 18 need not be provided.
  • In accordance with a preferred embodiment of the present invention, a resistance element 22 is disposed at a forward edge 24 of the forward end 12, and is coupled in series with an external power supply 26 via conductors 28, which typically extend along the length of the hemostasis device 10. Preferably, the series connection includes a resistance indicator 30, which provides an indication of the resistance at a resistance sensor 32.
  • As seen in FIG. 1A, a low level current, typically less than 0.1 ampere, is provided by external power supply 26 to enable the resistance indicator 30 to monitor the progress of hemostasis, to allow for timely removal of catheter introducer 11 and hemostasis device 10 from the patient.
  • It is appreciated that the heat conductivity of the blood in liquid form is measurably different from that of a blood clot formed during hemostasis, as will be described hereinbelow with reference to FIGS. 3A and 3B.
  • FIG. 1B illustrates the hemostasis device of FIG. 1A in a second preferred mode of operation. As shown in FIG. 1B, a high level electrical current, typically greater than 0.1 ampere, is supplied via the external power supply 26 to resistance element 22. The provision of this current causes heating of the blood adjacent to the resistance element 22 and provides for accelerated hemostasis. The provision of resistance indicator 30, connected to resistance sensor 32, enables the monitoring of the progress of the accelerated hemostasis, to allow for regulation of the current provided to resistance element 22 over time, and to allow timely removal of catheter introducer 11 and hemostasis device 10 from the patient.
  • It is appreciated that the heat conductivity of the blood in liquid form is measurably different from that of a blood clot formed during hemostasis, as will be described hereinbelow with reference to FIGS. 3A and 3B.
  • Reference is now made to FIG. 2, which is a simplified pictorial illustration of hemostasis device 10 of FIGS. 1A and 1B during hemostasis.
  • FIG. 2 shows the hemostasis device 10 of FIGS. 1A and 1B and illustrates the different heat conductivity of the blood during the various stages of hemostasis. As seen in FIG. 2, the blood flowing through the artery 16 and adjacent the puncture 14 in the artery is in liquid form, where its heat conductivity is greater than that of the blood 40 which has begun to coagulate. Blood 40 is in a viscous form, which has a heat conductivity greater than that of the blood 42, which has already begun to solidify into a blood clot. Resistance sensor 32 is thus able to measure the process of coagulation by measuring the heat conductivity of the adjacent blood.
  • Reference is now made to FIGS. 3A and 3B, which are graphs illustrating the typical conductivity levels measured by the catheter introducer assembly when used in the operating modes shown in FIGS. 1A and 1B, respectively.
  • FIG. 3A shows the heat conductivity of the blood over time, in the mode of operation illustrated in FIG. 1A, where the blood is in a liquid form at time T0, with relatively high heat conductivity, where the heat conductivity decreases gradually over time as the blood forms a clot at time TH.
  • FIG. 3B shows the heat conductivity of the blood over time, in the mode of operation illustrated in FIG. 1B, where the blood is heated to accelerate clotting. As seen in FIG. 3B, the heat conductivity begins at time T0 in a liquid form with relatively high heat conductivity, which decreases rapidly as the blood is heated and the clotting occurs at an accelerated rate. FIG. 3B also shows the heat conductivity curve over time shown in FIG. 3A, which clearly illustrates the accelerated hemostasis described in reference to FIG. 1B hereinabove, where THA is the accelerated hemostasis time and TH is the non-accelerated hemostasis time.
  • Reference is now made to FIG. 4, which is a simplified illustration of a hemostasis device 100 for producing hemostasis following arterial catheterization, in accordance with a preferred embodiment of the present invention. The hemostasis device 100 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 100 comprises a main shaft 102, which has an outer wall 104 and preferably includes at least three bores. A first bore, designated generally by reference numeral 110, extends along the main shaft 102 to an anchor balloon inflation location 112. A second bore 120 extends along the shaft 102 to a peripheral balloon inflation location 122. A third bore, designated generally by reference number 130, contains an electrocoagulation heating device 132 connected to an electrical power source and control module 134 by a connector 136.
  • Disposed at an end of main shaft 102 at anchor balloon inflation location 112 is an anchor balloon 140. Anchor balloon 140 is selectably inflated at anchor balloon inflation location 112, as shown in FIG. 5C, via a stopcock 142 and associated conduit 144 in fluid communication with main shaft 102 via a passageway 146 formed in a head element 150. Head element 150 is fixed to main shaft 102 at an end thereof opposite the end at which anchor balloon 140 is located.
  • Disposed adjacent the end of second bore 120 in fluid communication with peripheral balloon inflation location 122, exterior of wall 104, is a peripheral balloon 160. Peripheral balloon 160 is selectably inflated at peripheral balloon inflation location 112, as shown in FIG. 5E, via second bore 120, via a stopcock 162 and associated conduit 164 that communicate with second bore 120 via a passageway 166 formed in head element 150.
  • In accordance with a preferred embodiment of the present invention, electrocoagulation heating device 132 comprises an electrical conductor 170 connected to an electrocoagulation electrode 176 at an extreme end 178 of third bore 130. A pair of electrical cables 180 and 182 extends from electrical power source and control module 134. In the illustrated embodiment, electrical cable 180 serves as a power supply cable and is connected to electrocoagulation heating device 132 by connector 136. Electrical cable 182 serves as a return current cable and is preferably connected to an electrode 184 attached to a body of a patient.
  • Electrical power source and control module 134 preferably comprises a power supply, preferably an RF power supply source 186, including a feedback measurement circuit 188. The feedback measurement circuit 188 is preferably operative to measure current, blood resistance or blood temperature and thereby determine progress of hemostasis. The electrical power source and control module 134 also preferably includes a microprocessor 190, operative to adjust the power supplied to hemostasis device 100 according to the blood temperature or other feedback measurement received from feedback measurement circuit 188, in order to achieve optimal coagulation of the blood.
  • In accordance with a preferred embodiment of the present invention an operator actuation switch 192 is connected along electrical cable 180. In accordance with another preferred embodiment, switch 192 may be obviated and electrical cable 180 connected directly to connector 136.
  • Reference is now made to FIGS. 5A-5I, which illustrate various steps in a preferred mode of operation of the apparatus of FIG. 4.
  • FIG. 5A illustrates the hemostasis device 100 about to be inserted into an artery 200 via a conventional catheter introducer assembly 202, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 202. The catheter introducer assembly 202 conventionally includes a catheter introducer sheath 204.
  • FIG. 5B shows the hemostasis device 100 inserted into the catheter introducer assembly 202 such that the outer end of the main shaft 102 extends into the artery 200 well beyond the end of catheter introducer sheath 204. As shown with particularity in FIG. 5B, at this stage both anchor balloon 140 and peripheral balloon 160 are deflated.
  • Reference is now made to FIG. 5C, which shows initial inflation of the anchor balloon 140, preferably by use of a syringe 220, communicating with first bore 110 via the interior of head element 150, stopcock 142 and associated conduit 144. The inflated anchor balloon 140 preferably has a cusp-type configuration as seen with particularity in FIG. 5C.
  • Following inflation of the anchor balloon 140, the catheter introducer assembly 202 and the hemostasis device 100 are both withdrawn, such that the catheter introducer sheath 204 is removed from artery 200 only when the anchor balloon 140 already engages the interior wall of artery 200 in sealing engagement with the aperture in the artery 200 through which the catheter introducer sheath 204 is withdrawn and through which the main shaft 102 presently extends. This stage is shown in FIG. 5D.
  • As seen in FIG. 5E, initial inflation of the peripheral balloon 160 is effected, preferably by use of a syringe 240 communicating with second bore 120 via head element 150, stopcock 162 and associated conduit 164.
  • Thereafter, as seen in FIG. 5F, the anchor balloon 140 is deflated, preferably by operation of syringe 220, communicating with first bore 110 via the interior of head element 150, stopcock 142 and associated conduit 144, and the peripheral balloon 160 is inflated, which preferably causes the extreme end of the main shaft 102 to be withdrawn from the artery 200 to a location lying just outside the artery wall. As seen in FIG. 5F, peripheral balloon 160 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 140 is deflated. This volume of blood is located in a region, indicated by reference numeral 250, delimited by the engagement of peripheral balloon 160 with the artery wall.
  • At this stage, electric power is supplied to the electrode 176 to provide heating of the blood in region 250, causing coagulation thereof, as seen in FIG. 5G. In accordance with the illustrated embodiment of FIG. 4 and as shown in FIG. 5G, the electric power is provided by actuation of switch 192. In accordance with another preferred embodiment, switch 192 is obviated, and the electric power is provided by connecting electrical cable 180 (FIG. 4) directly to connector 136.
  • Preferably, the amount of electrical power supplied along electrical cable 180 (FIG. 4) from electrical power source and control module 134 to the electrocoagulation electrode 176 is between 0.1-10 watts at up to 25 volts at RF frequencies.
  • Once acceptable hemostasis has occurred in region 250, the peripheral balloon 160 is deflated, as shown in FIG. 5H, preferably by operation of syringe 240 communicating with second bore 120 via head element 150, stopcock 162 and associated conduit 164.
  • Thereafter, the hemostasis device 100 is entirely withdrawn from the patient, leaving a region 260 of hemostasis outside of artery 200, as shown in FIG. 5I.
  • Reference is now made to FIG. 6, which is a simplified illustration of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention. The embodiment of FIG. 6 is similar to that of FIG. 4, except as described hereinbelow. Elements that occur in both embodiments are identified by the same reference numerals.
  • In the embodiment of FIG. 6, electrocoagulation heating device 132 comprises a pair of separate electrical conductors 300 extending along third bore 130 connecting electrical power source and control module 134 to a pair of electrocoagulation electrodes 302 at end 178 of third bore 130. Electrical cables 180 and 182 are both connected to electrocoagulation heating device 132 by connector 136. The illustrated embodiment shows connector 136 directly connected to electrical cables 180 and 182.
  • In the embodiment of FIG. 6, the electrodes 302 may be arranged in mutual coaxial arrangement or in mutual side-by-side arrangement or in any other suitable arrangement.
  • Reference is now made to FIGS. 7A, 7B, 7C, 7D, 7E, 7F, 7G, 7H, 7I and 7J, which are simplified illustrations of a hemostasis device constructed and operative in accordance with another preferred embodiment of the present invention and various stages of its operation in a patient treatment context, and to FIGS. 8A, 8B, 8C and 8D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 7A shows a hemostasis device 400 for producing hemostasis following arterial catheterization in accordance with another preferred embodiment of the present invention. The hemostasis device 400 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 400 comprises a main shaft 402, which has first and second lumens 404 and 406. First lumen 404 extends along the main shaft 402 to an anchor balloon inflation location 412. Second lumen 406 extends along the shaft 402 to a peripheral balloon inflation location 422.
  • Disposed at an end of main shaft 402 at anchor balloon inflation location 412 is an anchor balloon 440. Anchor balloon 440 is selectably inflated, as shown in FIGS. 8A-8D, via a stopcock 442 and associated conduit 444 in fluid communication with main shaft 402 via a passageway 446 formed in a head element 450. Head element 450 is fixed to main shaft 402 at an end thereof opposite the end at which anchor balloon 440 is located.
  • Disposed adjacent the end of main shaft 402, in fluid communication with peripheral balloon inflation location 422, exterior of an outer wall 452 thereof, is a peripheral balloon 460. Peripheral balloon 460 is selectably inflated, as shown in FIGS. 8A-8D, via second lumen 406, via a stopcock 462 and associated conduit 464 that communicate with second lumen 406 via a passageway 466 formed in head element 450.
  • In accordance with a preferred embodiment of the present invention, a coagulant agent supply conduit 470 extends through the first lumen 404 and through a bore 472 formed along the length of head element 450. Coagulant agent supply conduit 470 communicates at one end thereof with a volume defined by inflation of the peripheral balloon 460, between the balloon 460 and the outer surface of an adjacent artery (not shown). At its opposite end, conduit 470 communicates with a supply of coagulant agent (not shown) via a stopcock 474 and associated conduit 476.
  • FIGS. 7B-7J illustrate various steps in a preferred mode of operation of the apparatus of FIG. 7A. FIG. 7B illustrates the hemostasis device 400 about to be inserted into an artery 500 via a conventional catheter introducer assembly 502, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 502. The catheter introducer assembly 502 conventionally includes a catheter introducer sheath 504.
  • FIG. 7C shows the hemostasis device 400 inserted into the catheter introducer assembly 502 such that the outer end of the main shaft 402 extends into the artery 500 well beyond the end of catheter introducer sheath 504. As shown with particularity in FIG. 7C, at this stage both anchor balloon 440 and peripheral balloon 460 are deflated, as seen clearly in FIG. 8A.
  • Reference is now made to FIG. 7D, which shows initial inflation of the anchor balloon 440, preferably by use of a syringe 520, communicating with first lumen 404 via passageway 446 extending through the interior of head element 450, stopcock 442 and associated conduit 444. The inflated anchor balloon 440 preferably has a cusp-type configuration as seen with particularity in FIGS. 7D and 8B.
  • Following inflation of the anchor balloon 440, the catheter introducer assembly 502 and the hemostasis device 400 are both withdrawn, such that the catheter introducer sheath 504 is removed from artery 500 only when the anchor balloon 440 already engages the interior wall of artery 500 in sealing engagement with the aperture in the artery 500 through which the catheter introducer sheath 504 is withdrawn and through which the main shaft 402 presently extends. This stage is shown in FIG. 7E.
  • As seen in FIGS. 7F and 8C, initial inflation of the peripheral balloon 460 is effected, preferably by use of a syringe 540 communicating with second lumen 406 via passageway 466 in head element 450, stopcock 462 and associated conduit 464.
  • Thereafter, as seen in FIGS. 7G and 8D, the anchor balloon 440 is deflated, preferably by operation of syringe 520, communicating with first lumen 404 via passageway 446 in head element 450, stopcock 442 and associated conduit 444, and the peripheral balloon 460 remains fully inflated, which preferably causes the extreme end of the main shaft 402 to be withdrawn from the artery 500 to a location lying just outside the artery wall. As seen in FIG. 7G, peripheral balloon 460 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 440 is deflated. This volume of blood is located in a region, indicated by reference numeral 550, delimited by the engagement of peripheral balloon 460 with the artery wall.
  • At this stage, a coagulant agent is preferably supplied to the volume of blood at region 550, between the balloon 460 and the outer surface of artery 500. The coagulant agent is supplied to region 550 by conduit 470 from a supply of coagulant agent 552 via stopcock 474 and associated conduit 476, as shown in FIG. 7H.
  • Once acceptable hemostasis has occurred in region 550, the peripheral balloon 460 is deflated, as shown in FIGS. 7I and 8A, preferably by operation of syringe 540, communicating with second lumen 406 via passageway 466 in head element 450, stopcock 462 and associated conduit 464.
  • Thereafter, the hemostasis device 400 is entirely withdrawn from the patient, leaving a region 560 of hemostasis outside of artery 500, as shown in FIG. 7J.
  • Reference is now made to FIGS. 9A, 9B, 9C, 9D, 9E, 9F, 9G, 9H, 9I and 9J, which are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context, and to FIGS. 10A, 10B, 10C and 10D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 9A shows a hemostasis device 600 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention. The hemostasis device 600 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 600 comprises a main shaft 602, which has first and second lumens 604 and 606. First lumen 604 extends along the main shaft 602 to an anchor balloon inflation location 612. Second lumen 606 extends along the shaft 602 to a peripheral balloon inflation location 622.
  • Disposed at an end of main shaft 602 at anchor balloon inflation location 612 is an anchor balloon 640. Anchor balloon 640 is selectably inflated, as shown in FIGS. 10A-10D, via a stopcock 642 and associated conduit 644 in fluid communication with main shaft 602 via a passageway 646 formed in a head element 650. Head element 650 is fixed to main shaft 602 at an end thereof opposite the end at which anchor balloon 640 is located.
