US3878839A - Cardiac assist apparatus - Google Patents

Cardiac assist apparatus Download PDF

Info

Publication number
US3878839A
US3878839A US332629A US33262973A US3878839A US 3878839 A US3878839 A US 3878839A US 332629 A US332629 A US 332629A US 33262973 A US33262973 A US 33262973A US 3878839 A US3878839 A US 3878839A
Authority
US
United States
Prior art keywords
pressure
housing
patient
body portion
actuation means
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US332629A
Inventor
Robert L Norton
William C Birtwell
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Hemodyne Inc
Original Assignee
Hemodyne Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Hemodyne Inc filed Critical Hemodyne Inc
Priority to US332629A priority Critical patent/US3878839A/en
Priority to JP49017722A priority patent/JPS6021739B2/en
Application granted granted Critical
Publication of US3878839A publication Critical patent/US3878839A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H9/00Pneumatic or hydraulic massage
    • A61H9/005Pneumatic massage
    • A61H9/0078Pneumatic massage with intermittent or alternately inflated bladders or cuffs
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H31/00Artificial respiration or heart stimulation, e.g. heart massage
    • A61H31/004Heart stimulation
    • A61H31/006Power driven
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/12Driving means
    • A61H2201/1238Driving means with hydraulic or pneumatic drive
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2205/00Devices for specific parts of the body
    • A61H2205/10Leg
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2230/00Measuring physical parameters of the user
    • A61H2230/04Heartbeat characteristics, e.g. E.G.C., blood pressure modulation