  • Disposed adjacent the end of main shaft 602 in fluid communication with peripheral balloon inflation location 622, exterior of an outer wall 652 thereof, is a peripheral balloon 660. Peripheral balloon 660 is selectably inflated, as shown in FIGS. 10A-10D, via second lumen 606, via a stopcock 662 and associated conduit 664 that communicate with second lumen 606 via a passageway 666 formed in head element 650.
  • Additionally, in accordance with a preferred embodiment of the present invention, an electrical resistance heating element 680 is disposed interiorly of the anchor balloon 640. Preferably, the resistance heating element 680 is formed of a foil or a wire which is electrically coupled at opposite ends thereof to electrical conductors which extend through the main shaft 602. In the illustrated embodiment, a first conductor 682 is attached to a first end 684 of resistance heating element 680 and preferably extends through the first lumen 604, and a second conductor 686 is attached to a second end 688 of resistance heating element 680 and extends through the second lumen 606.
  • Electrical power is supplied to resistance heating element 680 via a switch 690, which couples first conductor 682 and second conductor 686 to a source of electrical power. Heating of resistance heating element 680 enhances hemostasis at the aperture in the artery.
  • Reference is now made to FIGS. 9B-9J, which illustrate various steps in a preferred mode of operation of the apparatus of FIG. 9A. FIG. 9B illustrates the hemostasis device 600 about to be inserted into an artery 700 via a conventional catheter introducer assembly 702, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 702. The catheter introducer assembly 702 conventionally includes a catheter introducer sheath 704.
  • FIG. 9C shows the hemostasis device 600 inserted into the catheter introducer assembly 702 such that the outer end of the main shaft 602 extends into the artery 700 well beyond the end of catheter introducer sheath 704. As shown with particularity in FIG. 9C, at this stage both anchor balloon 640 and peripheral balloon 660 are deflated, as seen clearly in FIG. 10A.
  • Reference is now made to FIG. 9D, which shows initial inflation of the anchor balloon 640, preferably by use of a syringe 720, communicating with first lumen 604 via passageway 646 extending through the interior of head element 650, stopcock 642 and associated conduit 644. The inflated anchor balloon 640 preferably has a cusp-type configuration as seen with particularity in FIGS. 9D and 10B.
  • Following inflation of the anchor balloon 640, the catheter introducer assembly 702 and the hemostasis device 600 are both withdrawn, such that the catheter introducer sheath 704 is removed from artery 700 only when the anchor balloon 640 already engages the interior wall of artery 700 in sealing engagement with the aperture in the artery 700 through which the catheter introducer sheath 704 is withdrawn and through which the main shaft 602 presently extends. This stage is shown in FIG. 9E.
  • As seen in FIGS. 9F and 10C, initial inflation of the peripheral balloon 660 is effected, preferably by use of a syringe 740 communicating with second lumen 606 via passageway 666 in head element 650, stopcock 662 and associated conduit 664.
  • Thereafter, as seen in FIGS. 9G and 10D, the anchor balloon 640 is deflated, preferably by operation of syringe 720, communicating with first lumen 604 via passageway 646 in head element 650, stopcock 642 and associated conduit 644, and the peripheral balloon 660 remains fully inflated, which preferably causes the extreme end of the main shaft 602 to be withdrawn from the artery 700 to a location lying just outside the artery wall. As seen in FIG. 9G, peripheral balloon 660 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 640 is deflated. This volume of blood is located in a region, indicated by reference numeral 750, delimited by the engagement of peripheral balloon 660 with the artery wall.
  • Preferably at this stage heating of the electrical resistance heating element 680 is effected, preferably by an operator closing switch 690, as shown in FIG. 9H. This heating preferably continues for less than five minutes.
  • Once acceptable hemostasis has occurred in region 750, the peripheral balloon 660 is deflated, as shown in FIGS. 9I and 10A, preferably by operation of syringe 740, communicating with second lumen 606 via passageway 666 in head element 650, stopcock 662 and associated conduit 664.
  • Thereafter, the hemostasis device 600 is entirely withdrawn from the patient, leaving a region 760 of hemostasis outside of artery 700, as shown in FIG. 9J.
  • Reference is now made to FIGS. 11A, 11B, 11C, 11D, 11E, 11F, 11G, 11H, 11I and 11J, which are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 12A, 12B, 12C and 12D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 11A shows a hemostasis device 800 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention. The hemostasis device 800 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 800 comprises a main shaft 802, which has first and second lumens 804 and 806. First lumen 804 extends along the main shaft 802 to an anchor balloon inflation location 812. Second lumen 806 extends along the shaft 802 to a peripheral balloon inflation location 822.
  • Disposed at an end of main shaft 802 at anchor balloon inflation location 812 is an anchor balloon 840. Anchor balloon 840 is selectably inflated, as shown in FIGS. 12A-12D, via a stopcock 842 and associated conduit 844 in fluid communication with main shaft 802 via a passageway 846 formed in a head element 850. Head element 850 is fixed to main shaft 802 at an end thereof opposite the end at which anchor balloon 840 is located.
  • Disposed adjacent the end of main shaft 802 in fluid communication with peripheral balloon inflation location 822, exterior of an outer wall 852 thereof, is a peripheral balloon 860. Peripheral balloon 860 is selectably inflated, as shown in FIGS. 12A-12D, via second lumen 806, via a stopcock 862 and associated conduit 864 that communicate with second lumen 806 via a passageway 866 formed in head element 850.
  • Additionally, in accordance with a preferred embodiment of the present invention, a pair of mutually spaced electrodes 880 is disposed interiorly of the anchor balloon 840. Alternatively, electrodes 880 are disposed exteriorly of anchor balloon 840. Preferably, the electrodes 880 are each formed to have a configuration of a ball or knob and are each electrically coupled to a corresponding electrical conductor which extend through the main shaft 802. In the illustrated embodiment, a first conductor 882, which preferably extends through the first lumen 804, is attached to a first electrode 880 and a second conductor 884 is attached to a second electrode 880 and extends through the second lumen 806.
  • Electrical power is supplied to electrodes 880 via a switch, which couples first conductor 882 and second conductor 884 to an RF power source 890. Heating of electrodes 880 enhances hemostasis at the aperture in the artery.
  • Alternatively, a greater or lesser number of electrodes 880 may be employed. If only a single electrode 880 is provided, a suitable reference electrode (not shown) is preferably associated with a patient's body, such as underlying the patient.
  • Reference is now made to FIGS. 11B-11J, which illustrate various steps in a preferred mode of operation of the apparatus of FIG. 11A. FIG. 11B illustrates the hemostasis device 800 about to be inserted into an artery 900 via a conventional catheter introducer assembly 902, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 902. The catheter introducer assembly 902 conventionally includes a catheter introducer sheath 904.
  • FIG. 11C shows the hemostasis device 800 inserted into the catheter introducer assembly 902 such that the outer end of the main shaft 802 extends into the artery 900 well beyond the end of catheter introducer sheath 904. As shown with particularity in FIG. 11C, at this stage both anchor balloon 840 and peripheral balloon 860 are deflated, as seen clearly in FIG. 12A.
  • Reference is now made to FIG. 11D, which shows initial inflation of the anchor balloon 840, preferably by use of a syringe 920, communicating with first lumen 804 via passageway 846 extending through the interior of head element 850, stopcock 842 and associated conduit 844. The inflated anchor balloon 840 preferably has a cusp-type configuration as seen with particularity in FIGS. 11D and 12B.
  • Following inflation of the anchor balloon 840, the catheter introducer assembly 902 and the hemostasis device 800 are both withdrawn, such that the catheter introducer sheath 904 is removed from artery 900 only when the anchor balloon 840 already engages the interior wall of artery 900 in sealing engagement with the aperture in the artery 900 through which the catheter introducer sheath 904 is withdrawn and through which the main shaft 802 presently extends. This stage is shown in FIG. 11E.
  • As seen in FIGS. 11F and 12C, initial inflation of the peripheral balloon 860 is effected, preferably by use of a syringe 940 communicating with second lumen 806 via passageway 866 in head element 850, stopcock 862 and associated conduit 864.
  • Thereafter, as seen in FIGS. 11G and 12D, the anchor balloon 840 is deflated, preferably by operation of syringe 920, communicating with first lumen 804 via passageway 846 in head element 850, stopcock 842 and associated conduit 844, and the peripheral balloon 860 remains fully inflated, which preferably causes the extreme end of the main shaft 802 to be withdrawn from the artery 900 to a location lying just outside the artery wall. As seen in FIG. 11G, peripheral balloon 860 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 840 is deflated. This volume of blood is located in a region, indicated by reference numeral 950, delimited by the engagement of peripheral balloon 860 with the artery wall.
  • Preferably, at this stage, heating of the electrode or electrodes 880 is effected, preferably by an operator closing the switch coupling the first conductor 882 and the second conductor 884 to RF power source 890, as seen in FIG. 11H. This heating preferably continues for less than five minutes.
  • Once acceptable hemostasis has occurred in region 950, the peripheral balloon 860 is deflated, as shown in FIGS. 11I and 12A, preferably by operation of syringe 940, communicating with second lumen 806 via passageway 866 in head element 850, stopcock 862 and associated conduit 864.
  • Thereafter, the hemostasis device 800 is entirely withdrawn from the patient, leaving a region 960 of hemostasis outside of artery 900, as shown in FIG. 11J.
  • Reference is now made to FIGS. 13A, 13B, 13C, 13D, 13E, 13F, 13G, 13H, 13I and 13J, which are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 14A, 14B, 14C and 14D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 13A shows a hemostasis device 1000 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention. The hemostasis device 1000 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 1000 comprises a main shaft 1002, which has first and second lumens 1004 and 1006. First lumen 1004 extends along the main shaft 1002 to an anchor balloon inflation location 1012. Second lumen 1006 extends along the shaft 1002 to a peripheral balloon inflation location 1022.
  • Disposed at an end of main shaft 1002 at anchor balloon inflation location 1012 is an anchor balloon 1040. Anchor balloon 1040 is selectably inflated, as shown in FIGS. 14A-14D, via a stopcock 1042 and associated conduit 1044 in fluid communication with main shaft 1002 via a passageway 1046 formed in a head element 1050. Head element 1050 is fixed to main shaft 1002 at an end thereof opposite the end at which anchor balloon 1040 is located.
  • Disposed adjacent the end of main shaft 1002 in fluid communication with peripheral balloon inflation location 1022, exterior of an outer wall 1052 thereof, is a peripheral balloon 1060. Peripheral balloon 1060 is selectably inflated, as shown in FIGS. 14A-14D, via second lumen 1006, via a stopcock 1062 and associated conduit 1064 that communicate with second lumen 1006 via a passageway 1066 formed in head element 1050.
  • In accordance with a preferred embodiment of the present invention a coagulant agent supply conduit 1070 extends through the first lumen 1004 and through a bore 1072 formed along the length of head element 1050. Coagulant agent supply conduit 1070 communicates at one end thereof with a volume defined by inflation of the peripheral balloon 1060, between the balloon 1060 and the outer surface of an adjacent artery (not shown). At its opposite end, conduit 1070 communicates with a supply of coagulant agent (not shown) via a stopcock 1074 and associated conduit 1076.
  • Additionally, in accordance with a preferred embodiment of the present invention, an electrical resistance heating element 1080 is disposed interiorly of the anchor balloon 1040. Preferably, the resistance heating element 1080 is formed of a foil or a wire which is electrically coupled at opposite ends thereof to electrical conductors which extend through the main shaft 1002. In the illustrated embodiment, a first conductor, attached to a first end 1084 of resistance heating element 1080, is defined by or on the coagulant agent supply conduit 1070, which preferably extends through the first lumen 1004, and a second conductor 1086 is attached to a second end 1088 of resistance heating element 1080 and extends through the second lumen 1006.
  • Electrical power is supplied to resistance heating element 1080 via a switch 1090, which couples the first conductor, defined by conduit 1070, and second conductor 1086 to a source of electrical power. Heating of resistance heating element 1080 enhances hemostasis at the aperture in the artery. The operation of the resistance heating element 1080 as aforesaid is advantageously combined in this embodiment with the provision of a coagulation agent as described hereinabove.
  • Reference is now made to FIGS. 13B-13J, which illustrate various steps in a preferred mode of operation of the apparatus of FIG. 13A. FIG. 13B illustrates the hemostasis device 1000 about to be inserted into an artery 1100 via a conventional catheter introducer assembly 1102, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 1102. The catheter introducer assembly 1102 conventionally includes a catheter introducer sheath 1104.
  • FIG. 13C shows the hemostasis device 1000 inserted into the catheter introducer assembly 1102 such that the outer end of the main shaft 1002 extends into the artery 1100 well beyond the end of catheter introducer sheath 1104. As shown with particularity in FIG. 13C, at this stage both anchor balloon 1040 and peripheral balloon 1060 are deflated, as seen clearly in FIG. 14A.
  • Reference is now made to FIG. 13D, which shows initial inflation of the anchor balloon 1040, preferably by use of a syringe 1120, communicating with first lumen 1004 via passageway 1046 extending through the interior of head element 1050, stopcock 1042 and associated conduit 1044. The inflated anchor balloon 1040 preferably has a cusp-type configuration as seen with particularity in FIGS. 13D and 14B.
  • Following inflation of the anchor balloon 1040, the catheter introducer assembly 1102 and the hemostasis device 1000 are both withdrawn, such that the catheter introducer sheath 1104 is removed from artery 1100 only when the anchor balloon 1040 already engages the interior wall of artery 1100 in sealing engagement with the aperture in the artery 1100 through which the catheter introducer sheath 1104 is withdrawn and through which the main shaft 1002 presently extends. This stage is shown in FIG. 13E.
  • As seen in FIGS. 13F and 14C, initial inflation of the peripheral balloon 1060 is effected, preferably by use of a syringe 1140 communicating with second lumen 1006 via passageway 1066 in head element 1050, stopcock 1062 and associated conduit 1064.
  • Thereafter, as seen in FIGS. 13G and 14D, the anchor balloon 1040 is deflated, preferably by operation of syringe 1120, communicating with first lumen 1004 via passageway 1046 in head element 1050, stopcock 1042 and associated conduit 1044, and the peripheral balloon 1060 remains fully inflated, which preferably causes the extreme end of the main shaft 1002 to be withdrawn from the artery 1100 to a location lying just outside the artery wall. As seen in FIG. 13G, peripheral balloon 1060 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 1040 is deflated. This volume of blood is located in a region, indicated by reference numeral 1150, delimited by the engagement of peripheral balloon 1060 with the artery wall.
  • At this stage, a coagulant agent is preferably supplied to the volume of blood at region 1150, between the balloon 1060 and the outer surface of artery 1100. The coagulant agent is supplied to region 1150 by conduit 1070 from a supply of coagulant agent 1152 via stopcock 1074 and associated conduit 1076, as shown in FIG. 13H.
  • Preferably also at this stage, heating of the electrical resistance heating element 1080 is effected, preferably by an operator closing switch 1090. This heating preferably continues for less than five minutes.
  • Once acceptable hemostasis has occurred in region 1150, the peripheral balloon 1060 is deflated, as shown in FIGS. 13I and 14A, preferably by operation of syringe 1140, communicating with second lumen 1006 via passageway 1066 in head element 1050, stopcock 1062 and associated conduit 1064.
  • Thereafter, the hemostasis device 1000 is entirely withdrawn from the patient, leaving a region 1160 of hemostasis outside of artery 1100, as shown in FIG. 13J.
  • Reference is now made to FIGS. 15A, 15B, 15C, 15D, 15E, 15F, 15G, 15H, 15I and 15J, which are simplified illustrations of a hemostasis device constructed and operative in accordance with still another preferred embodiment of the present invention and various stages of its operation in a patient treatment context and to FIGS. 16A, 16B, 16C and 16D, which are simplified illustrations of four different states of inflation of the hemostasis device.
  • FIG. 15A shows a hemostasis device 1200 for producing hemostasis following arterial catheterization, in accordance with yet another preferred embodiment of the present invention. The hemostasis device 1200 is suitable for insertion via a conventional catheter introducer (not shown) following completion of catheterization and removal of the catheter from the catheter introducer.
  • In accordance with a preferred embodiment of the present invention, hemostasis device 1200 comprises a main shaft 1202, which has first and second lumens 1204 and 1206. First lumen 1204 extends along the main shaft 1202 to an anchor balloon inflation location 1212. Second lumen 1206 extends along the shaft 1202 to a peripheral balloon inflation location 1222.
  • Disposed at an end of main shaft 1202 at anchor balloon inflation location 1212 is an anchor balloon 1240. Anchor balloon 1240 is selectably inflated, as shown in FIGS. 16A-16D, via a stopcock 1242 and associated conduit 1244 in fluid communication with main shaft 1202 via a passageway 1246 formed in a head element 1250. Head element 1250 is fixed to main shaft 1202 at an end thereof opposite the end at which anchor balloon 1240 is located.
  • Disposed adjacent the end of main shaft 1202 in fluid communication with peripheral balloon inflation location 1222, exterior of an outer wall 1252 thereof, is a peripheral balloon 1260. Peripheral balloon 1260 is selectably inflated, as shown in FIGS. 16A-16D, via second lumen 1206, via a stopcock 1262 and associated conduit 1264 that communicate with second lumen 1206 via a passageway 1266 formed in head element 1250.
  • In accordance with a preferred embodiment of the present invention a coagulant agent supply conduit 1270 extends through the first lumen 1204 and through a bore 1272 formed in head element 1250. Coagulant agent supply conduit 1270 communicates at one end thereof, via a coagulant agent aperture 1273, with a volume defined by inflation of the peripheral balloon 1260, between the balloon 1260 and the outer surface of an adjacent artery (not shown). At its opposite end, conduit 1270 communicates with a supply of coagulant agent (not shown) via a stopcock 1274 and associated conduit 1276. Coagulant agent aperture 1273 is clearly shown in FIGS. 16A-16D.
  • Additionally, in accordance with a preferred embodiment of the present invention, a pair of mutually spaced electrodes 1280 is disposed interiorly of the anchor balloon 1240. Alternatively, electrodes 1280 are disposed exteriorly of anchor balloon 1240. Preferably, the electrodes 1280 are each formed to have a configuration of a ball or knob and are each electrically coupled to a corresponding electrical conductor which extend through the main shaft 1202. In the illustrated embodiment, a first conductor, attached to a first electrode 1280, is defined by or on the coagulant agent supply conduit 1270, which preferably extends through the first lumen 1204, and a second conductor 1286 is attached to a second electrode 1280 and extends through the second lumen 1206.
  • Electrical power is supplied to electrodes 1280 via a switch, which couples the first conductor and the second conductor 1286 to an RF power source 1290. Heating of electrodes 1280 enhances hemostasis at the aperture in the artery. The operation of the electrodes 1280 as aforesaid is advantageously combined in this embodiment with the provision of a coagulation agent as described hereinabove.
  • Alternatively, a greater or lesser number of electrodes 1280 may be employed. If only a single electrode 1280 is provided, a suitable reference electrode (not shown) is preferably associated with a patient's body, such as underlying the patient.
  • Reference is now made to FIGS. 15B-15J, which illustrate various steps in a preferred mode of operation of the apparatus of FIG. 15A. FIG. 15B illustrates the hemostasis device 1200 about to be inserted into an artery 1300 via a conventional catheter introducer assembly 1302, following completion of a catheterization procedure and withdrawal of a catheter (not shown) from the catheter introducer assembly 1302. The catheter introducer assembly 1302 conventionally includes a catheter introducer sheath 1304.
  • FIG. 15C shows the hemostasis device 1200 inserted into the catheter introducer assembly 1302 such that the outer end of the main shaft 1202 extends into the artery 1300 well beyond the end of catheter introducer sheath 1304. As shown with particularity in FIG. 15C, at this stage both anchor balloon 1240 and peripheral balloon 1260 are deflated, as seen clearly in FIG. 16A.
  • Reference is now made to FIG. 15D, which shows initial inflation of the anchor balloon 1240, preferably by use of a syringe 1320, communicating with first lumen 1204 via passageway 1246 extending through the interior of head element 1250, stopcock 1242 and associated conduit 1244. The inflated anchor balloon 1240 preferably has a cusp-type configuration as seen with particularity in FIGS. 15D and 16B.
  • Following inflation of the anchor balloon 1240, the catheter introducer assembly 1302 and the hemostasis device 1200 are both withdrawn, such that the catheter introducer sheath 1304 is removed from artery 1300 only when the anchor balloon 1240 already engages the interior wall of artery 1300 in sealing engagement with the aperture in the artery 1300 through which the catheter introducer sheath 1304 is withdrawn and through which the main shaft 1202 presently extends. This stage is shown in FIG. 15E.
  • As seen in FIGS. 15F and 16C, initial inflation of the peripheral balloon 1260 is effected, preferably by use of a syringe 1340 communicating with second lumen 1206 via passageway 1266 in head element 1250, stopcock 1262 and associated conduit 1264.
  • Thereafter, as seen in FIGS. 15G and 16D, the anchor balloon 1240 is deflated, preferably by operation of syringe 1320, communicating with first lumen 1204 via passageway 1246 in head element 1250, stopcock 1242 and associated conduit 1244, and the peripheral balloon 1260 remains fully inflated, which preferably causes the extreme end of the main shaft 1202 to be withdrawn from the artery 1300 to a location lying just outside the artery wall. As seen in FIG. 15G, peripheral balloon 1260 is preferably designed to allow a limited volume of blood to collect outside of the artery wall after the anchor balloon 1240 is deflated. This volume of blood is located in a region, indicated by reference numeral 1350, delimited by the engagement of peripheral balloon 1260 with the artery wall.
  • At this stage, a coagulant agent is preferably supplied to the volume of blood at region 1350, between the balloon 1260 and the outer surface of artery 1300. The coagulant agent is supplied to region 1350 by conduit 1270, via coagulant agent aperture 1273 from a supply of coagulant agent 1352 via stopcock 1274 and associated conduit 1276, as shown in FIG. 15H.
  • Preferably, also at this stage, heating of the electrode or electrodes 1280 is effected, preferably by an operator closing the switch coupling the first conductor and the second conductor 1286 to RF power source 1290, as seen in FIG. 15H. This heating preferably continues for less than five minutes.
  • Once acceptable hemostasis has occurred in region 1350, the peripheral balloon 1260 is deflated, as shown in FIGS. 15I and 16A, preferably by operation of syringe 1340, communicating with second lumen 1206 via passageway 1266 in head element 1250, stopcock 1262 and associated conduit 1264.
  • Thereafter, the hemostasis device 1200 is entirely withdrawn from the patient, leaving a region 1360 of hemostasis outside of artery 1300, as shown in FIG. 15J.
  • It will be appreciated by persons skilled in the art that the present invention is not limited by what has been particularly shown and described hereinabove. Rather the scope of the present invention includes both combinations and subcombinations of the various features described hereinabove and shown in the drawings as well as modifications and further developments thereof which would occur to a person of ordinary skill in the art upon reading the foregoing description and which are not in the prior art.

Claims (56)

1. A hemostasis device comprising:
a resistance heating element for accelerating hemostasis;
a blood resistance sensor; and
a blood resistance indicator, operative to provide an indication of the resistance at said resistance sensor of blood undergoing hemostasis.
2. A hemostasis device according to claim 1 and also comprising a power supply connected to said resistance heating element, said resistance sensor and said resistance indicator.
3. A hemostasis device according to claim 2 and wherein said power supply is operative to supply a relatively high level current to said resistance heating element.
4. A hemostasis device according to either of claims 2 and 3 and wherein said power supply is operative to supply a relatively low level current to said resistance sensor.
5. A method for accelerating hemostasis of an artery of a patient having a puncture after arterial catheterization, the method comprising the steps of:
following arterial catheterization, introducing a hemostasis device, such that a forward end of said hemostasis device lies exterior of the artery adjacent said puncture;
accelerating hemostasis by heating tissue in the vicinity of said puncture, thereby shortening the time required for hemostasis; and
following hemostasis, removing said hemostasis device from the patient.
6. A method according to claim 5 and also comprising inserting a catheter introducer into said artery prior to said arterial catheterization and wherein following said arterial catheterization, said hemostasis device is introduced through said catheter introducer.
7. A method according to any of claims 5-6 and also comprising measuring the conductivity of blood in the vicinity of said puncture during hemostasis.
8. A method for monitoring the progress of hemostasis of an artery of a patient having a puncture after arterial catheterization, the method comprising the steps of:
following arterial catheterization, introducing a hemostasis device, such that a forward end of said hemostasis device lies exterior of the artery adjacent said puncture;
during hemostasis, measuring the heat conductivity of blood in the vicinity of said puncture, thereby to provide an output indication of the progress of hemostasis; and
following hemostasis, removing said hemostasis device from the patient.
9. A method according to claim 8 and also comprising the step of inserting into an artery a catheter introducer prior to arterial catheterization and wherein following said arterial catheterization, said hemostasis device is introduced through said catheter introducer.
10. A method according to either of claim 8 or claim 9 and also comprising inflating a balloon to block said puncture, prior to said hemostasis.
11. A method according to claim 10 and also comprising deflating said balloon prior to removing said hemostasis device.
12. A hemostasis device comprising:
a main shaft;
at least one balloon mounted on said main shaft; and
at least one electrode, mounted on said main shaft and being operable to supply an electric current suitable for causing hemostasis.
13. A hemostasis device according to claim 12 and wherein said at least one balloon comprises:
at least one anchor balloon, disposed at an end of said main shaft; and
at least one peripheral balloon, disposed at a location along said main shaft exterior to a wall of said main shaft.
14. A hemostasis device according to claim 13 and wherein said at least one peripheral balloon and a wall of an artery are configured to delimit a region which is subject to hemostasis.
15. A hemostasis device according to any of claims 12-14 and also comprising an electrical power source and a control module.
16. A hemostasis device according to claim 15 and wherein said power source is an RF power supply.
17. A hemostasis device according to claim 16 and wherein said RF power supply is operative to supply electrical power at RF frequencies within a range of 0.1-10 watts at up to 25 volts.
18. A hemostasis device according to any of claims 15-17 and wherein said control module is operative to measure at least one of electrical current, blood resistance and blood temperature.
19. A hemostasis device according to any of claims 15-18 and wherein said control module is operative to adjust power supplied by said power source based on at least one measurement.
20. A hemostasis device according to any of claims 12-19 and wherein said at least one electrode comprises a pair of electrodes.
21. A method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization comprising:
introducing a hemostasis device comprising at least one electrode into the vicinity of said puncture;
supplying an electric current to said at least one electrode, thereby heating a volume of blood in the vicinity of said puncture, causing hemostasis; and
subsequently removing said hemostasis device from the patient.
22. A method according to claim 21 and wherein said introducing comprises introducing via a catheter introducer.
23. A method according to either of claims 21 and 22 and wherein said introducing also comprises inflating an anchor balloon attached to an end of said hemostasis device.
24. A method according to any of claims 21-23 and wherein said introducing comprises inflating a peripheral balloon.
25. A method according to claim 24 and wherein said removing said hemostasis device comprises deflating said peripheral balloon.
26. A method according to any of claims 21-25 and wherein said introducing comprises positioning said at least one electrode in close proximity to a volume of blood.
27. A method according to any of claims 21-26 and wherein said supplying comprises supplying electrical power at RF frequencies.
28. A method according to claim 27 and wherein said electrical power comprises electrical power in the range of 0.1-10 watts at up to 25 volts.
29. A method according to any of claims 21-28 and wherein said supplying also comprises adjusting said electric current based on a feedback measurement.
30. A hemostasis device comprising:
a main shaft;
at least one balloon mounted on said main shaft adjacent an end thereof; and
a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of said main shaft beyond said at least one balloon.
31. A hemostasis device according to claim 30 and also comprising at least one heating assembly operative to provide heating at said location.
32. A hemostasis device according to claim 31 and wherein said at least one heating assembly comprises at least one electrode disposed adjacent said location.
33. A hemostasis device according to claim 32 and wherein said at least one electrode is disposed interiorly of said at least one balloon.
34. A hemostasis device according to claim 32 and wherein said at least one electrode is disposed exteriorly of said at least one balloon.
35. A hemostasis device according to any of claims 31-33 and wherein said at least one heating assembly comprises an electrical resistive heating element.
36. A hemostasis device according to claim 35 and wherein said electrical resistive heating element is disposed within said at least one balloon.
37. A hemostasis device comprising:
a main shaft;
at least one balloon mounted on said main shaft adjacent an end thereof; and
at least one RF electrode located at a location at an end of said main shaft beyond said at least one balloon.
38. A hemostasis device according to claim 37 and also comprising a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of said main shaft beyond said at least one balloon.
39. A hemostasis device according to claim 37 and wherein said at least one RF electrode is disposed interiorly of said at least one balloon.
40. A hemostasis device according to claim 37 and wherein said at least one RF electrode is disposed exteriorly of said at least one balloon.
41. A hemostasis device comprising:
a main shaft;
at least one balloon mounted on said main shaft adjacent an end thereof; and
at least one resistive heating element located at a location at an end of said main shaft beyond said at least one balloon.
42. A hemostasis device according to claim 41 and also comprising a hemostasis agent supply conduit operative to supply a hemostasis agent at a location at an end of said main shaft beyond said at least one balloon.
43. A hemostasis device according to claim 42 and wherein said at least one resistance heating element is disposed interiorly of said at least one balloon.
44. A method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization comprising:
introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of said puncture; and
supplying a hemostasis agent to said location at said end of said shaft beyond said at least one balloon.
45. A method according to claim 44 and also comprising providing heating at said location.
46. A method according to claim 45 and wherein said providing heating includes locating at least one electrode adjacent said location.
47. A method according to claim 46 and wherein said at least one electrode is disposed interiorly of said at least one balloon.
48. A method according to claim 46 and wherein said at least one electrode is disposed exteriorly of said at least one balloon.
49. A method according to any of claims 45-48 and wherein said providing heating comprises providing electrical resistive heating.
50. A method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization comprising:
introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of said puncture; and
operating at least one RF electrode at said location at said end of said main shaft beyond said at least one balloon.
51. A method according to claim 50 and also comprising:
supplying a hemostasis agent to said location at said end of said shaft beyond said at least one balloon.
52. A method according to either of claims 50 and 51 and wherein said at least one RF electrode is disposed interiorly of said at least one balloon.
53. A method according to either of claims 50 and 51 and wherein said at least one RF electrode is disposed exteriorly of said at least one balloon.
54. A method for producing hemostasis at an artery of a patient having a puncture following arterial catheterization comprising:
introducing a hemostasis device including at least one balloon mounted adjacent an end of a shaft to a location in the vicinity of said puncture; and
operating at least one resistance heating element at said location at an end of said shaft beyond said at least one balloon.
55. A method according to claim 54 and also comprising:
supplying a hemostasis agent to said location at said end of said shaft beyond said at least one balloon.
56. A method according to either of claims 54 and 55 and wherein said at least one resistance heating element is disposed interiorly of said at least one balloon.