Definitions

  • a substantially rigid housing encloses a portion of the patients body, such as the legs, and a closed pneumatic pressure actuation system is used to actuate a pressure medium, at least a portion of which is gaseous, within the housing to cyclically apply pressure to the body in synchronism with the patients heartbeatv
  • the housing may be fabricated to provide either a fixed volume or a variable volume therein. Means are provided for effecting an efficient transfer of energy from the actua tion system to the pressure medium and thence to the patients body.
  • This invention relates generally to apparatus for assisting the circulation of blood in a human being and more particularly to an apparatus for doing so externally by the utilization of counter-pitlsation techniques.
  • a rigid housing encloses a portion of the patient's body. such as the legs. and a noncompressible hydraulic fluid is present within such housing.
  • a suitable hydraulically actuated compression and decompression means is then utilized to cycle the pressure on said body portions via the non-compressible hydraulic fluid.
  • Means are provided therein specifically to assure that the environment within the rigid housing is gas free so that no et fective dead space is present and the efficiency of the compression and decompression energy transfer is maximized. Further.
  • a first source lies in the apparatus hich comprises the system for producing the cyclic compression and de compression energy transfer to the patients body.
  • Such systenf' damping can arise because of the distensibil ity of the housing ⁇ vhich is used as well as the distensibility of the unsupported areas of the sealed portion of the system which contains the actuating fluid at the interface between the system and the portion of the pa tient's body to which the pulsating pressure is applied. Further. the instability of the shape of such sealed portion (i.e..).
  • a second source of damping relates to the physical nature of the patient's body itself and can be best de scribed as a form of "physiologic" damping.
  • Such damping arises. for example. from the o erall motion of the patient's body which can occur during the appli cation of the pressure actuation system thereto. Additional factors which contribute to such physiologic damping include the displacement of body tissue. both in the areas to which the pressure is directly applied and in the areas adjacent thereto. and the compressibility ofthe body in those areas thereof which can contain gas. such as the abdomen and/or the thoracic ca ⁇ ity.
  • This invention in one einbodi ment utilizes a compressible fluid. either alone or in combination with a non-compressible fluid. for energy transfer at the body interface.
  • the use thereof provides an improved external assist apparatus which has the ad vantage of being lighter in weight and less cumbersome to use than previously known apparatus. and further. which can be designed to reduce considerably the pos sibility of producing a traumatic evperience for the patient.
  • any increased interface damping which may resttlt from the use of at least a partially compressible lluid medium is taken into account by uti lizing a more efficient actuation system designed as a closed system wherein energy expended in transfer to the patient's body is effectively stored and retttrned to the system for reuse with a minimization of overall energy loss during operation.
  • Such efficient use of energy overcomes the effects of increased damping due to the utilization of compressible fluids
  • the effects of such increased damping can be overcome in other embodiments of the imention by utilizing housing units ha ⁇ ing adjustable volumes. the adjustment thereof being arranged to reduce the ⁇ olume and. hence. the dead space which may give rise to damping at the interface of the medium with the patients body.
  • the housing is formed as a rigid. fixed ⁇ olunie type and the pressure is applied to the patient's body portion. sttch as the legs. through a medium which is at least partially in gaseous form. Because the pressure medium is. at least partly. a gas. such as air. the mend] weight of the apparatus is reduced considerably and the compression and decompression cycle thereof can be actuated by the use of a pneumatic actuation system rather than a hydraulic system as in the prior art apparatus.
  • Such a pneumatic actuator and control sy stem can be placed at a position relatively remote from and ottt of the view of the patient without substantial pressure drops occurring in the pneumatic feed lines to the pressure applying medium.
  • the use of a pneumatic actuation apparatus which reduces the amount of equipment required to be located immediately adjacent the patient. thereby lessens the traumatic experience for the patient and provides more working space at the patient location for the medical personnel using the apparatus. Moreover. the reduction in weight makes the placement of the leg enclosure units on the patient much easier than with prior art devices.
  • the pnettmatie actuation system is designed so that some of the energy used to effect the desired pressure at the patient's limb is stored and reused so that the overall energy expenditure is at least comparable to that in the prior art structttres which require hydraulic fluids for such purpose.
  • the housing may he made of a rigid or semirigid material which is arranged to permit the formation of a variable volume of space within which the pressure medium is enclosed. 'Ihus. the housing is designed to be so adjustable that a sufficiently small spatial volume can be achiev ed to reduce considerably the presence of dead space which tnay arise dtte to the compressibility of the gas. Moreover. the arrangement of a variable ⁇ olunie enclosure permits the configuration of such housings to be adjusted to patients of different sizes.
  • FIG. I shows a pictorial view of an overall system utilizing the apparatus of the invention
  • FIG. 2 shows a ⁇ iew in longitudinal section of one embodiment of a body portion housing ttnit used in the apparatus of FIG. 1;
  • FIGS. 3 and 3A show both views in longitudinal and cross section of another embodiment of a body portion housing unit used in the apparatus of FIG. 1:
  • FIG. 4 shows a iew in crosssection of the body portion housing unit of FIG. 2 taken along the lines 4-4 thereof;
  • FIG. 5 shows a iew in cross-section of the body portion housing unit of FIG. 3 taken along the lines 5-5 thereof.
  • FIG. 6 shows a view in crosssection of a body portion housing unit utilizing one embodiment of a pressure medium comprising a gas-liquid combination
  • FIG. 7 shows a view in cross-section of a body portion ttnit utilizing another embodiment of a gas-liquid pressure medium
  • FIG. 8 shows a side elevational view of a body portion housing unit which has an adjustable configuration to permit the formation of a variable ⁇ olume within;
  • FIG. 9 shows a view in cross section of the body portion housing unit of FIG. 8 taken along the lines 9-9 thereof.
  • FIG. 10 shows another embodiment of a body por tion housing unit utilizing a configuration ofsegmented cones:
  • FIG. I shows a view in cross-section of a portion of the housing ttnit shown in FIG. I0;
  • FIG. [2 shows a graph of one embodiment of the pressure waveform used in the system of the invention
  • FIG. [3 shows a view. partially in block form and partially in diagrammatic form. of the pneumatic actuation system of the imention:
  • FIG. [4 shows a longitudinal section view of an alternate embodiment of the invention.
  • FIGS. ISA and [5B show an alternative embodiment of the configuration shown in FIG. 2.
  • the overall system in accordance with the invention comprises in one embodiment thereof a pair of leg units in the form of housings I0 which enclose a substantial portion of the legs of the patient to he treated.
  • the leg units are generally formed to permit the lower leg from approximately the ankle region down to the foot to project outwardly from the lower end of the housing unit. the unit extend ing upwardly therefrom to the upper leg in the region of the thighs.
  • Separate leg units may be used. or such units may be joined at their upper ends either by fixed connections to form a fixed angle with respect to each other or by pivotal connections so that such angle may be suitably varied as desired.
  • the leg units en close a pressurizeable medium which acts as an interface between the surface of the legs of the patient within the housing and a pressure actuation and control system I].
  • the medium as discussed below can be ei ther fully gaseous or at least partially gaseous and is actuated by a pneumatic pressure actuation system which cyclically feeds gas under pressure via tubings I2 to each of the leg units and then removes said gas by re- ⁇ ersal of said pressure to sub-atmospheric levels in a cyclic fashion.
  • the gas may be fed by a single tubing front the actuator and then supplied to each housing by a pair of branch tubings connected thereto by a suitable T-conneetion arrangement.
  • each leg unit comprises a rigid housing [5 in a substantially frusto-conical shape.
  • such housing in the embodiment described being made of aluminum or an appropriate rigid plastic material as desired.
  • a flexible. fluid-tight material forms a sealed member 16 which is pressure expansible the material thereof being preferably nondistensible.
  • the material is formed in a tubular shape and mounted within the rigid enclosure so as to completely enclose the major portion of the leg 17 of the patient (not shown l. the surface ofthe plastic material generally conforming to the contour of the patient's leg.
  • the flexible material is attached to the rigid housing by lapping the ends thereof over the rounded ends I8 of the housing so as to ermit the overlap ed ends to rest in notches I) of the housing oyer which notches appropriate sealing rings 20 may be attached.
  • the term "flexible material” may include thermosctting and thermoplastic clastomcric materials and may also inelude. for example. multi-layered materials. such as one lia ⁇ ing a first inner layer of distensible material and a second outer layer of a non-distensible material.
  • a fitting 21 is integrally formed in housing I5 to proyidc an opening 22 at the exterior surface of the housing which can be suitably connected to the pneumatic pressure actuation system II which supplies gas under pressure at above atmospheric pressure throughout a first portion of its cycle and which removes gas to create a subatmospheric pressure within the sealed member 16 during the remaining portion of its cycle.
  • the pressurizeable medium is introduced into the spatial volutne between flexible sealed member [6 and the inner wall 23 of housing 15 so that as the pressure therein increases during the compression portion ofthe cycle the pressure medium presses against the patients leg as desired.
  • a perforated tubtllar member 24 is attached by suitable means such as an adhesive to shoul dcrs 15A at the interior of housing 15 in the space between member 16 and housing 15 at about a position midway therebctweenv Member 24 may be a rigid plastic material. for example. and prevents the flexible member from collapsing completely against and adhering to the interior wall of housing I5 during the dccom pression portion of the cycle. which collapse may cause an effective but undesirable valving action which would prevent an efficient transfer of oscillatory energy from the actuator to the leg.
  • Member I6 can be made of any suitable thin metallic or plastic material. such as aluminum or acetal. for example.
  • the member which contains the pressurize-able medium is formed separately from the rigid housing itself.
  • a flexible. tubular sealed container 25 is made of a suitable flexible material such as nylonneoprene cloth. for example, In a collapsed state the container may be folded flat or rolled up into a com pact annular shape.
  • the container 25 is suitably unfurled and placed. as shown in FIG. 3. within the housing o ⁇ cr the patients leg.
  • the container has an appropriate integrally-formed fitting 26 which is inserted through a suitable opening in a rigid housing 27 and which is adapted to be con nected to a pressure actuation source.
  • the flexible container 25 is thereby enclosed by the rigid housing 27 which as seen in FIG. 5 can be constructed for this purpose in two pieces. 27A and 278. which are hingedly connected.
  • the major portion of the patients leg is encased in flexible container 25. is placed in lower piece 278 and the upper piece 27A is rotated to a closed position and clamped to the lower piece by any suitable conventional clamping mechanism 28 to form a rigid housing around container 25.
  • manifolding means may be used within the interior thereof to pre ent collapse of the outer surface thereof against the inner surface adjacent the wall of the housing.
  • One suitable manifolding means as shown in FIG. 3 can comprise an interior layer of rubber material 29 adjacent the housing wall. such layer having a plurality of projections 29A extending toward the interior of container 25 as shown.
  • a longitudinal force difference tends to exist along the patients legs during operation of the system because ofthe difference in the cross-sectional area at the patient's thighs and that at the patients ankles.
  • Such force differential causes the inner wall of the sealed members of the apparatus tie. the direct interface of the inner wall of flexible members 16 or 25 in contact with the patients leg in FIGS. 2 and 3. for examplel to move longitudinally with respect to the outer wall thereof tie. the housing wall in FIG. 2 or the outer wall of flexible container 25 in FIG. 3 which is in contact with the housingl.
  • Such movement tends to move the legs and. hence. the entire body of the patient outwardly front the housing and. in effect. to forcibly eject the patient from the housing units. thereby reducing the effectiveness ofthe system to perform its task as well as producing discomfort and a further traumatic effect on the patient.
  • the tethered portions 16A of the inner wall of container 16 may be arranged to be suitably tethered to the rounded end l8 of the housing and to the ends of perforated member 24 as shown therein.
  • the ends of the sealed member I6 may be effectively tethered without the necessity for adhering member If) to the housing wall.
  • FIGS. A and IE8 show an alternathe structure wherein the flexible member is formed of a multi-layer material in which a first inner layer 100 is rubber and a second outer layer llll is cloth.
  • a plurality of generally longitudinally directed pockets 102 are formed between the layers at each end thereof lfor simplicity only a iew of one end is shown in H0. 158 and only a part thereof in FIG. 15A].
  • the extreme end of member If) is held by the sealing ring in the manner discussed abo ⁇ e with reference to Fl(i. 2 and the pockets I02 extend from a point within the interior of the housing to a point approximately adjacent the region where member 16 o ⁇ crlaps the rounded end IX of the housing.
  • a plurality of spring lilve. or semi-rigid. stays 103 are inserted in the plurality of pockets at each end of flexible member Hi so as to project inwardly of the housing. The use of such stays tends to prc ⁇ ent longitudinal motion ofthe ends of flesible member 16 relative to the housing In so that such ends are effectively tethered thereby.
  • the pressurization medium in the above embodiments can be either fully gaseous or may be a gas-liquid combination depending upon the application which is desired.
  • the medium can be completely gaseous and dead space problems can be mercome by installing a suitably sized motor to operate under all expected dead-space conditions. b en in portable. or less permanently installed. apparatus a completely gaseous medium can often be used relati ⁇ ely effectively with smaller motors of less than 1 horsepower because of the effective utilization of energy brought about by the use of a closed pneumatic actuation system as discussed further below.
  • a further advantage of the use of pneumatic systems in this regard is that the compressible gaseous medium can inherently achieve the desired negatiye pressures with less expenditure of energy from the energy input source than is required when using an hydraulic me dium. such as water.
  • the use of a gaseous medium eliminates the static head which is present when using an hydraulic medium which completely surrounds the patient's limb. In the latter case the positive head must be overcome before any negative pressure is obtained.
  • Such an advantage in using a pneumatic system then tends further to offset any disadvantage which may arise because of any increase in damping due to the use of a compressible gaseous medium.
  • This advantage can still be obtained e ⁇ en when using a combined gas/liquid medium. particularly with the system discussed below with reference to FIG. 6 where the liquid portion thereof is maintained substantially below the patients leg so that no static head is present.
  • a housing of the form shown in FIG. 4. for example. has a sealed flexible container 31 which substantially conforms to the patients leg and has contained therein a liquid medium 32 and a gaseous medium 33 in direct contact therewith.
  • the liquid medium such as water. may preferably be approximately 5
  • a pneumatic actuation system as shown in FIG. 1 is then appropriately connected to fitting 34 so that the gaseous medium. such as air. can be pressurized.
  • the liquid medium taking up substan tially most of the dead space that may occur within the sealed enclosure due to the compressibility ofthe gase ous medium. in this way. a relatively efficient transfer of pressure to the leg can be achieved
  • FlG. 7. Another embodiment of a combined gas-liquid press urizeable medium is shown in FlG. 7. As can be seen therein. the liquid medium 42 and the gas medium 43 are separated from each other. the liquid medium being laced in a flexible sealed container 4] which encircles the leg of the patient and forms the direct pressure interface with the patient's body.
  • the gas coupling medium 43 is inserted into the housing between the scaled liquid container 4] and the interior surface of housing 40.
  • An appropriate fitting 44 is connected to a pneumatic actuation system for inserting and with drawing gas abo ⁇ e and below atmospheric pressure. which gas pressure variations are coupled via gas medium 43 to the liquid medium 42 and then to the patient's leg for providing the cyclic compression and dcconipression action required.