US10/543,654 2003-02-04 2004-02-03 Methods and apparatus for hemostasis following arterial catheterization Abandoned US20070055223A1 (en)

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US10/358,130 US7115127B2 (en) 2003-02-04 2003-02-04 Methods and apparatus for hemostasis following arterial catheterization
US10358130 2003-02-04
US10616887 2003-07-10
US10/616,887 US7223266B2 (en) 2003-02-04 2003-07-10 Methods and apparatus for hemostasis following arterial catheterization
US10/543,654 US20070055223A1 (en) 2003-02-04 2004-02-03 Methods and apparatus for hemostasis following arterial catheterization
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US11/791,448 Abandoned US20100228241A1 (en) 2003-02-04 2005-02-02 Methods and apparatus for hemostasis following arterial catheterization
US11/797,294 Abandoned US20070213710A1 (en) 2003-02-04 2007-05-02 Methods and apparatus for hemostasis following arterial catheterization
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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090118729A1 (en) * 2007-11-07 2009-05-07 Mirabilis Medica Inc. Hemostatic spark erosion tissue tunnel generator with integral treatment providing variable volumetric necrotization of tissue
US20090118725A1 (en) * 2007-11-07 2009-05-07 Mirabilis Medica, Inc. Hemostatic tissue tunnel generator for inserting treatment apparatus into tissue of a patient
US8366706B2 (en) 2007-08-15 2013-02-05 Cardiodex, Ltd. Systems and methods for puncture closure
US8372072B2 (en) 2003-02-04 2013-02-12 Cardiodex Ltd. Methods and apparatus for hemostasis following arterial catheterization
US20140164499A1 (en) * 2011-08-01 2014-06-12 Infobank Corp. Wireless communication device, information processing method and recording medium

Families Citing this family (67)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8323305B2 (en) * 1997-02-11 2012-12-04 Cardiva Medical, Inc. Expansile device for use in blood vessels and tracts in the body and method
US7756583B2 (en) 2002-04-08 2010-07-13 Ardian, Inc. Methods and apparatus for intravascularly-induced neuromodulation
US8347891B2 (en) 2002-04-08 2013-01-08 Medtronic Ardian Luxembourg S.A.R.L. Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen
US7115127B2 (en) 2003-02-04 2006-10-03 Cardiodex, Ltd. Methods and apparatus for hemostasis following arterial catheterization
US7322976B2 (en) * 2003-03-04 2008-01-29 Cardiva Medical, Inc. Apparatus and methods for closing vascular penetrations
JP2007504910A (en) 2003-09-12 2007-03-08 ミノウ・メディカル・エルエルシイ Selectable biased reshaping and / or excision of atherosclerotic material
US9017374B2 (en) * 2004-04-09 2015-04-28 Cardiva Medical, Inc. Device and method for sealing blood vessels
US20080154303A1 (en) 2006-12-21 2008-06-26 Cardiva Medical, Inc. Hemostasis-enhancing device and method for its use
US7993366B2 (en) 2004-05-27 2011-08-09 Cardiva Medical, Inc. Self-tensioning vascular occlusion device and method for its use
US7572274B2 (en) * 2004-05-27 2009-08-11 Cardiva Medical, Inc. Self-tensioning vascular occlusion device and method for its use
US8396548B2 (en) 2008-11-14 2013-03-12 Vessix Vascular, Inc. Selective drug delivery in a lumen
JP5068662B2 (en) 2004-11-22 2012-11-07 カーディオデックス リミテッド Heat treatment technology for varicose veins
US20060116635A1 (en) * 2004-11-29 2006-06-01 Med Enclosure L.L.C. Arterial closure device
EP2438877B1 (en) 2005-03-28 2016-02-17 Vessix Vascular, Inc. Intraluminal electrical tissue characterization and tuned RF energy for selective treatment of atheroma and other target tissues
CN102225024B (en) * 2005-07-21 2013-05-01 泰科医疗集团有限合伙公司 Systems and methods for treating a hollow anatomical structure
US8911472B2 (en) 2005-12-13 2014-12-16 Cardiva Medical, Inc. Apparatus and methods for delivering hemostatic materials for blood vessel closure
US9179897B2 (en) 2005-12-13 2015-11-10 Cardiva Medical, Inc. Vascular closure devices and methods providing hemostatic enhancement
US20100168767A1 (en) * 2008-06-30 2010-07-01 Cardiva Medical, Inc. Apparatus and methods for delivering hemostatic materials for blood vessel closure
US7691127B2 (en) * 2005-12-13 2010-04-06 Cardiva Medical, Inc. Drug eluting vascular closure devices and methods
US7789893B2 (en) * 2006-09-12 2010-09-07 Boston Scientific Scimed, Inc. Method and apparatus for promoting hemostasis of a blood vessel puncture
WO2008049082A2 (en) 2006-10-18 2008-04-24 Minnow Medical, Inc. Inducing desirable temperature effects on body tissue
AU2007310991B2 (en) 2006-10-18 2013-06-20 Boston Scientific Scimed, Inc. System for inducing desirable temperature effects on body tissue
EP2954868A1 (en) 2006-10-18 2015-12-16 Vessix Vascular, Inc. Tuned rf energy and electrical tissue characterization for selective treatment of target tissues
US20100070019A1 (en) * 2006-10-29 2010-03-18 Aneuwrap Ltd. extra-vascular wrapping for treating aneurysmatic aorta and methods thereof
WO2008097956A1 (en) 2007-02-05 2008-08-14 Boston Scientific Limited Vascular sealing device and method using clot enhancing balloon and electric field generation
US8469950B2 (en) * 2007-02-15 2013-06-25 Cardionova Ltd. Intra-atrial apparatus and method of use thereof
CN101715329B (en) 2007-03-05 2012-11-14 恩多斯潘有限公司 Multi-component expandable supportive bifurcated endoluminal grafts and methods for using same
US8496653B2 (en) 2007-04-23 2013-07-30 Boston Scientific Scimed, Inc. Thrombus removal
US8202269B2 (en) * 2007-05-25 2012-06-19 The Regents Of The Universtiy Of Michigan Electrical cautery device
US8486131B2 (en) 2007-12-15 2013-07-16 Endospan Ltd. Extra-vascular wrapping for treating aneurysmatic aorta in conjunction with endovascular stent-graft and methods thereof
US8241324B2 (en) * 2008-03-03 2012-08-14 Eilaz Babaev Ultrasonic vascular closure device
JP5616891B2 (en) 2008-08-26 2014-10-29 セント ジュード メディカル インコーポレイテッドSt. Jude Medical, Inc. Method and system for sealing a percutaneous puncture
CN102271603A (en) 2008-11-17 2011-12-07 明诺医学股份有限公司 Selective accumulation of energy with or without knowledge of tissue topography
US20100152748A1 (en) * 2008-12-12 2010-06-17 E-Pacing, Inc. Devices, Systems, and Methods Providing Body Lumen Access
US8551096B2 (en) 2009-05-13 2013-10-08 Boston Scientific Scimed, Inc. Directional delivery of energy and bioactives
EP2445444B1 (en) 2009-06-23 2018-09-26 Endospan Ltd. Vascular prostheses for treating aneurysms
CA2767596C (en) 2009-07-09 2015-11-24 Endospan Ltd. Apparatus for closure of a lumen and methods of using the same
US8845682B2 (en) 2009-10-13 2014-09-30 E-Pacing, Inc. Vasculature closure devices and methods
WO2011064782A2 (en) 2009-11-30 2011-06-03 Endospan Ltd. Multi-component stent-graft system for implantation in a blood vessel with multiple branches
WO2011070576A1 (en) 2009-12-08 2011-06-16 Endospan Ltd. Endovascular stent-graft system with fenestrated and crossing stent-grafts
CA2785953C (en) 2009-12-31 2016-02-16 Endospan Ltd. Endovascular flow direction indicator
CA2789304C (en) 2010-02-08 2018-01-02 Endospan Ltd. Thermal energy application for prevention and management of endoleaks in stent-grafts
EP2555699B1 (en) 2010-04-09 2019-04-03 Vessix Vascular, Inc. Power generating and control apparatus for the treatment of tissue
US9526638B2 (en) 2011-02-03 2016-12-27 Endospan Ltd. Implantable medical devices constructed of shape memory material
US9855046B2 (en) 2011-02-17 2018-01-02 Endospan Ltd. Vascular bands and delivery systems therefor
WO2012117395A1 (en) 2011-03-02 2012-09-07 Endospan Ltd. Reduced-strain extra- vascular ring for treating aortic aneurysm
US9055937B2 (en) 2011-04-01 2015-06-16 Edwards Lifesciences Corporation Apical puncture access and closure system
WO2012161875A1 (en) 2011-04-08 2012-11-29 Tyco Healthcare Group Lp Iontophoresis drug delivery system and method for denervation of the renal sympathetic nerve and iontophoretic drug delivery
US8574287B2 (en) 2011-06-14 2013-11-05 Endospan Ltd. Stents incorporating a plurality of strain-distribution locations
EP2579811B1 (en) 2011-06-21 2016-03-16 Endospan Ltd Endovascular system with circumferentially-overlapping stent-grafts
US9254209B2 (en) 2011-07-07 2016-02-09 Endospan Ltd. Stent fixation with reduced plastic deformation
WO2013030818A2 (en) 2011-08-28 2013-03-07 Endospan Ltd. Stent-grafts with post-deployment variable axial and radial displacement
US9427339B2 (en) 2011-10-30 2016-08-30 Endospan Ltd. Triple-collar stent-graft
WO2013084235A2 (en) 2011-12-04 2013-06-13 Endospan Ltd. Branched stent-graft system
US9770350B2 (en) 2012-05-15 2017-09-26 Endospan Ltd. Stent-graft with fixation elements that are radially confined for delivery
US9993360B2 (en) 2013-01-08 2018-06-12 Endospan Ltd. Minimization of stent-graft migration during implantation
US9668892B2 (en) 2013-03-11 2017-06-06 Endospan Ltd. Multi-component stent-graft system for aortic dissections
US10966697B2 (en) 2013-05-06 2021-04-06 Caveomed Gmbh Vascular closure device and method of positioning vascular closure device
EP2801325B1 (en) * 2013-05-06 2016-03-16 CaveoMed GmbH Vascular closure device
US10085731B2 (en) 2013-07-15 2018-10-02 E-Pacing, Inc. Vasculature closure devices and methods
US10603197B2 (en) 2013-11-19 2020-03-31 Endospan Ltd. Stent system with radial-expansion locking
US10709490B2 (en) 2014-05-07 2020-07-14 Medtronic Ardian Luxembourg S.A.R.L. Catheter assemblies comprising a direct heating element for renal neuromodulation and associated systems and methods
BR112017012425A2 (en) 2014-12-18 2018-01-02 Endospan Ltd endovascular stent graft with fatigue resistant lateral tube
WO2017075528A1 (en) 2015-10-30 2017-05-04 ECMOtek, LLC Devices for endovascular access through extracorporeal life support circuits
US11627795B2 (en) 2017-02-14 2023-04-18 G-Tech Llc Shoulder transfer weight support system and face shield
US10952710B2 (en) * 2017-07-16 2021-03-23 Steven Jay Blumenthal Balloon closure device
US11272941B1 (en) 2020-08-07 2022-03-15 William P Buchanan Secondary device holder and compression system, method of making and using the same

Citations (91)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2144090A (en) * 1936-03-17 1939-01-17 Trice Spencer Talley Electrical hemostat
US3176114A (en) * 1962-07-16 1965-03-30 Richard F Kneisley Device for removing nasal hair
US3301258A (en) * 1963-10-03 1967-01-31 Medtronic Inc Method and apparatus for treating varicose veins
US3302635A (en) * 1963-09-19 1967-02-07 Fred E Pittman Semi-rigid device for marking internal bleeding
US3494364A (en) * 1967-11-09 1970-02-10 Weck & Co Inc Edward Handle component for electro-surgical instrument
US3500828A (en) * 1966-08-31 1970-03-17 Fred W Podhora Intravenous catheter apparatus
US3636943A (en) * 1967-10-27 1972-01-25 Ultrasonic Systems Ultrasonic cauterization
US3858586A (en) * 1971-03-11 1975-01-07 Martin Lessen Surgical method and electrode therefor
US3938527A (en) * 1973-07-04 1976-02-17 Centre De Recherche Industrielle De Quebec Instrument for laparoscopic tubal cauterization
US4003380A (en) * 1974-09-05 1977-01-18 F.L. Fisher Bipolar coagulation instrument
US4007743A (en) * 1975-10-20 1977-02-15 American Hospital Supply Corporation Opening mechanism for umbrella-like intravascular shunt defect closure device
US4011872A (en) * 1974-04-01 1977-03-15 Olympus Optical Co., Ltd. Electrical apparatus for treating affected part in a coeloma
US4014343A (en) * 1975-04-25 1977-03-29 Neomed Incorporated Detachable chuck for electro-surgical instrument
US4074718A (en) * 1976-03-17 1978-02-21 Valleylab, Inc. Electrosurgical instrument
US4314559A (en) * 1979-12-12 1982-02-09 Corning Glass Works Nonstick conductive coating
US4314555A (en) * 1979-02-20 1982-02-09 Terumo Corporation Intravascular catheter assembly
US4317445A (en) * 1980-03-31 1982-03-02 Baxter Travenol Laboratories, Inc. Catheter insertion unit with separate flashback indication for the cannula
US4370980A (en) * 1981-03-11 1983-02-01 Lottick Edward A Electrocautery hemostat
US4424833A (en) * 1981-10-02 1984-01-10 C. R. Bard, Inc. Self sealing gasket assembly
US4654024A (en) * 1985-09-04 1987-03-31 C.R. Bard, Inc. Thermorecanalization catheter and method for use
US4801293A (en) * 1985-10-09 1989-01-31 Anthony Jackson Apparatus and method for detecting probe penetration of human epidural space and injecting a therapeutic substance thereinto
US4890612A (en) * 1987-02-17 1990-01-02 Kensey Nash Corporation Device for sealing percutaneous puncture in a vessel
US4900303A (en) * 1978-03-10 1990-02-13 Lemelson Jerome H Dispensing catheter and method
US4994060A (en) * 1984-09-17 1991-02-19 Xintec Corporation Laser heated cautery cap with transparent substrate
US5002051A (en) * 1983-10-06 1991-03-26 Lasery Surgery Software, Inc. Method for closing tissue wounds using radiative energy beams
US5078743A (en) * 1990-04-19 1992-01-07 Abraham Mikalov Method of placing an esophageal voice prosthesis in a laryngectomized person
US5080660A (en) * 1990-05-11 1992-01-14 Applied Urology, Inc. Electrosurgical electrode
US5085659A (en) * 1990-11-21 1992-02-04 Everest Medical Corporation Biopsy device with bipolar coagulation capability
US5087256A (en) * 1990-01-12 1992-02-11 Metcal Inc. Thermal atherectomy device
US5088997A (en) * 1990-03-15 1992-02-18 Valleylab, Inc. Gas coagulation device
US5178620A (en) * 1988-06-10 1993-01-12 Advanced Angioplasty Products, Inc. Thermal dilatation catheter and method
US5183464A (en) * 1991-05-17 1993-02-02 Interventional Thermodynamics, Inc. Radially expandable dilator
US5188634A (en) * 1990-07-13 1993-02-23 Trimedyne, Inc. Rotatable laser probe with beveled tip
US5188602A (en) * 1990-07-12 1993-02-23 Interventional Thermodynamics, Inc. Method and device for delivering heat to hollow body organs
US5190541A (en) * 1990-10-17 1993-03-02 Boston Scientific Corporation Surgical instrument and method
US5192300A (en) * 1990-10-01 1993-03-09 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5192302A (en) * 1989-12-04 1993-03-09 Kensey Nash Corporation Plug devices for sealing punctures and methods of use
US5275616A (en) * 1990-10-01 1994-01-04 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5277696A (en) * 1991-11-19 1994-01-11 Delma Elektro- Und Medizinische Apparatebau Gesellschaft Mbh Medical high frequency coagulation instrument
US5281216A (en) * 1992-03-31 1994-01-25 Valleylab, Inc. Electrosurgical bipolar treating apparatus
US5282827A (en) * 1991-11-08 1994-02-01 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5282799A (en) * 1990-08-24 1994-02-01 Everest Medical Corporation Bipolar electrosurgical scalpel with paired loop electrodes
US5290310A (en) * 1991-10-30 1994-03-01 Howmedica, Inc. Hemostatic implant introducer