  • FIGS. 27 While the use of rigid. fixed ⁇ olume housing units as shown in FIGS. 27 are useful in many applications. it is desirable in still other applications to provide for rigid or semi-rigid housings having adjustable volumes particularly for permitting an adjustment thereof when used with patients having different limb sizes. which adjustment can also be used to reduce any dead space which may exist when such structure is used with a completely or partially compressible medium.
  • One em bodiment of such a variable volume housing is shown in FIGS. 8 and 9. the diameter of which can be varied at varous points along the length thereof.
  • the housing may be made in the form of a collapsible. or adjustable. sheet of metallic material. such as sheet aluminum. which is formed in an overlapping manner into a substantially frusto-conical shape.
  • a plurality of adjustable bands. or rings 5] are placed at selected positions along the length thereof.
  • the patients leg is inserted into the housing when the bands are in a relatively loose condition so that an effectively large diameter housing is formed.
  • the bands are then tightened so as to reduce the volume of the space between the housing and the patient's limb in which a sealed container 52 fits.
  • the dead space. which ordi narily may be present when a compressible medium. such as air. is completely or partially used as the pressurizeable medium can be minimized no matter what the size of the patient's leg. Accordingly. the efficiency of the overall pneumatic actuation system can be increased thereby enhancing the capability of the system to operate even with pressure actuation systems of relatively low power.
  • variable volume structure shown can also use a completely non-compressible medium. In such a case.
  • variable volume housing structure perntits a closer comfortttity ofthe housing to the legs of the pa tient. less hydraulic fluid is required than in those fixed volume structures of tlte prior art so that a consequent overall reduction in weight of the portion of the app-a ratus at the patients legs occurs.
  • volume adjustments perntit a closer conforntity of the overall sealed container to the patient's body and tends to reduce the unsupported annular end regions of the flexible container and. accordingly. the dantping due thereto.
  • the housing volume is reduced. a better conformahility of the tethered portions of the sealed container to tlte patient's body results.
  • FIG. ll Another embodiment of a rigid. or semi-rigid housing which can be utilized to make the most efficient use of the apparatus oftlte inv cation for different size patients is shown in FIG. ll).
  • a relatively large frusto-conically shaped ltousing (it) can be forttted front a plurality of segmented frusto-conical members 61 each of which can be suitably attached and dctached to adjacent of said ntemhers ltaving corresponding diameters.
  • a selectable bor tion of the overall housing can he fortned in accordance with the si7e of the patients leg.
  • segments A-G seven separable segments A-G are depicted. segments A. B. C. E. F. G being of approvimately the same length and segntent D being approximately three tintes larger in the specific embodiment shown.
  • the overall housing with all segments attached together is made av ailablc for use with a patient.
  • sections A. B. C. D and E ntay be selected arid the segmented sections F and G may be detached therefrom.
  • Fora minimttt sized leg. it may be desirable to utilize only sectiotts B. (I D. E attd F with sections A and G detached therefrom.
  • For relatively large legs it ntay be desirable to use sections C. D. E.
  • the segments shown in FIG. can be attached by appropriate means as shown in the exemplary embodiment of FIG. II. As seen therein if housing segments. each of the type shown in FIG. 2. are used the flexible containers 62A or 62B of adjacent segments are lapped over the corresponding ends 63A and 63B thereof to rest itt notches 64A and 64B. (lamp members 65A and 658 have first flanges 66A and 668 which rest iit notches 64A and 648 respectively.
  • Upright flanges 67A and 67B lie adjacent each other at the junction of the housing segments and are appropriately clamped to each other at suitable points located on the periphery of the housings via threaded bolts (78 inserted through threaded openings in the upright flanges.
  • the flanges 66A and 66B are retained in the notched ends of the housing segments by suitable clantping bands 69A and 1598. respectively. as shown.
  • the pneumatic actuation system which is utilized will provide an effective sinusoidal pressure wave form 70 as shown in FIG. 12.
  • the pressure can vary in a particular embodiment front a minimum valve within a preferred range ofapproximately +25 mm. Hg.
  • the rise time is defined as the time the pressure rises front a low value equal to It) percent of the peak-to-peak value thereof to a value equal to 9() percent of such peak-to peak value. with the fall tinte being similarly defined as the time the pressure decreases front )tl percent of its peak-to-peak value to It) percent thereof.
  • a preferred rise time and a preferred fall time is usually set within a range of -150 milliseconds in each case.
  • the time duration of the pulsating portion of the wave form is defined as tltc time for the pressure wave fornt to rise front a low value at It) percent of its peakto-peak value to a time when it has passed through its positive peak value to a value of 9t) percent of the peak-to-peak value thereof.
  • Such time may preferably lie within a range of about -500 milliseconds.
  • FIG. I2 Although a sine wave is shown in FIG. I2. the system is not limited to such a wave form.
  • a square wave configuration may he acceptable in sotne applications if the discrete changes thereof do ttot cause ad ⁇ erse effects on the patient.
  • Other wave shapes may be devised also for such purpose.
  • FIG. I3 A pneumatic actuation system for achie ⁇ ing an appropriate pressure wave form is shown in FIG. I3 wherein it can be seen that a suitably sized crank dri ⁇ en piston 75. fitted with conventional low friction. lovv hysteresis seals and driven by a variable speed gear motor 76 through an appropriate clutch/brake combination 77. provides a means for producing synchronous pneumatic pressure pulses of the wave shape described above. such pressure pulses being applied to the coupling medium at the interface with the patient's limb to create the desired ltentodynamic results.
  • Appropriate and known means catt be utilized to adjust the amplitude of the pressure pulse and the relationship of the positive and negative peak pressure amplitudes with ambient (room atmospheric) pressure.
  • the atmospheric pressure volume of the medium in the pneumatic actuation system is such that the piston stroke is at its mid-stroke position.
  • driving the piston in one direction will create a positive pressure and driving it iii the opposite direction (hackvvard) will create a negative pressure.
  • Any appropriate combination of positive aitd negative peak pressures can be arranged within the total pressure differential capability of the pump system and can be selected for an individual patient by adjustment ofthe total volunte offluid in the system (often referred to as the charge on the system) to produce the optimum hemodynamic results which are desired.
  • Such volume adjustment can be made by adjustment of valve 78 which supplies air front air pump 79 to the system.
  • the hydraulic liquid catt be supplied from a liquid reservoir 81 via a suitable pump 80.
  • Appropriate synchronism with the patients heartbeat can then be provided by suitable monitoring of the patient's EKG by monitor 82.
  • a sensing of the R wave of the patient s heartbeat to provide suitable control of the operation of the clutch/brake combination 77 and. accordingly. of the piston ntotion of the actuation system relative to the R wave. as shown by the R-wave sensor and control device 83.
  • Such synchronization and control is explained in more detail. for example. in the article cited abo ⁇ e.
  • a further method of prot iding an appropriate seal is to arrange for an effecti ⁇ e self-e acuation system for such purpose. thereby eliminating the need for a kannum enclosure and external vacuum pump. Since the sub-atmospheric pressure in the space between the sealed container and the patients body is required only during the time w hen the pressure wave form is below atmospheric pressure. such time being a relatively short part of the o crall pressure cycle. there need not be a requirement for a constant negative pressure as would exist in the abo ⁇ c described externally actuated c ⁇ acuation system. Such a selt evacuation system is shown in FIG. 14. As seen therein.
  • ⁇ al ⁇ cs passiye oneway ⁇ al ⁇ cs )2 which permit the expulsion of air from such space to the atmosphere but which prevent the intake of air from the atmosphere to such spacer
  • ⁇ al es may be in the form of thin rubber rings placed over the ends of the housing 93. the free ends thereof being held tightly against the patients ankles and thighs when applied.
  • the ends of the one-way valves are opened and substantially all of the air in the space between the leg and the sealed container is expelled therefrom.
  • the output ⁇ alves may alternathely be attached to suitable suction pumps to further insure that no air will leak back into such space during the negative pressure phase of the pressure axe form.
  • suitable manifold means )4 may be placed within the container.
  • manifold means may be in the form of a rigid tubular structure preferably extending from the region below the knee to the end of the housing. The manifold provides a passageway for any trapped air that may be present. such trapped air being most likely to be present at such knee region.
  • the presence of the tethers may be sufticient to pro ide such passageways without the need for such an additional manifold means.
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means ha ⁇ ing a substantially fixed ⁇ olume for enclosing a portion of said patient's body;
  • said pressure applying means including a closed pneumatic pressure actuation means.
  • a pressure medium at least a portion which is in gaseous form. enclosed in a flexible sealed memher which is pressure expansible and positioned between said pressure actuation means and said portion of the patients body. at least a part of said sealed member being in contact with said body portion. a first portion of said sealed member being formed of a flexible material scalably clamped to the ends of said housing and a second portion thereof being formed by said housing. said pressure medium being responsi e to said pneumatic pressure actuation means to apply pressure to said body portion:
  • Apparatus for pro ⁇ iding external as 'tance for the circulation of blood in a patient comprising substantially rigid housing means having a substan tially fixed ⁇ olume for enclosing a portion of said patients body;
  • said pressure applying means including a closed pneumatic pressure actuation means
  • a pressure medium at least a portion of which is in gaseous form. enclosed in a flexible scaled mcm her which is pressure cxpansible and positioned between said pressure actuation means and said portion of the patient's body.
  • said sealed member being a flexible tubular means formed indepen dently of said housing. said sealed member being positioned during operation of said apparatus between the inner wall of said'housing and said body portion to flexibly enclose said body por tion.
  • said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion;
  • said said preventing means means comprises a flexible means ha ing a plurality of projections extending into the interior oi said sealed member 9.
  • apparatus for pro 'iding external assistance for the circulation of blood in a patient comprir ing substantially rigid housing means haying a substantially fixed volume for enclosing a portion of said patient's body. said housing comprising a pair of hingcdly connected portions piy'otally moyable relati 'c to each other from an open to a closed position;
  • said pressure applying means including a closed pneumatic pressure actuation means:
  • a pressu rc medium at least a portion of which is in gaseous form. enclosed in a flexible sealed member which is pressure expansihle. at least a part of said sealed member being in contact with said body portion. and positioned between said pressure actuation means and said portion of the patients body. said pressure medium being responsi e to said pneumatic pressure actuation means to apply pressure to said body portion: and
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means ha ing a substantially t'ixed ⁇ olume for enclosing a portion ot said patients body;
  • said pressure applying means including a closed pneumatic pressure actuation means:
  • a pressure medium enclosed in a flexible sealed member which is pressure e ⁇ pansible and positioned between said pressure actuation means and said portion of the patients body. at least a part of said sealed member being in contact with said body portion.
  • said pressure medium being a combination of a gaseous material and a liquid material placed within said flexible sealed member in contact with each other and further being responsive to said pneumatic pressure actuation means to apply pressure to said body portion;
  • Apparatus for pro ⁇ iding external assistance for the circulation of blood in a patient comprising substantially rigid housing means h 1 ⁇ ing a substantially lixed ⁇ olumc for enclosing a portion of said patients body:
  • said pressure applying means including a closed pneumatic pressure actuation means
  • a pressure medium positioned between said pres sure actuation means and said portion of the patients body. said pressure medium being responshe to said pneumatic pressure actuation means to apply pressure to said body portion:
  • said pressure medium being a combination of a gaseous material and a liquid material
  • liquid material being placed within a first flexible sealed member in contact with said body portion;
  • said gaseous material being placed within the said housing between said first flexible sealed member and said housing;
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means haying a substan tially fixed ⁇ olume tor enclosing a portion of said patient's body:
  • said pressure applying means including a closed pneumatic pressure actuation means.
  • a pressure medium positioned between said pres sure actuation means and said portion ot the patient's body. said pressure medium being respon she to said pneumatic pressure actuation means to apply pressure to said body portion;
  • said pressure medium being a combination ola gas eous material and a liquid material
  • said gaseous material being placed within a flexible sealed member in contact with and enclosing said body portion;
  • said liquid material being placed within said housing between said lle ⁇ ible gaseous container and said housing;
  • said pneumatic actuation means being coupled to said liquid material.
  • Apparatus for pro ⁇ iding external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient's body. said housing means including means for adjusting the volume enclosed thereby to pro ⁇ ide for a variable volume when enclosing said body portion;
  • said pressure applying means including a closed pneumatic pressure actuation means:
  • a pressure medium at least a portion of which is in gaseous lorm. positioned between said pressure actuation means and said portion of the patient's body. said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patients heartbeat.
  • a first portion oi s-aid sealed member is formed ofa flesible material sealably clamped to the ends of said housing and a second portion thereof is formed by said housing.
  • said sealed member is a flexible tubular means formed independently of said housing. said scaled member being positioned during operation of said apparatus between the inner wall of said housing and said body portion to flexibly enclose said body portion.
  • said pressure medium is a combination of a gaseous material and a liquid material placed within a flexible sealed member in contact with each other.
  • said pressure medium is a combination of a gaseous material and a liquid material
  • liquid material being placed within a first flexible sealed member in contact with said body portion;
  • said gaseous material is placed within the said hous ing between said flexible sealed member and said housing;
  • said pneumatic pressure actuation means is coupled to said gaseous material.
  • said gaseous material being contained within a flexible sealed member in contact with and enclosing said body portion;
  • said pneumatic actuation means is coupled to said liquid material.
  • said adjusting means providing for the adjustment of the amount of overlap of said o ⁇ erlapping portions to permit adjustment of the volume enclosed thereby.
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patients body;
  • said pressure applying means including pressure actuation means
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patients body:
  • said housing means comprising a plurality of lrustoconical segments and further including means for aftixing a selected number of said segments to one another to form a substantially rigid housing of a selected length and having openings at the ends thereof of predetermined diameters for use with body portions of different sizes; means for cyclically applying pressure to said body portion within said housing means.
  • said pressure applying means including a closed pneumatic pressure actuation means;
  • a pressure medium positioned between said pressure actuation means and said portion of the patients body.
  • said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion:
  • Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a por tion of said patient's body; means for cyclically applying pressure to said body portion within said housing means.
  • said pressure applying means including a closed pneumatic pressure actuation means;
  • a pressure medium positioned between said pressure actuation means and said portion olthe patient's body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion;
  • an evacuation chamber enclosing said housing means and the body portion enclosed by said housing; and vacuum pump means for maintaining a pressure within said evacuation chamber at a le ⁇ el below the lowest pressure achieved during the decompression Ill portion of the cyclical pressure applied to said body portion.
  • said oneavay valve comprises a flexible ring positioned over the ends of said housing. the free ends of said ring being held tightly against the body portions of said patient at said ends.
  • said flexible sealed member is formed of a first layer of rtzbberlike material and a second layer ol'cloth-like ma terial.

Abstract

An apparatus for providing external assistance for the circulation of blood in a patient wherein a substantially rigid housing encloses a portion of the patient''s body, such as the legs, and a closed pneumatic pressure actuation system is used to actuate a pressure medium, at least a portion of which is gaseous, within the housing to cyclically apply pressure to the body in synchronism with the patient''s heartbeat. The housing may be fabricated to provide either a fixed volume or a variable volume therein. Means are provided for effecting an efficient transfer of energy from the actuation system to the pressure medium and thence to the patient''s body.

Description

United States Patent 1191 Norton et a1.
1 1 Apr. 22, 1975 1 CARDIAC ASSIST APPARATUS [73] Assignee: l-lemodyne, lnc., Norfolk, Mass.
[22] Filed: Feb. 15, 1973 211 App]. No.: 332,629
152] U.S. Cl. 128/64 [51] Int. Cl A6lh 7/00 [58] Field of Search 128/64, 24 R, 297, 299, 128/60, 39, 40
[56] References Cited UNITED STATES PATENTS 2,249,579 7/1941 Rea 128/64 UX 2,832,336 4/1958 Davis et a1. 1 1 v 128/64 2.833275 5/1958 Tunnicliffc 128/64 X 3.053.249 9/1962 Smith t l l t v. 128/64 3.403.673 10/1968 MacLcod 1, 128/64 UX 3.478,?37 11/1969 Rassman 128/64 Primary Examiner-Lawrence W. Trapp Attorney, Agent, or FirmDike. Bronstein, Roberts.
Cushman & Pfund 1571 ABSTRACT An apparatus for providing external assistance for the circulation of blood in a patient wherein a substantially rigid housing encloses a portion of the patients body, such as the legs, and a closed pneumatic pressure actuation system is used to actuate a pressure medium, at least a portion of which is gaseous, within the housing to cyclically apply pressure to the body in synchronism with the patients heartbeatv The housing may be fabricated to provide either a fixed volume or a variable volume therein. Means are provided for effecting an efficient transfer of energy from the actua tion system to the pressure medium and thence to the patients body.
29 Claims, 17 Drawing Figures PATENTEUAPRZZ 1975 SHEET 1 I]? 5 PATENTEDAFRZZISFS SHIEI 2 OF 5 FIGS FIG?
htTfiNTEnAPazzzszs man u or 5 PRESSU RE FIG.|2
VACUUM PUMP WATER PUMP AIR PUMP
WATER RESERVOIR R -WAV E SENSOR 8| CONTROL E KG MONITOR PATENIEDAPRZZIHYS sum 5 pg 5 FIG. ISA
CARDIAC ASSIST APPARATLS This invention relates generally to apparatus for assisting the circulation of blood in a human being and more particularly to an apparatus for doing so externally by the utilization of counter-pitlsation techniques.
BACKGROUND OF THE INVENTION Apparatus for providing esternal assistance in the circulation of blood in patients has been described in previously issued articles and patents. particularly US. Pat. No. 3.654.)[9 issued to W. C. Birtuell vvherein a rigid housing encloses a portion of the patient's body. such as the legs. and a noncompressible hydraulic fluid is present within such housing. A suitable hydraulically actuated compression and decompression means is then utilized to cycle the pressure on said body portions via the non-compressible hydraulic fluid. Means are provided therein specifically to assure that the environment within the rigid housing is gas free so that no et fective dead space is present and the efficiency of the compression and decompression energy transfer is maximized. Further. in the decompression portion of the cycle. a negative pressure is achieved immediately adjacent the body portion and means are provided for synchronously overriding the substmospheric pressure \vhich is so obtained. such overriding being in appropri ate synchronism with the patient's heartbeat.
A number of problems arise in the use of the device described in the above Birtvvcll patent. First of all. it is a relati\ely cumbersome structure to handle. the use of a non-compressiblc hydraulic fluid. such as water. making the overall apparatus quite hca\y. Moreover. the hydraulic actuation equipment which is required to cause the compression and decompression flow of fluid within the hottsing tnust be placed relatively near the patient so as to avoid excessive hydraulic pressure drops along the fluid lines thereof. usually such actuae tor being placed on the table on which the patient l'tlt'lr self lies. often substantially centrally located between the patient's legs. as shown in the patent Not only is such apparatus therein difficult to use because of the large size and weight of the rigid housings and the hydraulic fluid. together with the hydraulic actuation equipment therefor. but the presence of such elaborate equipment in the direct view of the patient may tend to produce an adverse psychological reaction on the part of the patient when the apparatus is being applied to the patient's limbs.
Moreover. the use of such rigid. fixed volume housing requires that they be made sufficiently large to fit the limbs of the largest patient to which the apparatus is expected to be applied. Thus. for patients with relatively small limbs. substantially tnore hydraulic liquid is required to fill the enclosure. a factor which only adds to the weight of the overall device and its difficulty in use.
ln considering alternative structures for providing effective external assistance for the circulation of blood. the design thereofshould provide for a reduction in the above disadvantages while still maintaining an effectiv e energy transfer. The maintenance of such energy transfer must take into account the damping which may be present within the system. so that the effects thereof can be minimized and the overall efficiency of the system can be preserved.
Such damping can be broadly identified as arising from two major sources discussed in more detail below, A first source lies in the apparatus hich comprises the system for producing the cyclic compression and de compression energy transfer to the patients body. Such systenf' damping can arise because of the distensibil ity of the housing \vhich is used as well as the distensibility of the unsupported areas of the sealed portion of the system which contains the actuating fluid at the interface between the system and the portion of the pa tient's body to which the pulsating pressure is applied. Further. the instability of the shape of such sealed portion (i.e.. the fact that such sealed portion does not retain its shape during the pulsating cycle also contributes to the o\erall system damping, The compressibility of the actuating medium which gives rise to the presence of dead space within the housing also contributes to the system damping. Finally. both the presence of trapped air at various points within the system as well as the failure to provide an adequate contact bctvv een the sealed interface portion of the system and the pa tients body can introduce additional damping into the system.
A second source of damping relates to the physical nature of the patient's body itself and can be best de scribed as a form of "physiologic" damping. Such damping arises. for example. from the o erall motion of the patient's body which can occur during the appli cation of the pressure actuation system thereto. Additional factors which contribute to such physiologic damping include the displacement of body tissue. both in the areas to which the pressure is directly applied and in the areas adjacent thereto. and the compressibility ofthe body in those areas thereof which can contain gas. such as the abdomen and/or the thoracic ca\ ity.
A primary consideration in the design of the structure disclosed in the above-ntcntioned Birtyvell patent was the desire to reduce system damping which can arise because of the compressibility of the medium used to provide pressure actuation. Accordingly. such system used noncompressible hydraulic fluids. i.e.. liquids. such as water. as the pressurizing medium in the sealed container at the interface with the patient's body. thereby necessitating the use of the hydraulic actuation and control system shown therein. While some consideration was given to the reduction of damping due to one or more of the other factors listed above (i.e.. the utilization of a rigid. fixed volume housing. longitudinal tethering of the sealed container. etc. l. little or no consideration was given to making the most effective use of the energy available. the hydraulic actuation system being arranged as an effectively open system where hydraulic fluid was continually supplied from the energy source. As a result. prime importance has been attached to the purported need to use noncompressible fluids. as opposed to compressible fluids. such as air. for pressure actuation and interface energy transfer so that damping at the interface of a rigid. fixed volume housing structure is minimized.
SUMMARY OF THE lN\'ENTlON This invention. on the other hand. in one einbodi ment utilizes a compressible fluid. either alone or in combination with a non-compressible fluid. for energy transfer at the body interface. The use thereof provides an improved external assist apparatus which has the ad vantage of being lighter in weight and less cumbersome to use than previously known apparatus. and further. which can be designed to reduce considerably the pos sibility of producing a traumatic evperience for the patient. The effect of any increased interface damping which may resttlt from the use of at least a partially compressible lluid medium is taken into account by uti lizing a more efficient actuation system designed as a closed system wherein energy expended in transfer to the patient's body is effectively stored and retttrned to the system for reuse with a minimization of overall energy loss during operation. Such efficient use of energy overcomes the effects of increased damping due to the utilization of compressible fluids Further. the effects of such increased damping can be overcome in other embodiments of the imention by utilizing housing units ha\ing adjustable volumes. the adjustment thereof being arranged to reduce the \olume and. hence. the dead space which may give rise to damping at the interface of the medium with the patients body. More specifically. in one embodiment of the in\en tion. for csample. the housing is formed as a rigid. fixed \olunie type and the pressure is applied to the patient's body portion. sttch as the legs. through a medium which is at least partially in gaseous form. Because the pressure medium is. at least partly. a gas. such as air. the mend] weight of the apparatus is reduced considerably and the compression and decompression cycle thereof can be actuated by the use of a pneumatic actuation system rather than a hydraulic system as in the prior art apparatus. Such a pneumatic actuator and control sy stem can be placed at a position relatively remote from and ottt of the view of the patient without substantial pressure drops occurring in the pneumatic feed lines to the pressure applying medium. The use of a pneumatic actuation apparatus. which reduces the amount of equipment required to be located immediately adjacent the patient. thereby lessens the traumatic experience for the patient and provides more working space at the patient location for the medical personnel using the apparatus. Moreover. the reduction in weight makes the placement of the leg enclosure units on the patient much easier than with prior art devices. The pnettmatie actuation system is designed so that some of the energy used to effect the desired pressure at the patient's limb is stored and reused so that the overall energy expenditure is at least comparable to that in the prior art structttres which require hydraulic fluids for such purpose.
In still other embodiments of the apparatus ofthe invention utilizing such pneumatic actuation and control together with at least a partially gaseous pressure medium. the housing may he made of a rigid or semirigid material which is arranged to permit the formation of a variable volume of space within which the pressure medium is enclosed. 'Ihus. the housing is designed to be so adjustable that a sufficiently small spatial volume can be achiev ed to reduce considerably the presence of dead space which tnay arise dtte to the compressibility of the gas. Moreover. the arrangement of a variable \olunie enclosure permits the configuration of such housings to be adjusted to patients of different sizes.
Particular embodiments of the invention are discussed in more detail below with the help of the accom pany ing drawings wherein FIG. I shows a pictorial view of an overall system utilizing the apparatus of the invention;
hl I
FIG. 2 shows a \iew in longitudinal section of one embodiment of a body portion housing ttnit used in the apparatus of FIG. 1;
FIGS. 3 and 3A show both views in longitudinal and cross section of another embodiment of a body portion housing unit used in the apparatus of FIG. 1:
FIG. 4 shows a iew in crosssection of the body portion housing unit of FIG. 2 taken along the lines 4-4 thereof;
FIG. 5 shows a iew in cross-section of the body portion housing unit of FIG. 3 taken along the lines 5-5 thereof.
FIG. 6 shows a view in crosssection of a body portion housing unit utilizing one embodiment of a pressure medium comprising a gas-liquid combination;
FIG. 7 shows a view in cross-section of a body portion ttnit utilizing another embodiment of a gas-liquid pressure medium;
FIG. 8 shows a side elevational view of a body portion housing unit which has an adjustable configuration to permit the formation of a variable \olume within;
FIG. 9 shows a view in cross section of the body portion housing unit of FIG. 8 taken along the lines 9-9 thereof.
FIG. 10 shows another embodiment of a body por tion housing unit utilizing a configuration ofsegmented cones:
FIG. I] shows a view in cross-section of a portion of the housing ttnit shown in FIG. I0;
FIG. [2 shows a graph of one embodiment of the pressure waveform used in the system of the invention;
FIG. [3 shows a view. partially in block form and partially in diagrammatic form. of the pneumatic actuation system of the imention:
FIG. [4 shows a longitudinal section view of an alternate embodiment of the invention; and
FIGS. ISA and [5B show an alternative embodiment of the configuration shown in FIG. 2.
As shown in FIG. I. the overall system in accordance with the invention comprises in one embodiment thereof a pair of leg units in the form of housings I0 which enclose a substantial portion of the legs of the patient to he treated. The leg units are generally formed to permit the lower leg from approximately the ankle region down to the foot to project outwardly from the lower end of the housing unit. the unit extend ing upwardly therefrom to the upper leg in the region of the thighs. Separate leg units may be used. or such units may be joined at their upper ends either by fixed connections to form a fixed angle with respect to each other or by pivotal connections so that such angle may be suitably varied as desired.
As described in more detail below. the leg units en close a pressurizeable medium which acts as an interface between the surface of the legs of the patient within the housing and a pressure actuation and control system I]. The medium as discussed below can be ei ther fully gaseous or at least partially gaseous and is actuated by a pneumatic pressure actuation system which cyclically feeds gas under pressure via tubings I2 to each of the leg units and then removes said gas by re- \ersal of said pressure to sub-atmospheric levels in a cyclic fashion. Alternatively. the gas may be fed by a single tubing front the actuator and then supplied to each housing by a pair of branch tubings connected thereto by a suitable T-conneetion arrangement.
Accordingly. an appropriate compression and decompression of the patients legs will occur so as to assist the circulation ofthe blood. the cyclical application thereof being in appropriate synchronism with the patient's heartbeat as described in the aforementioned Birtwell patent. and as described. for example. in the article "Support of the Systemic Circulation and Left Ventricular Assist by Synchronous Pulsation of Extramural Pressure." Birtwcll et al.. Vol. XI. Trans. Amer. Soc. Artif. Int. Organs. I965.
One embodiment of leg units I0 is described in more detail in FIGS. 2 and 4 wherein it can be seen that each leg unit comprises a rigid housing [5 in a substantially frusto-conical shape. such housing in the embodiment described being made of aluminum or an appropriate rigid plastic material as desired. A flexible. fluid-tight material forms a sealed member 16 which is pressure expansible the material thereof being preferably nondistensible. The material is formed in a tubular shape and mounted within the rigid enclosure so as to completely enclose the major portion of the leg 17 of the patient (not shown l. the surface ofthe plastic material generally conforming to the contour of the patient's leg. In the embodiment shown the flexible material is attached to the rigid housing by lapping the ends thereof over the rounded ends I8 of the housing so as to ermit the overlap ed ends to rest in notches I) of the housing oyer which notches appropriate sealing rings 20 may be attached. As used herein the term "flexible material" may include thermosctting and thermoplastic clastomcric materials and may also inelude. for example. multi-layered materials. such as one lia\ ing a first inner layer of distensible material and a second outer layer of a non-distensible material. such as one ha\ing a layer of rubber backed by a layer of cloth A fitting 21 is integrally formed in housing I5 to proyidc an opening 22 at the exterior surface of the housing which can be suitably connected to the pneumatic pressure actuation system II which supplies gas under pressure at above atmospheric pressure throughout a first portion of its cycle and which removes gas to create a subatmospheric pressure within the sealed member 16 during the remaining portion of its cycle.
The pressurizeable medium is introduced into the spatial volutne between flexible sealed member [6 and the inner wall 23 of housing 15 so that as the pressure therein increases during the compression portion ofthe cycle the pressure medium presses against the patients leg as desired. A perforated tubtllar member 24 is attached by suitable means such as an adhesive to shoul dcrs 15A at the interior of housing 15 in the space between member 16 and housing 15 at about a position midway therebctweenv Member 24 may be a rigid plastic material. for example. and prevents the flexible member from collapsing completely against and adhering to the interior wall of housing I5 during the dccom pression portion of the cycle. which collapse may cause an effective but undesirable valving action which would prevent an efficient transfer of oscillatory energy from the actuator to the leg. Member I6 can be made of any suitable thin metallic or plastic material. such as aluminum or acetal. for example.
In the embodiment shown in FIGS. 3. 3A and 5. the member which contains the pressurize-able medium is formed separately from the rigid housing itself. As can be seen therein a flexible. tubular sealed container 25 is made of a suitable flexible material such as nylonneoprene cloth. for example, In a collapsed state the container may be folded flat or rolled up into a com pact annular shape. When the apparatus is to be used. the container 25 is suitably unfurled and placed. as shown in FIG. 3. within the housing o\cr the patients leg. The container has an appropriate integrally-formed fitting 26 which is inserted through a suitable opening in a rigid housing 27 and which is adapted to be con nected to a pressure actuation source. The flexible container 25 is thereby enclosed by the rigid housing 27 which as seen in FIG. 5 can be constructed for this purpose in two pieces. 27A and 278. which are hingedly connected. During use. the major portion of the patients leg is encased in flexible container 25. is placed in lower piece 278 and the upper piece 27A is rotated to a closed position and clamped to the lower piece by any suitable conventional clamping mechanism 28 to form a rigid housing around container 25.
In order to prevent any valving action in the embodiment of FIG. 3 appropriate manifolding means may be used within the interior thereof to pre ent collapse of the outer surface thereof against the inner surface adjacent the wall of the housing. One suitable manifolding means as shown in FIG. 3 can comprise an interior layer of rubber material 29 adjacent the housing wall. such layer having a plurality of projections 29A extending toward the interior of container 25 as shown.
In the embodiments discussed above with reference to FIGS. I5. as well as in the embodiments ofthe prior art. a longitudinal force difference tends to exist along the patients legs during operation of the system because ofthe difference in the cross-sectional area at the patient's thighs and that at the patients ankles. Such force differential causes the inner wall of the sealed members of the apparatus tie. the direct interface of the inner wall of flexible members 16 or 25 in contact with the patients leg in FIGS. 2 and 3. for examplel to move longitudinally with respect to the outer wall thereof tie. the housing wall in FIG. 2 or the outer wall of flexible container 25 in FIG. 3 which is in contact with the housingl. Asa result. such movement tends to move the legs and. hence. the entire body of the patient outwardly front the housing and. in effect. to forcibly eject the patient from the housing units. thereby reducing the effectiveness ofthe system to perform its task as well as producing discomfort and a further traumatic effect on the patient.
In order to overcome such movement it is desirable to longitudinally tether at least a portion of the inner wall of the sealed member to the housing (FIG. 2) or to the outer wall thereof adjacent the housing (FIG. 3). It has been found that if such tethering is effected. for example. along two or four parallel lines near each end ofthe housing. longitudinal movement of the inner wall of container 25 is reduced considerably. Four such tether lines 25A are shown in an exemplary embodiment of FIGS. 3 and 3A. Although the tethered portions may extend the entire length of the housing. it is not found necessary to do so in all applications. and tethering at the ends thereof may be sufficient. Accord ingly. they maybe arranged in preferred embodiments. for example. to extend inwardly front each end thereof to lengths of about l()-2t) percent of the total housing length. Moreover. additional tethered portions may be used at other positions in addition to the ends thereof. if desired,
In the embodiment of FIGS. 2 and 24 the tethered portions 16A of the inner wall of container 16 may be arranged to be suitably tethered to the rounded end l8 of the housing and to the ends of perforated member 24 as shown therein. Alternati ely. in FIG. 2 the ends of the sealed member I6 may be effectively tethered without the necessity for adhering member If) to the housing wall. For example. FIGS. A and IE8 show an alternathe structure wherein the flexible member is formed of a multi-layer material in which a first inner layer 100 is rubber and a second outer layer llll is cloth. A plurality of generally longitudinally directed pockets 102 are formed between the layers at each end thereof lfor simplicity only a iew of one end is shown in H0. 158 and only a part thereof in FIG. 15A]. The extreme end of member If) is held by the sealing ring in the manner discussed abo\e with reference to Fl(i. 2 and the pockets I02 extend from a point within the interior of the housing to a point approximately adjacent the region where member 16 o\crlaps the rounded end IX of the housing. A plurality of spring lilve. or semi-rigid. stays 103 are inserted in the plurality of pockets at each end of flexible member Hi so as to project inwardly of the housing. The use of such stays tends to prc\ ent longitudinal motion ofthe ends of flesible member 16 relative to the housing In so that such ends are effectively tethered thereby.
The pressurization medium in the above embodiments can be either fully gaseous or may be a gas-liquid combination depending upon the application which is desired. In permanent installations. for example. where sufficient power is available for the use of relatively large motors leg. over I horsepower). the medium can be completely gaseous and dead space problems can be mercome by installing a suitably sized motor to operate under all expected dead-space conditions. b en in portable. or less permanently installed. apparatus a completely gaseous medium can often be used relati\ely effectively with smaller motors of less than 1 horsepower because of the effective utilization of energy brought about by the use of a closed pneumatic actuation system as discussed further below.
A further advantage of the use of pneumatic systems in this regard is that the compressible gaseous medium can inherently achieve the desired negatiye pressures with less expenditure of energy from the energy input source than is required when using an hydraulic me dium. such as water. Thus. the use of a gaseous medium eliminates the static head which is present when using an hydraulic medium which completely surrounds the patient's limb. In the latter case the positive head must be overcome before any negative pressure is obtained. Such an advantage in using a pneumatic system then tends further to offset any disadvantage which may arise because of any increase in damping due to the use of a compressible gaseous medium. This advantage can still be obtained e\ en when using a combined gas/liquid medium. particularly with the system discussed below with reference to FIG. 6 where the liquid portion thereof is maintained substantially below the patients leg so that no static head is present.
If the dead space which exists due to the compressibility of the gaseous medium tends to prevent the creation of sufficient pressures as required and if sufficiently large actuator systems are not a\ ailable to overcome such problem. such dead space may be reduced by using an apparatus which utilizes a combined gas liquid pressure medium as shown with reference to FIGS. 6 and 7. As can be seen in PK}. 6. for example. a housing of the form shown in FIG. 4. for example. has a sealed flexible container 31 which substantially conforms to the patients leg and has contained therein a liquid medium 32 and a gaseous medium 33 in direct contact therewith. In a practical embodiment. for example. the liquid medium such as water. may preferably be approximately 5|) percent. or more. of the volume within the housing. A pneumatic actuation system as shown in FIG. 1 is then appropriately connected to fitting 34 so that the gaseous medium. such as air. can be pressurized. the liquid medium taking up substan tially most of the dead space that may occur within the sealed enclosure due to the compressibility ofthe gase ous medium. in this way. a relatively efficient transfer of pressure to the leg can be achieved Another embodiment of a combined gas-liquid press urizeable medium is shown in FlG. 7. As can be seen therein. the liquid medium 42 and the gas medium 43 are separated from each other. the liquid medium being laced in a flexible sealed container 4] which encircles the leg of the patient and forms the direct pressure interface with the patient's body. The gas coupling medium 43 is inserted into the housing between the scaled liquid container 4] and the interior surface of housing 40. An appropriate fitting 44 is connected to a pneumatic actuation system for inserting and with drawing gas abo\e and below atmospheric pressure. which gas pressure variations are coupled via gas medium 43 to the liquid medium 42 and then to the patient's leg for providing the cyclic compression and dcconipression action required.