US5292332A (en) * 1992-07-27 1994-03-08 Lee Benjamin I Methods and device for percutanceous sealing of arterial puncture sites
US5383896A (en) * 1993-05-25 1995-01-24 Gershony; Gary Vascular sealing device
US5383899A (en) * 1993-09-28 1995-01-24 Hammerslag; Julius G. Method of using a surface opening adhesive sealer
US5486195A (en) * 1993-07-26 1996-01-23 Myers; Gene Method and apparatus for arteriotomy closure
US5593406A (en) * 1992-05-01 1997-01-14 Hemostatic Surgery Corporation Endoscopic instrument with auto-regulating heater and method of using same
US5611798A (en) * 1995-03-02 1997-03-18 Eggers; Philip E. Resistively heated cutting and coagulating surgical instrument
US5716325A (en) * 1990-03-02 1998-02-10 General Surgical Innovations, Inc. Arthroscopic retractors and method of using the same
US5725551A (en) * 1993-07-26 1998-03-10 Myers; Gene Method and apparatus for arteriotomy closure
US5728122A (en) * 1994-01-18 1998-03-17 Datascope Investment Corp. Guide wire with releaseable barb anchor
US5728134A (en) * 1996-09-17 1998-03-17 Barak; Shlomo Method and apparatus for hemostasis
US5728133A (en) * 1996-07-09 1998-03-17 Cardiologics, L.L.C. Anchoring device and method for sealing percutaneous punctures in vessels
USRE35755E (en) * 1989-05-12 1998-03-24 Scimed Life Systems, Inc. Method for inducing thrombosis in blood vessels
US5868778A (en) * 1995-10-27 1999-02-09 Vascular Solutions, Inc. Vascular sealing apparatus and method
US5879499A (en) * 1996-06-17 1999-03-09 Heartport, Inc. Method of manufacture of a multi-lumen catheter
US6022361A (en) * 1998-10-09 2000-02-08 Biointerventional Corporation Device for introducing and polymerizing polymeric biomaterials in the human body and method
US6022336A (en) * 1996-05-20 2000-02-08 Percusurge, Inc. Catheter system for emboli containment
US6033398A (en) * 1996-03-05 2000-03-07 Vnus Medical Technologies, Inc. Method and apparatus for treating venous insufficiency using directionally applied energy
US6033401A (en) * 1997-03-12 2000-03-07 Advanced Closure Systems, Inc. Vascular sealing device with microwave antenna
US6179832B1 (en) * 1997-09-11 2001-01-30 Vnus Medical Technologies, Inc. Expandable catheter having two sets of electrodes
US20020002371A1 (en) * 2000-03-24 2002-01-03 Acker David E. Apparatus and methods for intrabody thermal treatment
US6350274B1 (en) * 1992-05-11 2002-02-26 Regen Biologics, Inc. Soft tissue closure systems
US20030005397A1 (en) * 2000-07-07 2003-01-02 Larsen Corey L. Method and apparatus for PCB array with compensated signal propagation
US6503247B2 (en) * 1997-06-27 2003-01-07 Daig Corporation Process and device for the treatment of atrial arrhythmia
US6508828B1 (en) * 2000-11-03 2003-01-21 Radi Medical Systems Ab Sealing device and wound closure device
US6512458B1 (en) * 1998-04-08 2003-01-28 Canon Kabushiki Kaisha Method and apparatus for detecting failure in solar cell module, and solar cell module
US6511479B2 (en) * 2000-02-28 2003-01-28 Conmed Corporation Electrosurgical blade having directly adhered uniform coating of silicone release material and method of manufacturing same
US20030022822A1 (en) * 1998-01-30 2003-01-30 David Michalovich Novel compounds
US20040006333A1 (en) * 1994-09-09 2004-01-08 Cardiofocus, Inc. Coaxial catheter instruments for ablation with radiant energy
US6676657B2 (en) * 2000-12-07 2004-01-13 The United States Of America As Represented By The Department Of Health And Human Services Endoluminal radiofrequency cauterization system
US6676685B2 (en) * 1999-02-22 2004-01-13 Tyco Healthcare Group Lp Arterial hole closure apparatus
US20040010298A1 (en) * 2001-12-27 2004-01-15 Gregory Altshuler Method and apparatus for improved vascular related treatment
US6679904B2 (en) * 1996-10-17 2004-01-20 Malachy Gleeson Device for closure of puncture wound
US6689126B1 (en) * 1997-09-11 2004-02-10 Vnus Medical Technologies, Inc. Expandable vein ligator catheter and method of use
US20040030348A1 (en) * 1998-11-06 2004-02-12 St. Jude Medical Atg, Inc. Medical graft connector and methods of making and installing same
US6840666B2 (en) * 2002-01-23 2005-01-11 Marena Systems Corporation Methods and systems employing infrared thermography for defect detection and analysis
US6846321B2 (en) * 2000-06-21 2005-01-25 Cardiodex, Ltd. Mechanical method and apparatus for enhancing hemostatis following arterial catheterization
US6984219B2 (en) * 1999-09-23 2006-01-10 Mark Ashby Depth and puncture control for blood vessel hemostasis system
US6997926B2 (en) * 2002-02-04 2006-02-14 Boston Scientific Scimed, Inc. Resistance heated tissue morcellation
US7001398B2 (en) * 2000-12-07 2006-02-21 Integrated Vascular Systems, Inc. Closure device and methods for making and using them
US7160297B2 (en) * 2002-12-12 2007-01-09 Orion Industries, Ltd. Anti-microbial electrosurgical electrode and method of manufacturing the same
US20070010391A1 (en) * 2005-07-05 2007-01-11 Ceradyne, Inc. Lightweight boron carbide materials with improved mechanical properties and process for their manufacture
US7164353B2 (en) * 2004-12-22 2007-01-16 Avery Dennison Corporation Method and system for testing RFID devices
US20070021770A1 (en) * 1995-09-15 2007-01-25 Boston Scientific Scimed, Inc. Apparatus and Method for Percutaneous Sealing of Blood Vessel Punctures
US20070021746A1 (en) * 2004-06-07 2007-01-25 Boston Scientific Scimend, Inc. (Formerly Known As Scimed Life Systems, Inc.) Ablation catheters having slidable anchoring capability and methods of using same
US7184811B2 (en) * 1999-11-22 2007-02-27 Boston Scientific Scimed, Inc. Apparatus for mapping and coagulating soft tissue in or around body orifices
US20080009747A1 (en) * 2005-02-02 2008-01-10 Voyage Medical, Inc. Transmural subsurface interrogation and ablation
US20080015569A1 (en) * 2005-02-02 2008-01-17 Voyage Medical, Inc. Methods and apparatus for treatment of atrial fibrillation
US20080039829A1 (en) * 1997-09-11 2008-02-14 Goldman Mitchel P Method and apparatus for applying energy to biological tissue including the use of tumescent tissue compression

Family Cites Families (332)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US524417A (en) 1894-08-14 Combined bevel and square
US1731069A (en) 1929-10-08 Surgical instrument
US1596004A (en) 1923-04-04 1926-08-17 Bengoa Miguel Becerro De Hypodermic syringe
US1881250A (en) 1929-06-20 1932-10-04 Tomlinson George Milton Electrosurgical instrument
US1983669A (en) 1933-04-19 1934-12-11 Gen Electric X Ray Corp Electrode
US2808833A (en) 1952-12-06 1957-10-08 Birtcher Corp Gas blanketed clotting instrument
US2790442A (en) * 1955-09-06 1957-04-30 Donaldson John Shearman Cannular surgical instrument
US3100489A (en) 1957-09-30 1963-08-13 Medtronic Inc Cautery device
US4198957A (en) * 1967-11-09 1980-04-22 Robert F. Shaw Method of using an electrically heated surgical cutting instrument
CH497505A (en) * 1967-12-06 1970-10-15 Ciba Geigy Azo pigment dyes for polsyiloxanes etc
US3532095A (en) 1968-06-21 1970-10-06 Weck & Co Inc Edward Electrosurgical instrument
US3595238A (en) 1968-08-09 1971-07-27 Stanislav Alexeevich Gavrilov Electrosurgical apparatus to coagulate biological tissues
US3613682A (en) 1970-02-05 1971-10-19 Concept Disposable cauteries
US3699967A (en) 1971-04-30 1972-10-24 Valleylab Inc Electrosurgical generator
US3825004A (en) 1972-09-13 1974-07-23 Durden Enterprises Ltd Disposable electrosurgical cautery
US3801800A (en) * 1972-12-26 1974-04-02 Valleylab Inc Isolating switching circuit for an electrosurgical generator
US3801766A (en) * 1973-01-22 1974-04-02 Valleylab Inc Switching means for an electro-surgical device including particular contact means and particular printed-circuit mounting means
US3874388A (en) * 1973-02-12 1975-04-01 Ochsner Med Found Alton Shunt defect closure system
US3963030A (en) 1973-04-16 1976-06-15 Valleylab, Inc. Signal generating device and method for producing coagulation electrosurgical current
DE2324658B2 (en) 1973-05-16 1977-06-30 Richard Wolf Gmbh, 7134 Knittlingen PROBE FOR COAGULATING BODY TISSUE
US4016881A (en) * 1973-07-04 1977-04-12 Centre De Recherche Industrielle Du Quebec Instrument for use in laparoscopic tubal cauterization
US3929137A (en) 1973-11-12 1975-12-30 Dentsply Res & Dev Sonic warning for electrosurgical device
US3886944A (en) 1973-11-19 1975-06-03 Khosrow Jamshidi Microcautery device
US3978863A (en) 1974-06-06 1976-09-07 Bruce E. Fettel Expanding tip embolectomy catheter with indicator balloon
JPS5710740B2 (en) 1974-06-17 1982-02-27
US4043342A (en) 1974-08-28 1977-08-23 Valleylab, Inc. Electrosurgical devices having sesquipolar electrode structures incorporated therein
US4054143A (en) 1975-04-26 1977-10-18 Richard Wolf Gmbh Single-pole coagulation forceps
US4359052A (en) 1976-01-26 1982-11-16 Concept Inc. Removable tip cautery
US4051855A (en) 1976-02-06 1977-10-04 Ipco Hospital Supply Corporation, Whaledent International Division Electrosurgical unit
MX144149A (en) 1976-04-28 1981-09-02 Kendall & Co IMPROVED DEVICE TO VERIFY THE POSITION OF A NEEDLE IN THE BODY OF A PATIENT
GB1511557A (en) 1976-09-27 1978-05-24 Monga L Catheters
US4112950A (en) 1976-10-22 1978-09-12 Aspen Laboratories Medical electronic apparatus and components
US4122853A (en) 1977-03-14 1978-10-31 Spectra-Med Infrared laser photocautery device
US4168708A (en) 1977-04-20 1979-09-25 Medical Engineering Corp. Blood vessel occlusion means suitable for use in anastomosis
US4202337A (en) 1977-06-14 1980-05-13 Concept, Inc. Bipolar electrosurgical knife
US4327709A (en) 1978-03-06 1982-05-04 Datascope Corp. Apparatus and method for the percutaneous introduction of intra-aortic balloons into the human body
US4215699A (en) 1978-04-03 1980-08-05 The Kendall Company Position indicating device
US4228800A (en) 1978-04-04 1980-10-21 Concept, Inc. Bipolar electrosurgical knife
US4211230A (en) * 1978-07-31 1980-07-08 Sybron Corporation Electrosurgical coagulation
US4273127A (en) 1978-10-12 1981-06-16 Research Corporation Method for cutting and coagulating tissue
US4418692A (en) 1978-11-17 1983-12-06 Guay Jean Louis Device for treating living tissue with an electric current
US4230119A (en) 1978-12-01 1980-10-28 Medical Engineering Corp. Micro-hemostat
US4271847A (en) 1979-06-28 1981-06-09 Medtronic, Inc. Temporary adjustable bipolar lead
US4271839A (en) 1979-07-25 1981-06-09 Thomas J. Fogarty Dilation catheter method and apparatus
US4269174A (en) 1979-08-06 1981-05-26 Medical Dynamics, Inc. Transcutaneous vasectomy apparatus and method
US4848337A (en) 1979-09-10 1989-07-18 Shaw Robert F Abherent surgical instrument and method
CA1161326A (en) 1979-09-10 1984-01-31 Robert F. Shaw Abherent surgical instrument and method
US4303073A (en) 1980-01-17 1981-12-01 Medical Plastics, Inc. Electrosurgery safety monitor
GB2071500B (en) 1980-02-27 1984-03-21 Nath G Coagulator
WO1981003271A1 (en) 1980-05-13 1981-11-26 American Hospital Supply Corp A multipolar electrosurgical device
US4522205A (en) 1980-09-03 1985-06-11 The University Court Of The University Of Edinburgh Therapeutic device and method of inducing thrombosis in a blood vessel
US4390018A (en) 1980-09-15 1983-06-28 Zukowski Henry J Method for preventing loss of spinal fluid after spinal tap
US4411266A (en) 1980-09-24 1983-10-25 Cosman Eric R Thermocouple radio frequency lesion electrode
US4353371A (en) 1980-09-24 1982-10-12 Cosman Eric R Longitudinally, side-biting, bipolar coagulating, surgical instrument
US4481057A (en) 1980-10-28 1984-11-06 Oximetrix, Inc. Cutting device and method of manufacture
US4364392A (en) 1980-12-04 1982-12-21 Wisconsin Alumni Research Foundation Detachable balloon catheter
US4476862A (en) 1980-12-08 1984-10-16 Pao David S C Method of scleral marking
US5116332A (en) 1981-03-11 1992-05-26 Lottick Edward A Electrocautery hemostat
IT8104805V0 (en) * 1981-03-31 1981-03-31 Panda Srl EXHAUST SILENCER, IN PARTICULAR FOR PISTOLS AND PNEUMATIC EQUIPMENT
US4404971A (en) 1981-04-03 1983-09-20 Leveen Harry H Dual balloon catheter
US4520823A (en) 1981-04-03 1985-06-04 Leveen Harry H Catheter with separable balloons
US4483338A (en) 1981-06-12 1984-11-20 Raychem Corporation Bi-Polar electrocautery needle
US4352924A (en) 1981-06-29 1982-10-05 Eastman Kodak Company Thermosetting powder coating compositions
EP0075860A3 (en) 1981-09-24 1984-12-27 James Robert Morris Microsurgical laser
US4470415A (en) 1982-08-19 1984-09-11 The Johns Hopkins University Sutureless vascular anastomosis means and method
US4498475A (en) * 1982-08-27 1985-02-12 Ipco Corporation Electrosurgical unit
US4492231A (en) * 1982-09-17 1985-01-08 Auth David C Non-sticking electrocautery system and forceps
US4548207A (en) 1982-11-17 1985-10-22 Mentor O & O, Inc. Disposable coagulator
US4672969A (en) 1983-10-06 1987-06-16 Sonomo Corporation Laser healing method
US4854320A (en) 1983-10-06 1989-08-08 Laser Surgery Software, Inc. Laser healing method and apparatus
DE3390567T1 (en) * 1983-12-21 1985-12-12 Char'kovskij naučno-issledovatel'skij institut obščej i neotložnoj chirurgii, Char'kov Bipolar electrocoagulator
US4671274A (en) 1984-01-30 1987-06-09 Kharkovsky Nauchno-Issledovatelsky Institut Obschei I Bipolar electrosurgical instrument
CA1221596A (en) * 1984-03-09 1987-05-12 David Evans Surgical needle
USRE33925E (en) 1984-05-22 1992-05-12 Cordis Corporation Electrosurgical catheter aned method for vascular applications
US4682596A (en) 1984-05-22 1987-07-28 Cordis Corporation Electrosurgical catheter and method for vascular applications
JPS6131142A (en) 1984-07-25 1986-02-13 富士写真光機株式会社 Blood vessel anastomosis laser probe
DE3532621A1 (en) 1984-09-13 1986-03-20 Olympus Optical Co., Ltd., Tokio/Tokyo CAUTERIZATION BLOODSTYLE DEVICE
DE3532603A1 (en) 1984-09-13 1986-03-20 Olympus Optical Co., Ltd., Tokio/Tokyo CAUTERIZATION BLOODSTYLE DEVICE
US4848339A (en) 1984-09-17 1989-07-18 Xintec Corporation Laser heated intravascular cautery cap assembly
GR851148B (en) * 1985-05-13 1985-05-22 Papantonakos Apostolos
US4716897A (en) * 1985-07-15 1988-01-05 Olympus Optical Co., Ltd. Electrosurgical apparatus
AT385894B (en) 1985-10-04 1988-05-25 Basem Dr Nashef TUBULAR PROBE
US4735201A (en) * 1986-01-30 1988-04-05 The Beth Israel Hospital Association Optical fiber with detachable metallic tip for intravascular laser coagulation of arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas
DE3610419A1 (en) 1986-03-27 1987-10-01 Pfrimmer Viggo Gmbh Co Kg CATHETER FOR PERCUTANEOUS GASTROSTOMY
JPS62236560A (en) 1986-04-09 1987-10-16 テルモ株式会社 Catheter for repairing blood vessel
US4709698A (en) 1986-05-14 1987-12-01 Thomas J. Fogarty Heatable dilation catheter
DE3689889D1 (en) 1986-07-17 1994-07-07 Erbe Elektromedizin High-frequency surgical device for the thermal coagulation of biological tissues.