While the use of rigid. fixed \olume housing units as shown in FIGS. 27 are useful in many applications. it is desirable in still other applications to provide for rigid or semi-rigid housings having adjustable volumes particularly for permitting an adjustment thereof when used with patients having different limb sizes. which adjustment can also be used to reduce any dead space which may exist when such structure is used with a completely or partially compressible medium. One em bodiment of such a variable volume housing is shown in FIGS. 8 and 9. the diameter of which can be varied at varous points along the length thereof. For example. the housing may be made in the form of a collapsible. or adjustable. sheet of metallic material. such as sheet aluminum. which is formed in an overlapping manner into a substantially frusto-conical shape. A plurality of adjustable bands. or rings 5] are placed at selected positions along the length thereof. The patients leg is inserted into the housing when the bands are in a relatively loose condition so that an effectively large diameter housing is formed. The bands are then tightened so as to reduce the volume of the space between the housing and the patient's limb in which a sealed container 52 fits. Thus. the dead space. which ordi narily may be present when a compressible medium. such as air. is completely or partially used as the pressurizeable medium can be minimized no matter what the size of the patient's leg. Accordingly. the efficiency of the overall pneumatic actuation system can be increased thereby enhancing the capability of the system to operate even with pressure actuation systems of relatively low power.
The variable volume structure shown can also use a completely non-compressible medium. In such a case.
because the variable volume housing structure perntits a closer confortttity ofthe housing to the legs of the pa tient. less hydraulic fluid is required than in those fixed volume structures of tlte prior art so that a consequent overall reduction in weight of the portion of the app-a ratus at the patients legs occurs. Further. the volume adjustments perntit a closer conforntity of the overall sealed container to the patient's body and tends to reduce the unsupported annular end regions of the flexible container and. accordingly. the dantping due thereto. Further. as the housing volume is reduced. a better conformahility of the tethered portions of the sealed container to tlte patient's body results.
Another embodiment ofa rigid. or semi-rigid housing which can be utilized to make the most efficient use of the apparatus oftlte inv cation for different size patients is shown in FIG. ll). As can be seen therein. a relatively large frusto-conically shaped ltousing (it) can be forttted front a plurality of segmented frusto-conical members 61 each of which can be suitably attached and dctached to adjacent of said ntemhers ltaving corresponding diameters. In the process of use. a selectable bor tion of the overall housing can he fortned in accordance with the si7e of the patients leg. For example. in the illustrated embodiment of a segmented housing of FIG. 10. seven separable segments A-G are depicted. segments A. B. C. E. F. G being of approvimately the same length and segntent D being approximately three tintes larger in the specific embodiment shown. The overall housing with all segments attached together is made av ailablc for use with a patient. For use with a patient having a relatively small diameter leg. sections A. B. C. D and E ntay be selected arid the segmented sections F and G may be detached therefrom. Fora mediuttt sized leg. it may be desirable to utilize only sectiotts B. (I D. E attd F with sections A and G detached therefrom. For relatively large legs it ntay be desirable to use sections C. D. E. F and G with sections A and B detached therefrom. Accordingly. the amount of dead space which is present for use in a system using a contplete or partial gaseous medium catt be minimized by the appropriate selection of segments in accordance with the size of a patients leg. The segments shown in FIG. can be attached by appropriate means as shown in the exemplary embodiment of FIG. II. As seen therein if housing segments. each of the type shown in FIG. 2. are used the flexible containers 62A or 62B of adjacent segments are lapped over the corresponding ends 63A and 63B thereof to rest itt notches 64A and 64B. (lamp members 65A and 658 have first flanges 66A and 668 which rest iit notches 64A and 648 respectively. above the lapped ends of the flexible containers therein. Upright flanges 67A and 67B lie adjacent each other at the junction of the housing segments and are appropriately clamped to each other at suitable points located on the periphery of the housings via threaded bolts (78 inserted through threaded openings in the upright flanges. The flanges 66A and 66B are retained in the notched ends of the housing segments by suitable clantping bands 69A and 1598. respectively. as shown.
In a preferred embodiment ofthe invention the pneumatic actuation system which is utilized will provide an effective sinusoidal pressure wave form 70 as shown in FIG. 12. As can be seen therein. the pressure can vary in a particular embodiment front a minimum valve within a preferred range ofapproximately +25 mm. Hg.
to 5( him. Hg.. although such minimum value may be set otherwise in some applications. to a maximum value within a preferred range of approsimately IOU mnt. Hg. to 150 mm. Hg. although such ma\intum \alue also may be set otherwise in sonte applications. The rise time is defined as the time the pressure rises front a low value equal to It) percent of the peak-to-peak value thereof to a value equal to 9() percent of such peak-to peak value. with the fall tinte being similarly defined as the time the pressure decreases front )tl percent of its peak-to-peak value to It) percent thereof. A preferred rise time and a preferred fall time is usually set within a range of -150 milliseconds in each case.
The time duration of the pulsating portion of the wave form is defined as tltc time for the pressure wave fornt to rise front a low value at It) percent of its peakto-peak value to a time when it has passed through its positive peak value to a value of 9t) percent of the peak-to-peak value thereof. Such time may preferably lie within a range of about -500 milliseconds.
Although a sine wave is shown in FIG. I2. the system is not limited to such a wave form. A square wave configuration may he acceptable in sotne applications if the discrete changes thereof do ttot cause ad\erse effects on the patient. Other wave shapes may be devised also for such purpose.
A pneumatic actuation system for achie\ing an appropriate pressure wave form is shown in FIG. I3 wherein it can be seen that a suitably sized crank dri\ en piston 75. fitted with conventional low friction. lovv hysteresis seals and driven by a variable speed gear motor 76 through an appropriate clutch/brake combination 77. provides a means for producing synchronous pneumatic pressure pulses of the wave shape described above. such pressure pulses being applied to the coupling medium at the interface with the patient's limb to create the desired ltentodynamic results. Appropriate and known means catt be utilized to adjust the amplitude of the pressure pulse and the relationship of the positive and negative peak pressure amplitudes with ambient (room atmospheric) pressure.
Thus. if the atmospheric pressure volume of the medium in the pneumatic actuation system is such that the piston stroke is at its mid-stroke position. driving the piston in one direction (forward) will create a positive pressure and driving it iii the opposite direction (hackvvard) will create a negative pressure. Any appropriate combination of positive aitd negative peak pressures can be arranged within the total pressure differential capability of the pump system and can be selected for an individual patient by adjustment ofthe total volunte offluid in the system (often referred to as the charge on the system) to produce the optimum hemodynamic results which are desired. Such volume adjustment can be made by adjustment of valve 78 which supplies air front air pump 79 to the system. In a system which uses an air/liquid combination or iii a variable volume system which uses a liquid medium alone. the hydraulic liquid catt be supplied from a liquid reservoir 81 via a suitable pump 80. Appropriate synchronism with the patients heartbeat can then be provided by suitable monitoring of the patient's EKG by monitor 82. a sensing of the R wave of the patient s heartbeat to provide suitable control of the operation of the clutch/brake combination 77 and. accordingly. of the piston ntotion of the actuation system relative to the R wave. as shown by the R-wave sensor and control device 83. Such synchronization and control is explained in more detail. for example. in the article cited abo\e.
'l'he effectncness in achie ing a negati c pressure at the patient's body is dependent upon how good a seal is maintained between the inner surface of the sealed container containing the energy coupling medium and the surface of the patients limbs during the negati\e portion of the pulsation cycle. Such seal can be main taincd by the use of an adhesi e compound on the surface of the sealed container between the container and the limb. How 0 er. such a method may be impractical or inappropriate in many situation Another method for pro\ iding such a seal is to e\ acuate all of the air between the limb and the sealed con tainer outer surface. such e acuation being maintained against the le els of those peak negati e pressures being created by the pneumatic actuation system applied through the actuation fluid in the sealed con tainer. Thus. a continuous suction can be created in the space between the limb and the sealed container by an external e\acuation device. One method of achie\ing this is to enclose the legs and housing units of the sys tem by a vacuum enclosure 84 as shown by the dashed line in FIG. 13. such enclosure being appropriately e\acuated by an external \acuum pump 85 which creates a /one of sub-atmospheric pressure below that expected at the lowest region of the pressure actuation cur e of Fl(i. l2 around such housing sy stem.
A further method of prot iding an appropriate seal is to arrange for an effecti\e self-e acuation system for such purpose. thereby eliminating the need for a meuum enclosure and external vacuum pump. Since the sub-atmospheric pressure in the space between the sealed container and the patients body is required only during the time w hen the pressure wave form is below atmospheric pressure. such time being a relatively short part of the o crall pressure cycle. there need not be a requirement for a constant negative pressure as would exist in the abo\c described externally actuated c\acuation system. Such a selt evacuation system is shown in FIG. 14. As seen therein. the ends ofthe space between the sealed container 90 and the patient's legs 91 at the ankles and at the thighs are fitted with passiye oneway \al\cs )2 which permit the expulsion of air from such space to the atmosphere but which prevent the intake of air from the atmosphere to such spacer Such \al es may be in the form of thin rubber rings placed over the ends of the housing 93. the free ends thereof being held tightly against the patients ankles and thighs when applied. During each positive pressure portion of the pressure wave form. the ends of the one-way valves are opened and substantially all of the air in the space between the leg and the sealed container is expelled therefrom. During the negative portions ofthc pressure wa\e form the ends thereof are closed and an effecthe e acuation of the space between the limb and container is maintained. While the air is \ented to the at mosphere in the embodiment shown in FIG. 14 the output \alves may alternathely be attached to suitable suction pumps to further insure that no air will leak back into such space during the negative pressure phase of the pressure axe form. In order to pre ent val ing of the container at suitable manifold means )4 may be placed within the container. Such manifold means may be in the form of a rigid tubular structure preferably extending from the region below the knee to the end of the housing. The manifold provides a passageway for any trapped air that may be present. such trapped air being most likely to be present at such knee region. In those embodiments which utilize tethers. as discussed above. the presence of the tethers may be sufticient to pro ide such passageways without the need for such an additional manifold means.
The abo\e description shows various embodiments of the invention. although other embodiments within the scope of the invention may occur to those in the art. Hence. the imention is not to be construed as limited to the particular embodiments shown herein except as defined by the appended claims.
The following LIS. Pat. Nos. were obtained by a patent Search: 1,608,239. 2,113,253, 2,168,611, 2.345.073. 2.361.242. 3.179.106. 3168.71 1. 3.288.133. 3.292.613. 3.303.841. 3.307.533. 3.329.141. 3.403.673. 3.411.496. 3.548.811). 3.5991131. 3.651.8(11. 3.h54.9|'-). 31159593.
What is claimed is:
1. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means ha\ing a substantially fixed \olume for enclosing a portion of said patient's body;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means.
a pressure medium. at least a portion which is in gaseous form. enclosed in a flexible sealed memher which is pressure expansible and positioned between said pressure actuation means and said portion of the patients body. at least a part of said sealed member being in contact with said body portion. a first portion of said sealed member being formed of a flexible material scalably clamped to the ends of said housing and a second portion thereof being formed by said housing. said pressure medium being responsi e to said pneumatic pressure actuation means to apply pressure to said body portion:
means for synchronizing the operation of said pres sure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient's heartbeat; and
means for pre\enting said flexible material from collapsing against said housing during the decompression portion of the cyclical application of said pressure.
2. An apparatus in accordance with claim 1 wherein at least selected portions of said flexible material are tethered to portions of said housing to pre\ent the tendency for relative mo ement between said flexible material and said housing.
3. An apparatus in accordance with claim 2 wherein said flexible material is tethered to said housing substantially at the ends thereof.
4. An apparatus in accordance with claim 1 wherein said last-named means is a perforated tubular member positioned within said housing between said housing and said flexible material.
5. Apparatus for pro\ iding external as 'tance for the circulation of blood in a patient comprising substantially rigid housing means having a substan tially fixed \olume for enclosing a portion of said patients body;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means;
a pressure medium. at least a portion of which is in gaseous form. enclosed in a flexible scaled mcm her which is pressure cxpansible and positioned between said pressure actuation means and said portion of the patient's body. said sealed member being a flexible tubular means formed indepen dently of said housing. said sealed member being positioned during operation of said apparatus between the inner wall of said'housing and said body portion to flexibly enclose said body por tion. said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion;
means for pre enting the walls of said flexible sealed member from collapsing against each other during the decompression portion ol the cyclical application of said pressure; and
means for synchronizing the operation otsaid pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression otsaid body portion in synchronism with said patient's heartbeat.
6. An apparatus in accordance with claim 5 wherein portions of the inner wall of said flexible sealed member adjacent said body portion are tethered to portions of the outer wall thereof adjacent said housing to pre- \cnt the tendency for relati c mmement of said inner and outer walls.
7. An apparatus in accordance with claim 6 wherein said tethered portions are substantially at the ends of said flexible sealed member.
8. An apparatus in accordance with claim 5 wherein said said preventing means means comprises a flexible means ha ing a plurality of projections extending into the interior oi said sealed member 9. apparatus for pro 'iding external assistance for the circulation of blood in a patient comprir ing substantially rigid housing means haying a substantially fixed volume for enclosing a portion of said patient's body. said housing comprising a pair of hingcdly connected portions piy'otally moyable relati 'c to each other from an open to a closed position;
means for clamping said portions together in said closed position;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means:
a pressu rc medium. at least a portion of which is in gaseous form. enclosed in a flexible sealed member which is pressure expansihle. at least a part of said sealed member being in contact with said body portion. and positioned between said pressure actuation means and said portion of the patients body. said pressure medium being responsi e to said pneumatic pressure actuation means to apply pressure to said body portion: and
means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient's heartbeat.
10. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means ha ing a substantially t'ixed \olume for enclosing a portion ot said patients body;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means:
a pressure medium enclosed in a flexible sealed member which is pressure e\pansible and positioned between said pressure actuation means and said portion of the patients body. at least a part of said sealed member being in contact with said body portion. said pressure medium being a combination of a gaseous material and a liquid material placed within said flexible sealed member in contact with each other and further being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and
means for synchronizing the operation ot said pressure actuation means to apply said pressure cyclically to produce alternating compression and dc compression of said body portion in synchronism with said patient's heartbeat.
11. Apparatus for pro\iding external assistance for the circulation of blood in a patient comprising substantially rigid housing means h 1\ing a substantially lixed \olumc for enclosing a portion of said patients body:
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means;
a pressure medium positioned between said pres sure actuation means and said portion of the patients body. said pressure medium being responshe to said pneumatic pressure actuation means to apply pressure to said body portion:
said pressure medium being a combination of a gaseous material and a liquid material;
said liquid material being placed within a first flexible sealed member in contact with said body portion;
said gaseous material being placed within the said housing between said first flexible sealed member and said housing;
said pneumatic pressure actuation means being coupled to said gaseous material: and
means for synchronizing the operation of said pres sure actuation means to apply said pressure cyclically to produce alternating compression and dccompression of said body portion in synchronism with said patient's heartbeat.
12. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means haying a substan tially fixed \olume tor enclosing a portion of said patient's body:
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means.
a pressure medium positioned between said pres sure actuation means and said portion ot the patient's body. said pressure medium being respon she to said pneumatic pressure actuation means to apply pressure to said body portion;
said pressure medium being a combination ola gas eous material and a liquid material;
said gaseous material being placed within a flexible sealed member in contact with and enclosing said body portion;
said liquid material being placed within said housing between said lle\ible gaseous container and said housing;
said pneumatic actuation means being coupled to said liquid material. and
means for sy nchroni7ing the operation of said pres sure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient's heartbeat.
l3. Apparatus for pro\iding external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient's body. said housing means including means for adjusting the volume enclosed thereby to pro\ ide for a variable volume when enclosing said body portion;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means:
a pressure medium. at least a portion of which is in gaseous lorm. positioned between said pressure actuation means and said portion of the patient's body. said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patients heartbeat.
14. Apparatus in accordance with claim 13 wherein said pressure medium is enclosed in a flexible sealed member which is pressure expansible. at least a part of said sealed member being in contact with said body portion.
15. Apparatus in accordance with claim 14 wherein a first portion oi s-aid sealed member is formed ofa flesible material sealably clamped to the ends of said housing and a second portion thereof is formed by said housing.
If). Apparatus in accordance with claim [4 wherein said sealed member is a flexible tubular means formed independently of said housing. said scaled member being positioned during operation of said apparatus between the inner wall of said housing and said body portion to flexibly enclose said body portion.
17. Apparatus in accordance with claim l3 wherein said pressure medium is a combination of a gaseous material and a liquid material placed within a flexible sealed member in contact with each other.
18. Apparatus in accordance with claim 13 wherein said pressure medium is a combination of a gaseous material and a liquid material;
said liquid material being placed within a first flexible sealed member in contact with said body portion;
ltl
Ill
said gaseous material is placed within the said hous ing between said flexible sealed member and said housing; and
said pneumatic pressure actuation means is coupled to said gaseous material.
1). Apparatus in accordance with claim 13 wherein said pressure medium is a combination of a gaseous material and a liquid material:
said gaseous material being contained within a flexible sealed member in contact with and enclosing said body portion;
said liquid material being placed within said housing between said flexible sealed member and said hous ing'. and
said pneumatic actuation means is coupled to said liquid material.
20. An apparatus in accordance with claim [3 wherein said housing is formed of sheet metal being arranged in a substantially frusto-conical shape and having overlapping portions along the longitudinal direction thereof; and
said adjusting means providing for the adjustment of the amount of overlap of said o\erlapping portions to permit adjustment of the volume enclosed thereby.
2|. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patients body;
means for adjusting the volume enclosed by said housing means to provide for a variable volume when enclosing said body portion;
means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including pressure actuation means;
a liquid pressure medium enclosed in a flexible sealed member which is pressure cxpansihle. said sealed member being positioned between said pressure actuation means and said portion of the patient's body. said pressure medium being responsive to said pressure actuation means to apply pressure to said body portion; and
means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patients heartbeat.
22. Apparatus in accordance with claim 21 wherein said pressure actuation means is a hydraulic pressure actuation means coupled to said liquid material in said flexible scaled member.
23. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patients body:
said housing means comprising a plurality of lrustoconical segments and further including means for aftixing a selected number of said segments to one another to form a substantially rigid housing of a selected length and having openings at the ends thereof of predetermined diameters for use with body portions of different sizes; means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means;
a pressure medium. at least a portion of which is in gaseous form. positioned between said pressure actuation means and said portion of the patients body. said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion: and
means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient's heartbeatv 24. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a por tion of said patient's body; means for cyclically applying pressure to said body portion within said housing means. said pressure applying means including a closed pneumatic pressure actuation means;
a pressure medium. at least a portion of which is in gaseous form. positioned between said pressure actuation means and said portion olthe patient's body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion;
means for synchronizing the operation of said pres sure actuation means to apply said pressure cyclically to produce alternating compression and decompression otsaid body portion in synchronism with said patient's heartbeat;
an evacuation chamber enclosing said housing means and the body portion enclosed by said housing; and vacuum pump means for maintaining a pressure within said evacuation chamber at a le\el below the lowest pressure achieved during the decompression Ill portion of the cyclical pressure applied to said body portion.
25. An apparatus in accordance with claim 23 wherein said oneavay valve comprises a flexible ring positioned over the ends of said housing. the free ends of said ring being held tightly against the body portions of said patient at said ends.
26. An apparatus in accordance with claim 25 and further including manifold means for conveying trapped air from the interior otsaid housing to said end regions thereof.
27. An apparatus in accordance with claim 24 wherein the ends of said member include a plurality of pockets formed therein between said layers; and
a substantially rigid stay positioned in each of said pockets;
whereby the tendency for said flexible sealed memher to move relative to said housing tends to be reduced.
28. An apparatus in accordance with claim 9 and further including one-way val\e means positioned at the common ends of said housing and said flexible sealed member to permit the expulsion of air from the region at said ends during the compression portion of said cy clically applied pressure and to prevent the intake of air into said region during the decompression portion of said cyclically applied pressure. thereby to maintain an effective evacuation of air in said region during said de compression portion.
29. An apparatus in accordance with claim 1 herein said flexible sealed member is formed of a first layer of rtzbberlike material and a second layer ol'cloth-like ma terial.

Claims (29)

1. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium, at least a portion which is in gaseous form, enclosed in a flexible sealed member which is pressure expansible and positioned between said pressure actuation means and said portion of the patient''s body, at least a part of said sealed member being in contact with said body portion, a first portion of said sealed member being formed of a flexible material sealably clamped to the ends of said housing and a second portion thereof being formed by said housing, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat; and means for preventing said flexible material from collapsing against said housing during the decompression portion of the cyclical application of said pressure.
2. An apparatus in accordance with claim 1 wherein at least selected portions of said flexible material are tethered to portions of said housing to prevent the tendency for relative movement between said flexible material and said housing.
3. An apparatus in accordance with claim 2 wherein said flexible material is tethered to said housing substantially at the ends thereof.
4. An apparatus in accordance with claim 1 wherein said last-named means is a perforated tubular member positioned within said housing between said housing and said flexible material.
5. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium, at least a portion of which is in gaseous form, enclosed in a flexible sealed member which is pressure expansible and positioned between said pressure actuation means and said portion of the patient''s body, said sealed member being a flexible tubular means formed independently of said housing, said sealed member being positioned during operation of said apparatus between the inner wall of said housing and said body portion to flexibly enclose said body portion, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; means for preventing the walls of said flexible sealed member froM collapsing against each other during the decompression portion of the cyclical application of said pressure; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
6. An apparatus in accordance with claim 5 wherein portions of the inner wall of said flexible sealed member adjacent said body portion are tethered to portions of the outer wall thereof adjacent said housing to prevent the tendency for relative movement of said inner and outer walls.
7. An apparatus in accordance with claim 6 wherein said tethered portions are substantially at the ends of said flexible sealed member.
8. An apparatus in accordance with claim 5 wherein said said preventing means means comprises a flexible means having a plurality of projections extending into the interior of said sealed member.
9. apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body, said housing comprising a pair of hingedly connected portions pivotally movable relative to each other from an open to a closed position; means for clamping said portions together in said closed position; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium, at least a portion of which is in gaseous form, enclosed in a flexible sealed member which is pressure expansible, at least a part of said sealed member being in contact with said body portion, and positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
9. APPARATUS FOR PROVIDING EXTERNAL ASSISTANCE FOR THE CIRCULATION OF BLOOD IN A PATIENT COMPRISING SUBSTANTIALLY RIGID HOUSING MEANS HAVING A SUBSTANTIALLY FIXED VOLUME FOR ENCLOSING A PORTION OF SAID PATIENT''S BODY, SAID HOUSING COMPRISING A PAIR OF HINGEDLY CONNECTED PORTIONS PIVOTALLY MOVABLE RELATIVE TO EACH OTHER FROM AN OPEN TO A CLOSED POSITION; MEANS FOR CLAMPING SAID PORTIONS TOGETHER IN SAID CLOSED POSITION; MEANS FOR CYCLICALLY APPLYING PRESSURE TO SAID BODY PORTION WITHIN SAID HOUSING MEANS, SAID PRESSURE APPLYING MEANS INCLUDING A CLOSED PNEUMATIC PRESSURE ACTUATION MEANS; A PRESSURE MEDIUM, AT LEAST A PORTION OF WHICH IS IN GASEOUS FORM, ENCLOSED IN A FLEXIBLE SEALED MEMBER WHICH IS PRESSURE EXPANSIBLE, AT LEAST A PART OF SAID SEALED MEMBER BEING IN CONTACT WITH SAID BODY PORTION, AND POSITIONED BETWEEN SAID PRESSURE ACTUATION MEANS AND SAID PORTION OF THE PATIENT''S BODY, SAID PRESSURE MEDIUM BEING RESPONSIVE TO SAID PNEUMATIC PRESSURE ACTUATION MEANS TO APPLY PRESSURE TO SAID BODY PORTION; AND MEANS FOR SYNCHRONIZING THE OPERATION OF SAID PRESSURE ACTUATION MEANS TO APPLY SAID PRESSURE CYCLICALLY TO PRODUCE ALTERNATING COMPRESSION AND DECOMPRESSION OF SAID BODY PORTION IN SYNCHRONISM WITH SAID PATIENT''S HEARTBEAT.
10. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium enclosed in a flexible sealed member which is pressure expansible and positioned between said pressure actuation means and said portion of the patient''s body, at least a part of said sealed member being in contact with said body portion, said pressure medium being a combination of a gaseous material and a liquid material placed within said flexible sealed member in contact with each other and further being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
11. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation meAns to apply pressure to said body portion; said pressure medium being a combination of a gaseous material and a liquid material; said liquid material being placed within a first flexible sealed member in contact with said body portion; said gaseous material being placed within the said housing between said first flexible sealed member and said housing; said pneumatic pressure actuation means being coupled to said gaseous material; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
12. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means having a substantially fixed volume for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; said pressure medium being a combination of a gaseous material and a liquid material; said gaseous material being placed within a flexible sealed member in contact with and enclosing said body portion; said liquid material being placed within said housing between said flexible gaseous container and said housing; said pneumatic actuation means being coupled to said liquid material; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
13. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient''s body, said housing means including means for adjusting the volume enclosed thereby to provide for a variable volume when enclosing said body portion; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium, at least a portion of which is in gaseous form, positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
14. Apparatus in accordance with claim 13 wherein said pressure medium is enclosed in a flexible sealed member which is pressure expansible, at least a part of said sealed member being in contact with said body portion.
15. Apparatus in accordance with claim 14 wherein a first portion of said sealed member is formed of a flexible material sealably clamped to the ends of said housing and a second portion thereof is formed by said housing.
16. Apparatus in accordance with claim 14 wherein said sealed member is a flexible tubular means formed independently of said housing, said sealed member being positioned during operation of said apparatus between the inner wall of said housing and said body portion to flexibly enclose said body portion.
17. Apparatus in accordance with claim 13 wherein said pressure medium is a combination of a gaseous material and a liquid material placed within a flexible sealed member in contact with each other.
18. Apparatus in accordance with claim 13 wherein said pressure medium is a combination of a gaseous material and a liquid material; said liquid material being placed within a first flexible sealed member in contact with said body portion; said gaseous material is placed within the said housing between said flexible sealed member and said housing; and said pneumatic pressure actuation means is coupled to said gaseous material.
19. Apparatus in accordance with claim 13 wherein said pressure medium is a combination of a gaseous material and a liquid material; said gaseous material being contained within a flexible sealed member in contact with and enclosing said body portion; said liquid material being placed within said housing between said flexible sealed member and said housing; and said pneumatic actuation means is coupled to said liquid material.
20. An apparatus in accordance with claim 13 wherein said housing is formed of sheet metal being arranged in a substantially frusto-conical shape and having overlapping portions along the longitudinal direction thereof; and said adjusting means providing for the adjustment of the amount of overlap of said overlapping portions to permit adjustment of the volume enclosed thereby.
21. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient''s body; means for adjusting the volume enclosed by said housing means to provide for a variable volume when enclosing said body portion; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including pressure actuation means; a liquid pressure medium enclosed in a flexible sealed member which is pressure expansible, said sealed member being positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
22. Apparatus in accordance with claim 21 wherein said pressure actuation means is a hydraulic pressure actuation means coupled to said liquid material in said flexible sealed member.
23. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient''s body; said housing means comprising a plurality of frusto-conical segments and further including means for affixing a selected number of said segments to one another to form a substantially rigid housing of a selected length and having openings at the ends thereof of predetermined diameters for use with body portions of different sizes; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure actuation means; a pressure medium, at least a portion of which is in gaseous form, positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; and means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat.
24. Apparatus for providing external assistance for the circulation of blood in a patient comprising substantially rigid housing means for enclosing a portion of said patient''s body; means for cyclically applying pressure to said body portion within said housing means, said pressure applying means including a closed pneumatic pressure Actuation means; a pressure medium, at least a portion of which is in gaseous form, positioned between said pressure actuation means and said portion of the patient''s body, said pressure medium being responsive to said pneumatic pressure actuation means to apply pressure to said body portion; means for synchronizing the operation of said pressure actuation means to apply said pressure cyclically to produce alternating compression and decompression of said body portion in synchronism with said patient''s heartbeat; an evacuation chamber enclosing said housing means and the body portion enclosed by said housing; and vacuum pump means for maintaining a pressure within said evacuation chamber at a level below the lowest pressure achieved during the decompression portion of the cyclical pressure applied to said body portion.
25. An apparatus in accordance with claim 23 wherein said one-way valve comprises a flexible ring positioned over the ends of said housing, the free ends of said ring being held tightly against the body portions of said patient at said ends.
26. An apparatus in accordance with claim 25 and further including manifold means for conveying trapped air from the interior of said housing to said end regions thereof.
27. An apparatus in accordance with claim 24 wherein the ends of said member include a plurality of pockets formed therein between said layers; and a substantially rigid stay positioned in each of said pockets; whereby the tendency for said flexible sealed member to move relative to said housing tends to be reduced.
28. An apparatus in accordance with claim 9 and further including one-way valve means positioned at the common ends of said housing and said flexible sealed member to permit the expulsion of air from the region at said ends during the compression portion of said cyclically applied pressure and to prevent the intake of air into said region during the decompression portion of said cyclically applied pressure, thereby to maintain an effective evacuation of air in said region during said decompression portion.
US332629A 1973-02-15 1973-02-15 Cardiac assist apparatus Expired - Lifetime US3878839A (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US332629A US3878839A (en) 1973-02-15 1973-02-15 Cardiac assist apparatus
JP49017722A JPS6021739B2 (en) 1973-02-15 1974-02-15 cardiac assist device