US4760847A (en) 1986-08-18 1988-08-02 Vincent Vaillancourt Depth measuring device
US5215103A (en) 1986-11-14 1993-06-01 Desai Jawahar M Catheter for mapping and ablation and method therefor
US4765331A (en) 1987-02-10 1988-08-23 Circon Corporation Electrosurgical device with treatment arc of less than 360 degrees
US4848352A (en) 1987-02-13 1989-07-18 Telectronics, N.V. Method for cardiac pacing and sensing using combination of electrodes
US4744364A (en) 1987-02-17 1988-05-17 Intravascular Surgical Instruments, Inc. Device for sealing percutaneous puncture in a vessel
US4852568A (en) 1987-02-17 1989-08-01 Kensey Nash Corporation Method and apparatus for sealing an opening in tissue of a living being
US4869248A (en) 1987-04-17 1989-09-26 Narula Onkar S Method and apparatus for localized thermal ablation
DE3722142A1 (en) 1987-06-17 1989-01-05 S & T Spingler Tritt Chirurgis SPRING PLIERS OR TWEEZERS, IN PARTICULAR COAGULATION TWEEZERS
US4943290A (en) 1987-06-23 1990-07-24 Concept Inc. Electrolyte purging electrode tip
US4836204A (en) 1987-07-06 1989-06-06 Landymore Roderick W Method for effecting closure of a perforation in the septum of the heart
US4850960A (en) 1987-07-08 1989-07-25 Joseph Grayzel Diagonally tapered, bevelled tip introducing catheter and sheath and method for insertion
US4790819A (en) 1987-08-24 1988-12-13 American Cyanamid Company Fibrin clot delivery device and method
US4920980A (en) 1987-09-14 1990-05-01 Cordis Corporation Catheter with controllable tip
IT1211530B (en) 1987-11-16 1989-11-03 Consiglio Nazionale Ricerche AREA OF THE POINT OF ORIGIN OF ARITCATERERE FOR ENDOCARDIC BIOPSY AND MY VENTRICULARS THAT CAN BE USED ALSO FOR THE INDIVIDUAL
US5035695A (en) 1987-11-30 1991-07-30 Jaroy Weber, Jr. Extendable electrocautery surgery apparatus and method
DE3743578A1 (en) 1987-12-22 1989-07-13 Andreas Dr Zeiher BALLOON CATHETER FOR RECANALIZING STENOSES IN BODY CHANNELS, IN PARTICULAR CORONARY VESSELS AND PERIPHERAL ARTERIAL VESSELS
US4921478A (en) 1988-02-23 1990-05-01 C. R. Bard, Inc. Cerebral balloon angioplasty system
US5053046A (en) 1988-08-22 1991-10-01 Woodrow W. Janese Dural sealing needle and method of use
US4917089A (en) * 1988-08-29 1990-04-17 Sideris Eleftherios B Buttoned device for the transvenous occlusion of intracardiac defects
US5159925A (en) 1988-09-09 1992-11-03 Gynelab, Inc. Cauterizing apparatus and method for laparoscopic cholecystostomy, gallbladder ablation and treatment of benign prostate hypertrophy
US4929246A (en) 1988-10-27 1990-05-29 C. R. Bard, Inc. Method for closing and sealing an artery after removing a catheter
US5151098A (en) 1990-07-23 1992-09-29 Hanspeter Loertscher Apparatus for controlled tissue ablation
DE3838840C2 (en) 1988-11-17 1997-02-20 Leibinger Gmbh High frequency coagulation device for surgical purposes
US4960133A (en) 1988-11-21 1990-10-02 Brunswick Manufacturing Co., Inc. Esophageal electrode
US5257635A (en) 1988-11-25 1993-11-02 Sensor Electronics, Inc. Electrical heating catheter
US5230349A (en) 1988-11-25 1993-07-27 Sensor Electronics, Inc. Electrical heating catheter
US4961729A (en) 1988-12-13 1990-10-09 Vaillancourt Vincent L Catheter insertion assembly
US5073166A (en) 1989-02-15 1991-12-17 Medical Innovations Corporation Method and apparatus for emplacement of a gastrostomy catheter
US4938761A (en) 1989-03-06 1990-07-03 Mdt Corporation Bipolar electrosurgical forceps
US4946463A (en) 1989-04-10 1990-08-07 Pioneering Technologies, Inc. Vessel occluder
US4979948A (en) 1989-04-13 1990-12-25 Purdue Research Foundation Method and apparatus for thermally destroying a layer of an organ
US5006119A (en) * 1989-05-25 1991-04-09 Engineering & Research Associates, Inc. Hollow core coaxial catheter
DE4017626A1 (en) 1989-05-31 1990-12-06 Kyocera Corp BLUTGEFAESSKOAGULATIONS - / - hemostatic DEVICE
US5049148A (en) 1989-06-29 1991-09-17 Mehl Thomas L Radio frequency hair removal tweezer
US5009656A (en) 1989-08-17 1991-04-23 Mentor O&O Inc. Bipolar electrosurgical instrument
JPH0380847A (en) * 1989-08-22 1991-04-05 Olympus Optical Co Ltd Patient electrode for high frequency treatment
US5057105A (en) 1989-08-28 1991-10-15 The University Of Kansas Med Center Hot tip catheter assembly
US5220924A (en) 1989-09-28 1993-06-22 Frazin Leon J Doppler-guided retrograde catheterization using transducer equipped guide wire
US5038789A (en) 1989-09-28 1991-08-13 Frazin Leon J Method and device for doppler-guided retrograde catheterization
DE3937700C2 (en) 1989-11-13 1998-02-19 Sutter Hermann Select Med Tech Bipolar coagulation forceps with switch
US5061274A (en) 1989-12-04 1991-10-29 Kensey Nash Corporation Plug device for sealing openings and method of use
US5226908A (en) 1989-12-05 1993-07-13 Inbae Yoon Multi-functional instruments and stretchable ligating and occluding devices
US5013312A (en) 1990-03-19 1991-05-07 Everest Medical Corporation Bipolar scalpel for harvesting internal mammary artery
US5131394A (en) 1990-03-28 1992-07-21 Gehlbach Steve M Ultrasonic guided needle
US5122137A (en) 1990-04-27 1992-06-16 Boston Scientific Corporation Temperature controlled rf coagulation
US5021059A (en) 1990-05-07 1991-06-04 Kensey Nash Corporation Plug device with pulley for sealing punctures in tissue and methods of use
US5103804A (en) 1990-07-03 1992-04-14 Boston Scientific Corporation Expandable tip hemostatic probes and the like
EP0476178A1 (en) 1990-09-21 1992-03-25 Bioplex Medical B.V. Device for placing styptic material on perforated blood vessels
US5391183A (en) 1990-09-21 1995-02-21 Datascope Investment Corp Device and method sealing puncture wounds
US5141515A (en) 1990-10-11 1992-08-25 Eberbach Mark A Apparatus and methods for repairing hernias
DE4032471C2 (en) 1990-10-12 1997-02-06 Delma Elektro Med App Electrosurgical device
US5147316A (en) 1990-11-19 1992-09-15 Castillenti Thomas A Laparoscopic trocar with self-locking port sleeve
US5419765A (en) 1990-12-27 1995-05-30 Novoste Corporation Wound treating device and method for treating wounds
US5129882A (en) * 1990-12-27 1992-07-14 Novoste Corporation Wound clotting device and method of using same
US5221259A (en) 1990-12-27 1993-06-22 Novoste Corporation Wound treating device and method of using same
US5108420A (en) 1991-02-01 1992-04-28 Temple University Aperture occlusion device
US5156613A (en) 1991-02-13 1992-10-20 Interface Biomedical Laboratories Corp. Collagen welding rod material for use in tissue welding
AU660444B2 (en) 1991-02-15 1995-06-29 Ingemar H. Lundquist Torquable catheter and method
US5147357A (en) 1991-03-18 1992-09-15 Rose Anthony T Medical instrument
US5217460A (en) 1991-03-22 1993-06-08 Knoepfler Dennis J Multiple purpose forceps
US5133714A (en) 1991-05-06 1992-07-28 Kirwan Surgical Products, Inc. Electrosurgical suction coagulator
US5217451A (en) 1991-05-24 1993-06-08 Dexide, Inc. Gear activated trocar assembly
US5207675A (en) 1991-07-15 1993-05-04 Jerome Canady Surgical coagulation device
US5217459A (en) 1991-08-27 1993-06-08 William Kamerling Method and instrument for performing eye surgery
US5349166A (en) 1991-10-31 1994-09-20 Engineering & Research Associates, Inc. RF generator for plastic tubing sealers
US5411520A (en) 1991-11-08 1995-05-02 Kensey Nash Corporation Hemostatic vessel puncture closure system utilizing a plug located within the puncture tract spaced from the vessel, and method of use
US5222974A (en) 1991-11-08 1993-06-29 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5676689A (en) 1991-11-08 1997-10-14 Kensey Nash Corporation Hemostatic puncture closure system including vessel location device and method of use
US5258000A (en) 1991-11-25 1993-11-02 Cook Incorporated Tissue aperture repair device
US5211624A (en) 1991-12-09 1993-05-18 Cinberg James Z Surgical closure device method
US6056768A (en) 1992-01-07 2000-05-02 Cates; Christopher U. Blood vessel sealing system
US5304214A (en) 1992-01-21 1994-04-19 Med Institute, Inc. Transurethral ablation catheter
GB9204217D0 (en) * 1992-02-27 1992-04-08 Goble Nigel M Cauterising apparatus
US5158561A (en) 1992-03-23 1992-10-27 Everest Medical Corporation Monopolar polypectomy snare with coagulation electrode
US5217024A (en) 1992-03-27 1993-06-08 Dorsey Denis P Tissue sampling device with visual and tactile indicator
US5217458A (en) 1992-04-09 1993-06-08 Everest Medical Corporation Bipolar biopsy device utilizing a rotatable, single-hinged moving element
WO1993021844A1 (en) * 1992-04-23 1993-11-11 Scimed Life Systems, Inc. Apparatus and method for sealing vascular punctures
US5810810A (en) 1992-04-23 1998-09-22 Scimed Life Systems, Inc. Apparatus and method for sealing vascular punctures
US6063085A (en) 1992-04-23 2000-05-16 Scimed Life Systems, Inc. Apparatus and method for sealing vascular punctures
US5458573A (en) 1992-05-01 1995-10-17 American Biomed, Inc. Everting toposcopic dilation catheter
US5221281A (en) 1992-06-30 1993-06-22 Valleylab Inc. Electrosurgical tubular trocar
US5413571A (en) 1992-07-16 1995-05-09 Sherwood Medical Company Device for sealing hemostatic incisions
US5258006A (en) 1992-08-21 1993-11-02 Everest Medical Corporation Bipolar electrosurgical forceps
US5342393A (en) 1992-08-27 1994-08-30 Duke University Method and device for vascular repair
US5306254A (en) 1992-10-01 1994-04-26 Kensey Nash Corporation Vessel position locating device and method of use
US6398782B1 (en) 1992-10-13 2002-06-04 Edwards Lifesciences Corporation Bipolar vascular sealing apparatus and methods
US5415657A (en) 1992-10-13 1995-05-16 Taymor-Luria; Howard Percutaneous vascular sealing method
US5364389A (en) 1992-11-25 1994-11-15 Premier Laser Systems, Inc. Method and apparatus for sealing and/or grasping luminal tissue
US5304117A (en) 1992-11-27 1994-04-19 Wilk Peter J Closure method for use in laparoscopic surgery
US5342359A (en) 1993-02-05 1994-08-30 Everest Medical Corporation Bipolar coagulation device
US5320639A (en) 1993-03-12 1994-06-14 Meadox Medicals, Inc. Vascular plug delivery system
DE69333783T2 (en) * 1993-04-23 2005-08-25 Scimed Life Systems, Inc., Maple Grove DEVICE FOR CLOSING VASCULAR SPUNCTIONS
US5419195A (en) 1993-04-30 1995-05-30 Westinghouse Electric Corporation Ultrasonic booted head probe for motor bore inspection
US6832996B2 (en) 1995-06-07 2004-12-21 Arthrocare Corporation Electrosurgical systems and methods for treating tissue
US5626601A (en) 1995-10-27 1997-05-06 Gary Gershony Vascular sealing apparatus and method
AU7099994A (en) 1993-06-04 1995-01-03 Kensey Nash Corporation Hemostatic vessel puncture closure with filament lock
FR2707862B1 (en) 1993-07-21 1995-10-13 Nycomed Lab Sa System for temporarily closing an orifice in a perforated organ, such as in particular a vessel.
US5431639A (en) 1993-08-12 1995-07-11 Boston Scientific Corporation Treating wounds caused by medical procedures
US5462529A (en) 1993-09-29 1995-10-31 Technology Development Center Adjustable treatment chamber catheter
US5370660A (en) 1993-11-01 1994-12-06 Cordis Corporation Apparatus and method for delivering a vessel plug into the body of a patient
US5417689A (en) 1994-01-18 1995-05-23 Cordis Corporation Thermal balloon catheter and method
US5658282A (en) 1994-01-18 1997-08-19 Endovascular, Inc. Apparatus for in situ saphenous vein bypass and less-invasive varicose vein treatment
WO1995032671A1 (en) 1994-06-01 1995-12-07 Perclose, Inc. Method and device for providing vascular hemostasis
US6142994A (en) 1994-10-07 2000-11-07 Ep Technologies, Inc. Surgical method and apparatus for positioning a diagnostic a therapeutic element within the body
US6152920A (en) 1997-10-10 2000-11-28 Ep Technologies, Inc. Surgical method and apparatus for positioning a diagnostic or therapeutic element within the body
US5624452A (en) 1995-04-07 1997-04-29 Ethicon Endo-Surgery, Inc. Hemostatic surgical cutting or stapling instrument
US5654566A (en) 1995-04-21 1997-08-05 Johnson; Mark B. Magnetic spin injected field effect transistor and method of operation
US5645566A (en) 1995-09-15 1997-07-08 Sub Q Inc. Apparatus and method for percutaneous sealing of blood vessel punctures
US5702387A (en) 1995-09-27 1997-12-30 Valleylab Inc Coated electrosurgical electrode
US6228082B1 (en) 1995-11-22 2001-05-08 Arthrocare Corporation Systems and methods for electrosurgical treatment of vascular disorders
US6287322B1 (en) 1995-12-07 2001-09-11 Loma Linda University Medical Center Tissue opening locator and everter and method
US6036687A (en) 1996-03-05 2000-03-14 Vnus Medical Technologies, Inc. Method and apparatus for treating venous insufficiency
US5728132A (en) * 1996-04-08 1998-03-17 Tricardia, L.L.C. Self-sealing vascular access device
US6002361A (en) 1996-04-30 1999-12-14 Trimble Navigation Limited Direct integrated approach to multipath signal identification
ATE375758T1 (en) 1996-08-06 2007-11-15 St Jude Med Puerto Rico Bv INTRODUCTION DEVICE FOR INSERTING A HEMOSTATIC OCCLUSION INTO AN INCISION
US5906636A (en) 1996-09-20 1999-05-25 Texas Heart Institute Heat treatment of inflamed tissue
US6091995A (en) * 1996-11-08 2000-07-18 Surx, Inc. Devices, methods, and systems for shrinking tissues
US5895386A (en) 1996-12-20 1999-04-20 Electroscope, Inc. Bipolar coagulation apparatus and method for arthroscopy
US5782861A (en) 1996-12-23 1998-07-21 Sub Q Inc. Percutaneous hemostasis device
US5951589A (en) 1997-02-11 1999-09-14 Biointerventional Corporation Expansile device for use in blood vessels and tracts in the body and tension application device for use therewith and method
US5782860A (en) 1997-02-11 1998-07-21 Biointerventional Corporation Closure device for percutaneous occlusion of puncture sites and tracts in the human body and method
US6056769A (en) 1997-02-11 2000-05-02 Biointerventional Corporation Expansile device for use in blood vessels and tracts in the body and tension application device for use therewith and method
US6464712B1 (en) 1997-02-11 2002-10-15 Biointerventional Corporation Expansile device for use in blood vessels and tracts in the body and method
US5836945A (en) 1997-02-20 1998-11-17 Perkins; Rodney C. Biological vessel harvesting device
US6626901B1 (en) 1997-03-05 2003-09-30 The Trustees Of Columbia University In The City Of New York Electrothermal instrument for sealing and joining or cutting tissue
US5941897A (en) 1997-05-09 1999-08-24 Myers; Gene E. Energy activated fibrin plug
US5944730A (en) 1997-05-19 1999-08-31 Cardio Medical Solutions, Inc. Device and method for assisting end-to-side anastomosis
US6409739B1 (en) 1997-05-19 2002-06-25 Cardio Medical Solutions, Inc. Device and method for assisting end-to side anastomosis
US5911719A (en) 1997-06-05 1999-06-15 Eggers; Philip E. Resistively heating cutting and coagulating surgical instrument
US5891138A (en) 1997-08-11 1999-04-06 Irvine Biomedical, Inc. Catheter system having parallel electrodes
US6111424A (en) 1997-09-04 2000-08-29 Lucent Technologies Inc. Testing method and apparatus for flat panel displays using infrared imaging
US6267761B1 (en) 1997-09-09 2001-07-31 Sherwood Services Ag Apparatus and method for sealing and cutting tissue
US6200312B1 (en) * 1997-09-11 2001-03-13 Vnus Medical Technologies, Inc. Expandable vein ligator catheter having multiple electrode leads
US5964782A (en) 1997-09-18 1999-10-12 Scimed Life Systems, Inc. Closure device and method
US6468272B1 (en) * 1997-10-10 2002-10-22 Scimed Life Systems, Inc. Surgical probe for supporting diagnostic and therapeutic elements in contact with tissue in or around body orifices
US6478808B2 (en) 1997-12-17 2002-11-12 Closys Corporation Clotting cascade initiating apparatus and methods of use and methods of closing wounds
US6104291A (en) 1998-01-09 2000-08-15 Intermec Ip Corp. Method and apparatus for testing RFID tags
WO1999040861A1 (en) 1998-02-17 1999-08-19 Baker James A Radiofrequency medical instrument for vessel welding
US6911028B2 (en) 1998-10-28 2005-06-28 John H. Shadduck Medical instrument working end and method for endoluminal treatments
US7674259B2 (en) 2000-12-09 2010-03-09 Tsunami Medtech Medical instruments and techniques for thermally-mediated therapies
US6450989B2 (en) * 1998-04-27 2002-09-17 Artemis Medical, Inc. Dilating and support apparatus with disease inhibitors and methods for use
US20030077795A1 (en) 1999-03-10 2003-04-24 Wilson C. Ron Cytochrome P450 monooxygenase and NADPH Cytochrome P450 oxidoreductase genes and proteins related to the omega hydroxylase complex of candida tropicals and methods relating thereto
US6740098B2 (en) 1998-05-11 2004-05-25 Surgical Connections, Inc. Surgical stabilizer devices and methods
US6322559B1 (en) 1998-07-06 2001-11-27 Vnus Medical Technologies, Inc. Electrode catheter having coil structure
US6048358A (en) 1998-07-13 2000-04-11 Barak; Shlomo Method and apparatus for hemostasis following arterial catheterization
JP2003521270A (en) * 1998-08-04 2003-07-15 フュージョン メディカル テクノロジーズ, インコーポレイテッド Percutaneous tissue tract occlusion assemblies and methods
US6093173A (en) * 1998-09-09 2000-07-25 Embol-X, Inc. Introducer/dilator with balloon protection and methods of use
US6123702A (en) 1998-09-10 2000-09-26 Scimed Life Systems, Inc. Systems and methods for controlling power in an electrosurgical probe
US6080183A (en) 1998-11-24 2000-06-27 Embol-X, Inc. Sutureless vessel plug and methods of use
US6210406B1 (en) * 1998-12-03 2001-04-03 Cordis Webster, Inc. Split tip electrode catheter and signal processing RF ablation system
US6235027B1 (en) 1999-01-21 2001-05-22 Garrett D. Herzon Thermal cautery surgical forceps
US6120524A (en) 1999-02-16 2000-09-19 Taheri; Syde A. Device for closing an arterial puncture and method
US6743196B2 (en) * 1999-03-01 2004-06-01 Coaxia, Inc. Partial aortic occlusion devices and methods for cerebral perfusion augmentation
US6695859B1 (en) 1999-04-05 2004-02-24 Coalescent Surgical, Inc. Apparatus and methods for anastomosis
US20010007070A1 (en) 1999-04-05 2001-07-05 Medtronic, Inc. Ablation catheter assembly and method for isolating a pulmonary vein
US6537299B1 (en) * 1999-04-05 2003-03-25 Ethicon, Inc. Intravascular hemostasis device and method
US6352533B1 (en) 1999-05-03 2002-03-05 Alan G. Ellman Electrosurgical handpiece for treating tissue
US6428550B1 (en) 1999-05-18 2002-08-06 Cardica, Inc. Sutureless closure and deployment system for connecting blood vessels
AU5160500A (en) 1999-05-28 2000-12-18 Cohesion Technologies, Inc. Apparatuses, methods and compositions for closing tissue puncture openings
US6626899B2 (en) 1999-06-25 2003-09-30 Nidus Medical, Llc Apparatus and methods for treating tissue
US6451007B1 (en) 1999-07-29 2002-09-17 Dale E. Koop Thermal quenching of tissue
US6607520B2 (en) 1999-09-15 2003-08-19 The General Hospital Corporation Coiled ablation catheter system
US6231561B1 (en) * 1999-09-20 2001-05-15 Appriva Medical, Inc. Method and apparatus for closing a body lumen
US6306133B1 (en) 1999-10-02 2001-10-23 Quantum Cor Incorporated Ablation catheter system and methods for repairing a valvular annulus
AU2619301A (en) 1999-10-25 2001-06-06 Therus Corporation Use of focused ultrasound for vascular sealing
US6911032B2 (en) 1999-11-18 2005-06-28 Scimed Life Systems, Inc. Apparatus and method for compressing body tissue
US6942674B2 (en) 2000-01-05 2005-09-13 Integrated Vascular Systems, Inc. Apparatus and methods for delivering a closure device
JP2001190561A (en) * 2000-01-12 2001-07-17 Olympus Optical Co Ltd Coagulation treatment tool
US7033352B1 (en) 2000-01-18 2006-04-25 Afx, Inc. Flexible ablation instrument
US6547806B1 (en) 2000-02-04 2003-04-15 Ni Ding Vascular sealing device and method of use
US6593853B1 (en) 2000-02-18 2003-07-15 Brady Worldwide, Inc. RFID label printing system
US6402745B1 (en) 2000-02-23 2002-06-11 Peter J. Wilk Intravenous whip electrode for vein ablation
US6443947B1 (en) 2000-03-01 2002-09-03 Alexei Marko Device for thermal ablation of a cavity
US6569161B2 (en) * 2000-03-02 2003-05-27 Stephen M. Zappala Retractable radiofrequency needle point electrode and methods for using same
AU2001268535A1 (en) 2000-06-20 2002-01-02 Starion Instruments, Inc. Devices and methods for repair of valves in the human body
WO2002005865A2 (en) 2000-07-14 2002-01-24 Sub-Q, Inc. Sheath-mounted arterial plug delivery device
US20030120256A1 (en) 2001-07-03 2003-06-26 Syntheon, Llc Methods and apparatus for sclerosing the wall of a varicose vein
US6890342B2 (en) * 2000-08-02 2005-05-10 Loma Linda University Method and apparatus for closing vascular puncture using hemostatic material
US7201725B1 (en) 2000-09-25 2007-04-10 Sub-Q, Inc. Device and method for determining a depth of an incision
US6626918B1 (en) 2000-10-06 2003-09-30 Medical Technology Group Apparatus and methods for positioning a vascular sheath
US7549987B2 (en) 2000-12-09 2009-06-23 Tsunami Medtech, Llc Thermotherapy device
US6969397B2 (en) 2000-12-14 2005-11-29 Ensure Medical, Inc. Guide wire element for positioning vascular closure devices and methods for use
DE60205780T2 (en) 2001-01-12 2006-05-18 Radi Medical Systems Ab Arterial wall occlusion device provided with a position indicator
EP1357842B1 (en) * 2001-01-16 2010-11-03 Cytyc Surgical Products Apparatus and method for treating venous reflux
US6669262B1 (en) 2001-02-16 2003-12-30 Crotty Corporation Clip lock visor
US6743195B2 (en) 2001-03-14 2004-06-01 Cardiodex Balloon method and apparatus for vascular closure following arterial catheterization
JP2002301088A (en) * 2001-04-05 2002-10-15 Olympus Optical Co Ltd Endoscopic treatment device
US6551313B1 (en) 2001-05-02 2003-04-22 John M. Levin Electrosurgical instrument with separate cutting and coagulating members
US7029489B1 (en) 2001-05-18 2006-04-18 Sub-Q, Inc. System and method for delivering hemostasis promoting material to a blood vessel puncture site
US6511010B1 (en) * 2001-07-03 2003-01-28 Flextronics International Optical fiber management installation appliance
US6657447B1 (en) 2001-07-31 2003-12-02 Xilnx, Inc. Liquid crystal method to localize metal short on multi-layer metal CMOS process
JP4671560B2 (en) 2001-08-29 2011-04-20 トッパン・フォームズ株式会社 Inspection method and inspection system for electrostatic coupling type RF-ID
US7070597B2 (en) 2001-10-18 2006-07-04 Surgrx, Inc. Electrosurgical working end for controlled energy delivery
US7025748B2 (en) 2001-11-08 2006-04-11 Boston Scientific Scimed, Inc. Sheath based blood vessel puncture locator and depth indicator
US7037322B1 (en) 2001-11-08 2006-05-02 Sub-Q, Inc. System and method for delivering hemostasis promoting material to a blood vessel puncture with a staging tube
US6814743B2 (en) 2001-12-26 2004-11-09 Origin Medsystems, Inc. Temporary seal and method for facilitating anastomosis
US7099717B2 (en) 2002-01-03 2006-08-29 Afx Inc. Catheter having improved steering
US6817743B2 (en) 2002-01-28 2004-11-16 Allen Sharper Vehicle wheel illumination system
JP2003220074A (en) 2002-01-30 2003-08-05 Olympus Optical Co Ltd Medical apparatus
US7007698B2 (en) 2002-04-03 2006-03-07 Boston Scientific Corporation Body lumen closure
AU2003237884A1 (en) 2002-05-15 2003-12-02 Stephen T. Flock Method and device for anastomoses
DE60200515T2 (en) 2002-06-12 2004-09-30 Radi Medical Systems Ab closure device
US6768086B2 (en) * 2002-07-08 2004-07-27 Sunbeam Products, Inc. Temperature sensor for a warming blanket
US6780177B2 (en) 2002-08-27 2004-08-24 Board Of Trustees Of The University Of Arkansas Conductive interstitial thermal therapy device
JP2006502628A (en) 2002-10-09 2006-01-19 シーメンス アクチエンゲゼルシヤフト Method and apparatus for operating a power switch
AU2003287511A1 (en) 2002-10-31 2004-05-25 Cooltouch, Incorporated Endovenous closure of varicose veins with mid infrared laser
US6719257B1 (en) 2003-01-09 2004-04-13 Tim L. Greene Adjustable stop for telescoping tubes
US7115127B2 (en) 2003-02-04 2006-10-03 Cardiodex, Ltd. Methods and apparatus for hemostasis following arterial catheterization
WO2005074364A2 (en) 2004-02-03 2005-08-18 Cardiodex Ltd. Methods and apparatus for hemostasis following arterial catheterization
US7223266B2 (en) 2003-02-04 2007-05-29 Cardiodex Ltd. Methods and apparatus for hemostasis following arterial catheterization
DE10304849A1 (en) 2003-02-06 2004-08-19 Institut für Neue Materialien gemeinnützige Gesellschaft mit beschränkter Haftung Chemomechanical production of functional colloids
US7257450B2 (en) 2003-02-13 2007-08-14 Coaptus Medical Corporation Systems and methods for securing cardiovascular tissue
US7225992B2 (en) 2003-02-13 2007-06-05 Avery Dennison Corporation RFID device tester and method
US7850654B2 (en) 2003-04-24 2010-12-14 St. Jude Medical Puerto Rico B.V. Device and method for positioning a closure device
US7101387B2 (en) 2003-04-30 2006-09-05 Scimed Life Systems, Inc. Radio frequency ablation cooling shield
US20040249324A1 (en) 2003-06-04 2004-12-09 John Louis Massage tool for applying localized pressure
US7331979B2 (en) 2003-06-04 2008-02-19 Access Closure, Inc. Apparatus and methods for sealing a vascular puncture
US8852229B2 (en) 2003-10-17 2014-10-07 Cordis Corporation Locator and closure device and method of use
US7896873B2 (en) 2003-12-01 2011-03-01 Biotronik Crm Patent Ag Electrode catheter for the electrotherapy of cardiac tissue
CA2553940A1 (en) 2004-01-30 2005-08-18 Nmt Medical, Inc. Devices, systems, and methods for closure of cardiac openings
US20080154303A1 (en) 2006-12-21 2008-06-26 Cardiva Medical, Inc. Hemostasis-enhancing device and method for its use
US9017374B2 (en) 2004-04-09 2015-04-28 Cardiva Medical, Inc. Device and method for sealing blood vessels
US7572274B2 (en) 2004-05-27 2009-08-11 Cardiva Medical, Inc. Self-tensioning vascular occlusion device and method for its use
US7993366B2 (en) 2004-05-27 2011-08-09 Cardiva Medical, Inc. Self-tensioning vascular occlusion device and method for its use
US7151442B1 (en) 2004-06-03 2006-12-19 National Semiconductor Corporation System, apparatus, and method for testing identification tags
US20060089637A1 (en) 2004-10-14 2006-04-27 Werneth Randell L Ablation catheter