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US332629A US3878839A (en) 1973-02-15 1973-02-15 Cardiac assist apparatus

Publications (1)

Publication Number Publication Date
US3878839A true US3878839A (en) 1975-04-22

Family

ID=23299101

Family Applications (1)

Application Number Title Priority Date Filing Date
US332629A Expired - Lifetime US3878839A (en) 1973-02-15 1973-02-15 Cardiac assist apparatus

Country Status (2)

Country Link
US (1) US3878839A (en)
JP (1) JPS6021739B2 (en)

Cited By (66)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2937360A1 (en) * 1979-09-15 1981-04-02 Dietrich 2100 Hamburg Schmidt Massage instrument for circulation trouble - comprises two hollow cylindrical components sealed by sleeves to human limbs
US4269175A (en) * 1977-06-06 1981-05-26 Dillon Richard S Promoting circulation of blood
FR2510399A1 (en) * 1981-08-03 1983-02-04 Jobst Institute METHOD AND APPARATUS FOR DYNAMICALLY APPLYING A PRESSURE WAVE TO AN END OF A MAN OR ANIMAL
US4388919A (en) * 1980-11-17 1983-06-21 Intermedics Cardiassist Corporation Rapid stabilization of external cardiac pulsation
FR2519544A1 (en) * 1982-01-11 1983-07-18 Casile Jean Pierre CIRCULATORY ASSISTANCE DEVICE
US4753226A (en) * 1985-04-01 1988-06-28 Biomedical Engineering Development Center of Sun Yat-Sen University of Medical Science Combination device for a computerized and enhanced type of external counterpulsation and extra-thoracic cardiac massage apparatus
WO1988005667A1 (en) * 1987-01-30 1988-08-11 Baxter Travenol Laboratories, Inc. Blood extraction assist apparatus and method
EP0569308A1 (en) * 1992-05-07 1993-11-10 Vasomedical, Inc. A high efficiency external counter pulsation apparatus and method for controlling same
US5344385A (en) * 1991-09-30 1994-09-06 Thoratec Laboratories Corporation Step-down skeletal muscle energy conversion system
US5425742A (en) * 1994-03-28 1995-06-20 Patrick S. Quigley Use of hollow hypobaric chambers on body parts for increasing blood flow, reducing pressure and decreasing pain
US5672148A (en) * 1991-12-06 1997-09-30 Maunier; Daniel Hydraulic device for lymphatic drainage and massage of the human body
US20020107461A1 (en) * 2000-11-10 2002-08-08 Hui John C.K. High efficiency external counterpulsation apparatus and method for controlling same
US20030139255A1 (en) * 1991-12-17 2003-07-24 Kinetic Concepts, Inc. Pneumatic compression device and methods for use in the medical field
US6620116B2 (en) 2000-12-08 2003-09-16 Michael P. Lewis External counterpulsation unit
WO2003099188A1 (en) * 2002-05-23 2003-12-04 Otto Bock Healthcare Lp Pulsating pressure chamber and method for enhanced blood flow
US20030233118A1 (en) * 2002-06-13 2003-12-18 Hui John C. K. Method for treating congestive heart failure using external counterpulsation
EP1392216A2 (en) * 2001-05-10 2004-03-03 Pptt Llc External counterpulsation cardiac assist device
US20040106885A1 (en) * 1997-08-18 2004-06-03 Paul Shabty Counterpulsation device using noncompressed air
WO2004058131A2 (en) * 2002-12-31 2004-07-15 Thermonor As Device for applying a pulsating pressure to a local region of the body and applications thereof
US20050070755A1 (en) * 1993-05-06 2005-03-31 Zhensheng Zheng High efficiency external counterpulsation method
US20060058715A1 (en) * 2004-09-14 2006-03-16 Hui John C External counterpulsation device with multiple processors
US7048702B2 (en) 2002-06-13 2006-05-23 Vasomedical, Inc. External counterpulsation and method for minimizing end diastolic pressure
US20070272250A1 (en) * 2006-05-24 2007-11-29 Michael Paul Lewis External pulsation treatment apparatus
US20080021531A1 (en) * 2003-09-24 2008-01-24 Kane John R Methods and apparatus for increasing blood circulation
WO2008011548A1 (en) * 2006-07-19 2008-01-24 The Brigham And Women's Hospital, Inc. Sub-atmospheric pressure chamber for mechanical assistance of blood flow
US20080033228A1 (en) * 2001-05-10 2008-02-07 Jahangir Rastegar External counterpulsation (ECP) device for use in an ambulance or the like for heart attack patients to limit heart muscle damage
US20080064994A1 (en) * 2004-12-06 2008-03-13 Vissman S.R.L. Apparatus and Method for the Conditioning of Muscular Fibrils Reaction Coordination Capacity by Means a Pressure Wave, and Eesthetic and Therapeutic Application Thereof
US20080132976A1 (en) * 2006-12-04 2008-06-05 Kane John Roy Methods and apparatus for adjusting blood circulation
US20080132816A1 (en) * 2006-12-04 2008-06-05 Kane John Roy Methods and Apparatus for Adjusting Blood Circulation
FR2913594A1 (en) * 2007-03-16 2008-09-19 Francois Dufay Open wound treating equipment for e.g. cosmetic field, has envelope placed around part of body to be treated and constituted of lower and upper shells that define cavity whose section is greater than that of body to be treated
US20080234615A1 (en) * 2005-07-26 2008-09-25 Novamedix Distribution Limited Limited Durability Fastening for a Garment
US20080249444A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device with Structural Support Features
US20080245361A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device with S-Shaped Bladder
US20080249441A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression device with strategic weld construction
US20080249442A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Breathable Compression Device
US20080249443A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device Having Weld Seam Moisture Transfer
US20080319248A1 (en) * 2007-06-20 2008-12-25 Michael Paul Lewis Hydraulically Actuated External Pulsation Treatment Apparatus
US20090062703A1 (en) * 2005-12-12 2009-03-05 Tyco Healthcare Group Lp Compression Sleeve Having Air Conduits
USRE40814E1 (en) * 1996-06-11 2009-06-30 Hill-Rom Services, Inc. Oscillatory chest compression device
US20090177184A1 (en) * 2008-01-09 2009-07-09 Christensen Scott A Method and apparatus for improving venous access
US20100081975A1 (en) * 2008-09-30 2010-04-01 Tyco Healthcare Group Lp Compression Device with Removable Portion
US20100152633A1 (en) * 2008-12-16 2010-06-17 Thermanor As Portable patient temperature adjustment apparatus and method
US20100152821A1 (en) * 2008-12-16 2010-06-17 Thermanor As Portable patient temperature adjustment apparatus and method
US20110098616A1 (en) * 2009-10-13 2011-04-28 Mego Afek Ac Ltd. Compression bag
US20110172749A1 (en) * 2010-01-08 2011-07-14 Christensen Scott A Methods and apparatus for enhancing vascular access in an appendage to enhance therapeutic and interventional procedures
US8016778B2 (en) 2007-04-09 2011-09-13 Tyco Healthcare Group Lp Compression device with improved moisture evaporation
US8016779B2 (en) 2007-04-09 2011-09-13 Tyco Healthcare Group Lp Compression device having cooling capability
US8021388B2 (en) 2007-04-09 2011-09-20 Tyco Healthcare Group Lp Compression device with improved moisture evaporation
US8066752B2 (en) 2003-09-24 2011-11-29 Dynatherm Medical, Inc. Methods and apparatus for adjusting body core temperature
US8070699B2 (en) 2007-04-09 2011-12-06 Tyco Healthcare Group Lp Method of making compression sleeve with structural support features
US8109892B2 (en) 2007-04-09 2012-02-07 Tyco Healthcare Group Lp Methods of making compression device with improved evaporation
US8114117B2 (en) 2008-09-30 2012-02-14 Tyco Healthcare Group Lp Compression device with wear area
US8652079B2 (en) 2010-04-02 2014-02-18 Covidien Lp Compression garment having an extension
CN103889387A (en) * 2011-10-25 2014-06-25 黑泽谅 Medical treatment device and medical treatment method
CN103908400A (en) * 2014-04-01 2014-07-09 山东梁山三利树脂有限公司 Blood circulation promoting instrument
US9205021B2 (en) 2012-06-18 2015-12-08 Covidien Lp Compression system with vent cooling feature
CN105662808A (en) * 2016-03-29 2016-06-15 孙香莲 Upper limb massager after breast cancer operation
US10071011B2 (en) 2014-06-30 2018-09-11 Kpr U.S., Llc Compression garment inflation
CN109464272A (en) * 2018-12-12 2019-03-15 江苏美德愈医疗科技有限公司 The negative high voltage diabetes Wound treating device and operating method of segmented
USD889634S1 (en) 2018-08-10 2020-07-07 Otivio As Pressure control unit
US10751221B2 (en) 2010-09-14 2020-08-25 Kpr U.S., Llc Compression sleeve with improved position retention
USD900996S1 (en) 2017-10-16 2020-11-03 Otivio As Pressure chamber
US10940075B2 (en) 2017-09-29 2021-03-09 Otivio As Medical pressure therapy device and components thereof
US11110021B2 (en) 2017-09-29 2021-09-07 Otivio As Medical pressure therapy device and components thereof
US11259985B2 (en) 2017-09-29 2022-03-01 Otivio As Medical pressure therapy device and components thereof
US20230240691A1 (en) * 2018-11-28 2023-08-03 Steve Eugene Everett Compression exertion device