JP5068662B2 (en) 2004-11-22 2012-11-07 カーディオデックス リミテッド Heat treatment technology for varicose veins
US20060190066A1 (en) 2005-02-23 2006-08-24 Worthen William J System and method for bringing hypothermia rapidly onboard
US8002742B2 (en) 2005-04-22 2011-08-23 Accessclosure, Inc. Apparatus and methods for sealing a puncture in tissue
US20060276836A1 (en) 2005-06-07 2006-12-07 Bergin Patrick J Hemostatic wire guided bandage and method of use
US7147634B2 (en) 2005-05-12 2006-12-12 Orion Industries, Ltd. Electrosurgical electrode and method of manufacturing same
US20080091193A1 (en) 2005-05-16 2008-04-17 James Kauphusman Irrigated ablation catheter having magnetic tip for magnetic field control and guidance
US20060271032A1 (en) 2005-05-26 2006-11-30 Chin Albert K Ablation instruments and methods for performing abalation
AU2006262447A1 (en) 2005-06-20 2007-01-04 Medtronic Ablation Frontiers Llc Ablation catheter
ITFI20050163A1 (en) 2005-07-22 2007-01-23 Luciano Alcidi DEVICE FOR ARTERIAL Haemostatic Interventions
US8920442B2 (en) 2005-08-24 2014-12-30 Abbott Vascular Inc. Vascular opening edge eversion methods and apparatuses
US20070213616A1 (en) 2005-10-20 2007-09-13 Thomas Anderson Systems and methods for arteriotomy localization
US20070198057A1 (en) 2006-02-21 2007-08-23 Daniel Gelbart Method and device for closing holes in tissue
US7154283B1 (en) 2006-02-22 2006-12-26 Avery Dennison Corporation Method of determining performance of RFID devices
JP2007323161A (en) 2006-05-30 2007-12-13 Toshiba Corp Communication equipment and communication method
US7789893B2 (en) 2006-09-12 2010-09-07 Boston Scientific Scimed, Inc. Method and apparatus for promoting hemostasis of a blood vessel puncture
WO2008033964A2 (en) 2006-09-13 2008-03-20 Accessclosure, Inc. Apparatus for sealing a vascular puncture
US7766208B2 (en) 2007-01-24 2010-08-03 Medtronic Vascular, Inc. Low-profile vascular closure systems and methods of using same
US8366706B2 (en) 2007-08-15 2013-02-05 Cardiodex, Ltd. Systems and methods for puncture closure
US20090149847A1 (en) 2007-10-05 2009-06-11 Cardiodex Ltd. Systems and methods for puncture closure

Patent Citations (100)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2144090A (en) * 1936-03-17 1939-01-17 Trice Spencer Talley Electrical hemostat
US3176114A (en) * 1962-07-16 1965-03-30 Richard F Kneisley Device for removing nasal hair
US3302635A (en) * 1963-09-19 1967-02-07 Fred E Pittman Semi-rigid device for marking internal bleeding
US3301258A (en) * 1963-10-03 1967-01-31 Medtronic Inc Method and apparatus for treating varicose veins
US3500828A (en) * 1966-08-31 1970-03-17 Fred W Podhora Intravenous catheter apparatus
US3636943A (en) * 1967-10-27 1972-01-25 Ultrasonic Systems Ultrasonic cauterization
US3794040A (en) * 1967-10-27 1974-02-26 Ultrasonic Systems Ultrasonic surgical procedures
US3494364A (en) * 1967-11-09 1970-02-10 Weck & Co Inc Edward Handle component for electro-surgical instrument
US3858586A (en) * 1971-03-11 1975-01-07 Martin Lessen Surgical method and electrode therefor
US3938527A (en) * 1973-07-04 1976-02-17 Centre De Recherche Industrielle De Quebec Instrument for laparoscopic tubal cauterization
US4011872A (en) * 1974-04-01 1977-03-15 Olympus Optical Co., Ltd. Electrical apparatus for treating affected part in a coeloma
US4003380A (en) * 1974-09-05 1977-01-18 F.L. Fisher Bipolar coagulation instrument
US4014343A (en) * 1975-04-25 1977-03-29 Neomed Incorporated Detachable chuck for electro-surgical instrument
US4007743A (en) * 1975-10-20 1977-02-15 American Hospital Supply Corporation Opening mechanism for umbrella-like intravascular shunt defect closure device
US4074718A (en) * 1976-03-17 1978-02-21 Valleylab, Inc. Electrosurgical instrument
US4900303A (en) * 1978-03-10 1990-02-13 Lemelson Jerome H Dispensing catheter and method
US4314555A (en) * 1979-02-20 1982-02-09 Terumo Corporation Intravascular catheter assembly
US4314559A (en) * 1979-12-12 1982-02-09 Corning Glass Works Nonstick conductive coating
US4317445A (en) * 1980-03-31 1982-03-02 Baxter Travenol Laboratories, Inc. Catheter insertion unit with separate flashback indication for the cannula
US4370980A (en) * 1981-03-11 1983-02-01 Lottick Edward A Electrocautery hemostat
US4424833A (en) * 1981-10-02 1984-01-10 C. R. Bard, Inc. Self sealing gasket assembly
US5002051A (en) * 1983-10-06 1991-03-26 Lasery Surgery Software, Inc. Method for closing tissue wounds using radiative energy beams
US4994060A (en) * 1984-09-17 1991-02-19 Xintec Corporation Laser heated cautery cap with transparent substrate
US4654024A (en) * 1985-09-04 1987-03-31 C.R. Bard, Inc. Thermorecanalization catheter and method for use
US4801293A (en) * 1985-10-09 1989-01-31 Anthony Jackson Apparatus and method for detecting probe penetration of human epidural space and injecting a therapeutic substance thereinto
US4890612A (en) * 1987-02-17 1990-01-02 Kensey Nash Corporation Device for sealing percutaneous puncture in a vessel
US5178620A (en) * 1988-06-10 1993-01-12 Advanced Angioplasty Products, Inc. Thermal dilatation catheter and method
USRE35755E (en) * 1989-05-12 1998-03-24 Scimed Life Systems, Inc. Method for inducing thrombosis in blood vessels
US5192302A (en) * 1989-12-04 1993-03-09 Kensey Nash Corporation Plug devices for sealing punctures and methods of use
US5087256A (en) * 1990-01-12 1992-02-11 Metcal Inc. Thermal atherectomy device
US5716325A (en) * 1990-03-02 1998-02-10 General Surgical Innovations, Inc. Arthroscopic retractors and method of using the same
US5088997A (en) * 1990-03-15 1992-02-18 Valleylab, Inc. Gas coagulation device
US5078743A (en) * 1990-04-19 1992-01-07 Abraham Mikalov Method of placing an esophageal voice prosthesis in a laryngectomized person
US5080660A (en) * 1990-05-11 1992-01-14 Applied Urology, Inc. Electrosurgical electrode
US5188602A (en) * 1990-07-12 1993-02-23 Interventional Thermodynamics, Inc. Method and device for delivering heat to hollow body organs
US5188634A (en) * 1990-07-13 1993-02-23 Trimedyne, Inc. Rotatable laser probe with beveled tip
US5282799A (en) * 1990-08-24 1994-02-01 Everest Medical Corporation Bipolar electrosurgical scalpel with paired loop electrodes
US5192300A (en) * 1990-10-01 1993-03-09 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5275616B1 (en) * 1990-10-01 1996-01-23 Quinton Instr Insertion assembly and method of inserting a vessel plug into the body of a patient
US5275616A (en) * 1990-10-01 1994-01-04 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5716375A (en) * 1990-10-01 1998-02-10 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5190541A (en) * 1990-10-17 1993-03-02 Boston Scientific Corporation Surgical instrument and method
US5085659A (en) * 1990-11-21 1992-02-04 Everest Medical Corporation Biopsy device with bipolar coagulation capability
US5183464A (en) * 1991-05-17 1993-02-02 Interventional Thermodynamics, Inc. Radially expandable dilator
US5290310A (en) * 1991-10-30 1994-03-01 Howmedica, Inc. Hemostatic implant introducer
US5282827A (en) * 1991-11-08 1994-02-01 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US6179863B1 (en) * 1991-11-08 2001-01-30 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5277696A (en) * 1991-11-19 1994-01-11 Delma Elektro- Und Medizinische Apparatebau Gesellschaft Mbh Medical high frequency coagulation instrument
US5281216A (en) * 1992-03-31 1994-01-25 Valleylab, Inc. Electrosurgical bipolar treating apparatus
US5593406A (en) * 1992-05-01 1997-01-14 Hemostatic Surgery Corporation Endoscopic instrument with auto-regulating heater and method of using same
US6350274B1 (en) * 1992-05-11 2002-02-26 Regen Biologics, Inc. Soft tissue closure systems
US5292332A (en) * 1992-07-27 1994-03-08 Lee Benjamin I Methods and device for percutanceous sealing of arterial puncture sites
US5383896A (en) * 1993-05-25 1995-01-24 Gershony; Gary Vascular sealing device
US5486195A (en) * 1993-07-26 1996-01-23 Myers; Gene Method and apparatus for arteriotomy closure
US5725551A (en) * 1993-07-26 1998-03-10 Myers; Gene Method and apparatus for arteriotomy closure
US5383899A (en) * 1993-09-28 1995-01-24 Hammerslag; Julius G. Method of using a surface opening adhesive sealer
US5728122A (en) * 1994-01-18 1998-03-17 Datascope Investment Corp. Guide wire with releaseable barb anchor
US20050038419A9 (en) * 1994-09-09 2005-02-17 Cardiofocus, Inc. Coaxial catheter instruments for ablation with radiant energy
US20040006333A1 (en) * 1994-09-09 2004-01-08 Cardiofocus, Inc. Coaxial catheter instruments for ablation with radiant energy
US5611798A (en) * 1995-03-02 1997-03-18 Eggers; Philip E. Resistively heated cutting and coagulating surgical instrument
US20070021770A1 (en) * 1995-09-15 2007-01-25 Boston Scientific Scimed, Inc. Apparatus and Method for Percutaneous Sealing of Blood Vessel Punctures
US7175646B2 (en) * 1995-09-15 2007-02-13 Boston Scientific Scimed, Inc. Apparatus and method for percutaneous sealing of blood vessel punctures
US5868778A (en) * 1995-10-27 1999-02-09 Vascular Solutions, Inc. Vascular sealing apparatus and method
US6033398A (en) * 1996-03-05 2000-03-07 Vnus Medical Technologies, Inc. Method and apparatus for treating venous insufficiency using directionally applied energy
US6022336A (en) * 1996-05-20 2000-02-08 Percusurge, Inc. Catheter system for emboli containment
US5879499A (en) * 1996-06-17 1999-03-09 Heartport, Inc. Method of manufacture of a multi-lumen catheter
US5728133A (en) * 1996-07-09 1998-03-17 Cardiologics, L.L.C. Anchoring device and method for sealing percutaneous punctures in vessels
US5728134A (en) * 1996-09-17 1998-03-17 Barak; Shlomo Method and apparatus for hemostasis
US6679904B2 (en) * 1996-10-17 2004-01-20 Malachy Gleeson Device for closure of puncture wound
US6033401A (en) * 1997-03-12 2000-03-07 Advanced Closure Systems, Inc. Vascular sealing device with microwave antenna
US6503247B2 (en) * 1997-06-27 2003-01-07 Daig Corporation Process and device for the treatment of atrial arrhythmia
US6179832B1 (en) * 1997-09-11 2001-01-30 Vnus Medical Technologies, Inc. Expandable catheter having two sets of electrodes
US20080039829A1 (en) * 1997-09-11 2008-02-14 Goldman Mitchel P Method and apparatus for applying energy to biological tissue including the use of tumescent tissue compression
US20080039793A1 (en) * 1997-09-11 2008-02-14 Goldman Mitchel P Method and apparatus for applying energy to biological tissue including the use of tumescent tissue compression
US6689126B1 (en) * 1997-09-11 2004-02-10 Vnus Medical Technologies, Inc. Expandable vein ligator catheter and method of use
US6682526B1 (en) * 1997-09-11 2004-01-27 Vnus Medical Technologies, Inc. Expandable catheter having two sets of electrodes, and method of use
US20030022822A1 (en) * 1998-01-30 2003-01-30 David Michalovich Novel compounds
US6512458B1 (en) * 1998-04-08 2003-01-28 Canon Kabushiki Kaisha Method and apparatus for detecting failure in solar cell module, and solar cell module
US6022361A (en) * 1998-10-09 2000-02-08 Biointerventional Corporation Device for introducing and polymerizing polymeric biomaterials in the human body and method
US20040030348A1 (en) * 1998-11-06 2004-02-12 St. Jude Medical Atg, Inc. Medical graft connector and methods of making and installing same
US6676685B2 (en) * 1999-02-22 2004-01-13 Tyco Healthcare Group Lp Arterial hole closure apparatus
US6984219B2 (en) * 1999-09-23 2006-01-10 Mark Ashby Depth and puncture control for blood vessel hemostasis system
US7184811B2 (en) * 1999-11-22 2007-02-27 Boston Scientific Scimed, Inc. Apparatus for mapping and coagulating soft tissue in or around body orifices
US7474909B2 (en) * 1999-11-22 2009-01-06 Boston Scientific Scimed, Inc. Apparatus for mapping and coagulating soft tissue in or around body orifices
US6511479B2 (en) * 2000-02-28 2003-01-28 Conmed Corporation Electrosurgical blade having directly adhered uniform coating of silicone release material and method of manufacturing same
US20020002371A1 (en) * 2000-03-24 2002-01-03 Acker David E. Apparatus and methods for intrabody thermal treatment
US6846321B2 (en) * 2000-06-21 2005-01-25 Cardiodex, Ltd. Mechanical method and apparatus for enhancing hemostatis following arterial catheterization
US20030005397A1 (en) * 2000-07-07 2003-01-02 Larsen Corey L. Method and apparatus for PCB array with compensated signal propagation
US6508828B1 (en) * 2000-11-03 2003-01-21 Radi Medical Systems Ab Sealing device and wound closure device
US7001398B2 (en) * 2000-12-07 2006-02-21 Integrated Vascular Systems, Inc. Closure device and methods for making and using them
US6676657B2 (en) * 2000-12-07 2004-01-13 The United States Of America As Represented By The Department Of Health And Human Services Endoluminal radiofrequency cauterization system
US20040010298A1 (en) * 2001-12-27 2004-01-15 Gregory Altshuler Method and apparatus for improved vascular related treatment
US6840666B2 (en) * 2002-01-23 2005-01-11 Marena Systems Corporation Methods and systems employing infrared thermography for defect detection and analysis
US6997926B2 (en) * 2002-02-04 2006-02-14 Boston Scientific Scimed, Inc. Resistance heated tissue morcellation
US7160297B2 (en) * 2002-12-12 2007-01-09 Orion Industries, Ltd. Anti-microbial electrosurgical electrode and method of manufacturing the same
US20070021746A1 (en) * 2004-06-07 2007-01-25 Boston Scientific Scimend, Inc. (Formerly Known As Scimed Life Systems, Inc.) Ablation catheters having slidable anchoring capability and methods of using same
US7164353B2 (en) * 2004-12-22 2007-01-16 Avery Dennison Corporation Method and system for testing RFID devices
US20080009747A1 (en) * 2005-02-02 2008-01-10 Voyage Medical, Inc. Transmural subsurface interrogation and ablation
US20080015569A1 (en) * 2005-02-02 2008-01-17 Voyage Medical, Inc. Methods and apparatus for treatment of atrial fibrillation
US20070010391A1 (en) * 2005-07-05 2007-01-11 Ceradyne, Inc. Lightweight boron carbide materials with improved mechanical properties and process for their manufacture

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8372072B2 (en) 2003-02-04 2013-02-12 Cardiodex Ltd. Methods and apparatus for hemostasis following arterial catheterization
US8366706B2 (en) 2007-08-15 2013-02-05 Cardiodex, Ltd. Systems and methods for puncture closure
US20090118729A1 (en) * 2007-11-07 2009-05-07 Mirabilis Medica Inc. Hemostatic spark erosion tissue tunnel generator with integral treatment providing variable volumetric necrotization of tissue
US20090118725A1 (en) * 2007-11-07 2009-05-07 Mirabilis Medica, Inc. Hemostatic tissue tunnel generator for inserting treatment apparatus into tissue of a patient
US8187270B2 (en) * 2007-11-07 2012-05-29 Mirabilis Medica Inc. Hemostatic spark erosion tissue tunnel generator with integral treatment providing variable volumetric necrotization of tissue
US8439907B2 (en) 2007-11-07 2013-05-14 Mirabilis Medica Inc. Hemostatic tissue tunnel generator for inserting treatment apparatus into tissue of a patient
US20140164499A1 (en) * 2011-08-01 2014-06-12 Infobank Corp. Wireless communication device, information processing method and recording medium
US9961537B2 (en) * 2011-08-01 2018-05-01 Infobank Corp. Wireless communication device, information processing method and recording medium

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