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5450179A (en) * 1977-09-29 1979-04-19 Katsumasa Hara Air massager
CN85200905U (en) * 1985-04-01 1985-09-10 中山医学院 Microcomputerized enhanced external counter-pulsation for treatment of coronary heart diseases
JP2004261592A (en) * 2003-02-12 2004-09-24 Nishimura Kikai Kk External counter pulsation apparatus
JP7186453B2 (en) * 2020-01-20 2022-12-09 株式会社辰巳菱機 Blood circulation promotion device

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2249579A (en) * 1939-08-05 1941-07-15 John G Rea Circulation promotion device
US2832336A (en) * 1955-06-23 1958-04-29 Davis Physiotherapy device
US2833275A (en) * 1956-02-28 1958-05-06 Tunnicliffe Edward Alber James Mechanical breathing apparatus
US3053249A (en) * 1959-08-25 1962-09-11 Gorman Rupp Ind Inc Cardiac massage apparatus
US3403673A (en) * 1965-07-14 1968-10-01 Welton Whann R Means and method for stimulating arterial and venous blood flow
US3478737A (en) * 1967-02-23 1969-11-18 William R Rassman Heart massager

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2249579A (en) * 1939-08-05 1941-07-15 John G Rea Circulation promotion device
US2832336A (en) * 1955-06-23 1958-04-29 Davis Physiotherapy device
US2833275A (en) * 1956-02-28 1958-05-06 Tunnicliffe Edward Alber James Mechanical breathing apparatus
US3053249A (en) * 1959-08-25 1962-09-11 Gorman Rupp Ind Inc Cardiac massage apparatus
US3403673A (en) * 1965-07-14 1968-10-01 Welton Whann R Means and method for stimulating arterial and venous blood flow
US3478737A (en) * 1967-02-23 1969-11-18 William R Rassman Heart massager

Cited By (136)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4269175A (en) * 1977-06-06 1981-05-26 Dillon Richard S Promoting circulation of blood
DE2937360A1 (en) * 1979-09-15 1981-04-02 Dietrich 2100 Hamburg Schmidt Massage instrument for circulation trouble - comprises two hollow cylindrical components sealed by sleeves to human limbs
US4388919A (en) * 1980-11-17 1983-06-21 Intermedics Cardiassist Corporation Rapid stabilization of external cardiac pulsation
FR2510399A1 (en) * 1981-08-03 1983-02-04 Jobst Institute METHOD AND APPARATUS FOR DYNAMICALLY APPLYING A PRESSURE WAVE TO AN END OF A MAN OR ANIMAL
FR2519544A1 (en) * 1982-01-11 1983-07-18 Casile Jean Pierre CIRCULATORY ASSISTANCE DEVICE
US4753226A (en) * 1985-04-01 1988-06-28 Biomedical Engineering Development Center of Sun Yat-Sen University of Medical Science Combination device for a computerized and enhanced type of external counterpulsation and extra-thoracic cardiac massage apparatus
WO1988005667A1 (en) * 1987-01-30 1988-08-11 Baxter Travenol Laboratories, Inc. Blood extraction assist apparatus and method
US4883462A (en) * 1987-01-30 1989-11-28 Baxter Travenol Laboratories, Inc. Blood extraction assist apparatus and method
US5701919A (en) * 1991-09-30 1997-12-30 Thoratec Laboratories Corporation Step-down skeletal muscle energy conversion system
US5984857A (en) * 1991-09-30 1999-11-16 Thoratec Laboratories Corporation Step-down skeletal muscle energy conversion system
US5344385A (en) * 1991-09-30 1994-09-06 Thoratec Laboratories Corporation Step-down skeletal muscle energy conversion system
US5653676A (en) * 1991-09-30 1997-08-05 Thoratec Laboratories Corporation Step-down skeletal muscle energy conversion method
US5672148A (en) * 1991-12-06 1997-09-30 Maunier; Daniel Hydraulic device for lymphatic drainage and massage of the human body
US20030139255A1 (en) * 1991-12-17 2003-07-24 Kinetic Concepts, Inc. Pneumatic compression device and methods for use in the medical field
US6572621B1 (en) 1992-05-07 2003-06-03 Vasomedical, Inc. High efficiency external counterpulsation apparatus and method for controlling same
EP0569308A1 (en) * 1992-05-07 1993-11-10 Vasomedical, Inc. A high efficiency external counter pulsation apparatus and method for controlling same
US5554103A (en) * 1992-05-07 1996-09-10 Vasomedical, Inc. High efficiency external counterpulsation apparatus and method for controlling same
US20050070755A1 (en) * 1993-05-06 2005-03-31 Zhensheng Zheng High efficiency external counterpulsation method
US5425742A (en) * 1994-03-28 1995-06-20 Patrick S. Quigley Use of hollow hypobaric chambers on body parts for increasing blood flow, reducing pressure and decreasing pain
USRE40814E1 (en) * 1996-06-11 2009-06-30 Hill-Rom Services, Inc. Oscillatory chest compression device
US20050137507A1 (en) * 1997-08-18 2005-06-23 Paul Shabty Counterpulsation device using noncompressed air
US20040106885A1 (en) * 1997-08-18 2004-06-03 Paul Shabty Counterpulsation device using noncompressed air
US6589267B1 (en) 2000-11-10 2003-07-08 Vasomedical, Inc. High efficiency external counterpulsation apparatus and method for controlling same
US7314478B2 (en) 2000-11-10 2008-01-01 Vasomedical, Inc. High efficiency external counterpulsation apparatus and method for controlling same
US6962599B2 (en) 2000-11-10 2005-11-08 Vasomedical, Inc. High efficiency external counterpulsation apparatus and method for controlling same
US20020107461A1 (en) * 2000-11-10 2002-08-08 Hui John C.K. High efficiency external counterpulsation apparatus and method for controlling same
US20050131456A1 (en) * 2000-11-10 2005-06-16 Hui John C.K. High efficiency external counterpulsation apparatus and method for controlling same
US6620116B2 (en) 2000-12-08 2003-09-16 Michael P. Lewis External counterpulsation unit
EP1392216A4 (en) * 2001-05-10 2007-03-28 Pptt Llc External counterpulsation cardiac assist device
KR100833669B1 (en) * 2001-05-10 2008-05-29 피피티티 엘엘씨 External counterpulsation cardiac assist device
EP1392216A2 (en) * 2001-05-10 2004-03-03 Pptt Llc External counterpulsation cardiac assist device
US8043239B2 (en) 2001-05-10 2011-10-25 Pptt, Llc External counterpulsation (ECP) device for use in an ambulance or the like for heart attack patients to limit heart muscle damage
US20080033228A1 (en) * 2001-05-10 2008-02-07 Jahangir Rastegar External counterpulsation (ECP) device for use in an ambulance or the like for heart attack patients to limit heart muscle damage
WO2003099188A1 (en) * 2002-05-23 2003-12-04 Otto Bock Healthcare Lp Pulsating pressure chamber and method for enhanced blood flow
US20040024322A1 (en) * 2002-05-23 2004-02-05 Caspers Carl A. Pulsating pressure chamber and method for enhanced blood flow
US20030233118A1 (en) * 2002-06-13 2003-12-18 Hui John C. K. Method for treating congestive heart failure using external counterpulsation
US7048702B2 (en) 2002-06-13 2006-05-23 Vasomedical, Inc. External counterpulsation and method for minimizing end diastolic pressure
US8021314B2 (en) 2002-12-31 2011-09-20 Otivio As Device for applying a pulsating pressure to a local region of the body and the applications thereof
WO2004058131A2 (en) * 2002-12-31 2004-07-15 Thermonor As Device for applying a pulsating pressure to a local region of the body and applications thereof
EP1736132A3 (en) * 2002-12-31 2009-02-11 Thermonor AS Device for applying a pulsating pressure to a local region of the body and applications thereof
EP1736131A2 (en) 2002-12-31 2006-12-27 Thermonor AS Device for applying a pulsating pressure to a local region of the body and applications thereof
EP1736131A3 (en) * 2002-12-31 2009-02-11 Thermonor AS Device for applying a pulsating pressure to a local region of the body and applications thereof
US20110301510A1 (en) * 2002-12-31 2011-12-08 Otivio As Device for applying a pulsating pressure to a local region of the body and the applications thereof
WO2004058131A3 (en) * 2002-12-31 2004-08-26 Thermonor As Device for applying a pulsating pressure to a local region of the body and applications thereof
US8361001B2 (en) * 2002-12-31 2013-01-29 Otivio As Device for applying a pulsating pressure to a local region of the body and the applications thereof
US8821422B2 (en) 2002-12-31 2014-09-02 Otivio As Device for applying a pulsating pressure to a local region of the body and applications thereof
US20090036959A1 (en) * 2002-12-31 2009-02-05 Thermanor As Device for applying a pulsating pressure to a local region of the body and the applications thereof
US20050027218A1 (en) * 2002-12-31 2005-02-03 Marius Filtvedt Device for applying a pulsating pressure to a local region of the body and applications thereof
US20110021960A1 (en) * 2002-12-31 2011-01-27 Otivio As Device for applying a pulsating pressure to a local region of the body and the applications thereof
US7833179B2 (en) * 2002-12-31 2010-11-16 Otivio As Device for applying a pulsating pressure to a local region of the body and applications thereof
US7833180B2 (en) * 2002-12-31 2010-11-16 Otivio As Device for applying a pulsating pressure to a local region of the body and the applications thereof
CN1756522B (en) * 2002-12-31 2010-06-02 塞莫诺尔公司 Device for applying a pulsating pressure to a local region of the body
US8066752B2 (en) 2003-09-24 2011-11-29 Dynatherm Medical, Inc. Methods and apparatus for adjusting body core temperature
US20080021531A1 (en) * 2003-09-24 2008-01-24 Kane John R Methods and apparatus for increasing blood circulation
US8182521B2 (en) 2003-09-24 2012-05-22 Dynatherm Medical Inc. Methods and apparatus for increasing blood circulation
US20060058717A1 (en) * 2004-09-14 2006-03-16 Hui John C K External counterpulsation device having a curvilinear bed
US20060058716A1 (en) * 2004-09-14 2006-03-16 Hui John C K Unitary external counterpulsation device
US20060058715A1 (en) * 2004-09-14 2006-03-16 Hui John C External counterpulsation device with multiple processors
US20080064994A1 (en) * 2004-12-06 2008-03-13 Vissman S.R.L. Apparatus and Method for the Conditioning of Muscular Fibrils Reaction Coordination Capacity by Means a Pressure Wave, and Eesthetic and Therapeutic Application Thereof
US8105254B2 (en) * 2004-12-06 2012-01-31 Vissman S.R.L. Apparatus and method for the conditioning of muscular fibrils reaction coordination capacity by means of a pressure wave, and aesthetic and therapeutic application thereof
US20080234615A1 (en) * 2005-07-26 2008-09-25 Novamedix Distribution Limited Limited Durability Fastening for a Garment
US8539647B2 (en) 2005-07-26 2013-09-24 Covidien Ag Limited durability fastening for a garment
US9364037B2 (en) 2005-07-26 2016-06-14 Covidien Ag Limited durability fastening for a garment
US20090062703A1 (en) * 2005-12-12 2009-03-05 Tyco Healthcare Group Lp Compression Sleeve Having Air Conduits
US8079970B2 (en) 2005-12-12 2011-12-20 Tyco Healthcare Group Lp Compression sleeve having air conduits formed by a textured surface
US20110009785A1 (en) * 2005-12-12 2011-01-13 Tyco Healthcare Group Lp Compression sleeve having air conduits formed by a textured surface
US8029451B2 (en) 2005-12-12 2011-10-04 Tyco Healthcare Group Lp Compression sleeve having air conduits
US20070272250A1 (en) * 2006-05-24 2007-11-29 Michael Paul Lewis External pulsation treatment apparatus
US7981066B2 (en) 2006-05-24 2011-07-19 Michael Paul Lewis External pulsation treatment apparatus
US20090312675A1 (en) * 2006-07-19 2009-12-17 The Brigham And Women's Hospital, Inc. Sub-atmospheric pressure chamber for mechanical assistance of blood flow
WO2008011548A1 (en) * 2006-07-19 2008-01-24 The Brigham And Women's Hospital, Inc. Sub-atmospheric pressure chamber for mechanical assistance of blood flow
EP1884226A1 (en) 2006-08-02 2008-02-06 Dynatherm Medical, Inc. Methods and apparatus for increasing blood circulation
US9308148B2 (en) 2006-12-04 2016-04-12 Thermatx, Inc. Methods and apparatus for adjusting blood circulation
US20080132816A1 (en) * 2006-12-04 2008-06-05 Kane John Roy Methods and Apparatus for Adjusting Blood Circulation
US11324656B2 (en) 2006-12-04 2022-05-10 Avacore Technologies, Inc. Methods and apparatus for adjusting blood circulation
US8603150B2 (en) 2006-12-04 2013-12-10 Carefusion 2200, Inc. Methods and apparatus for adjusting blood circulation
US10350134B2 (en) 2006-12-04 2019-07-16 Avacore Technologies, Inc. Methods and apparatus for adjusting blood circulation
US20080132976A1 (en) * 2006-12-04 2008-06-05 Kane John Roy Methods and apparatus for adjusting blood circulation
FR2913594A1 (en) * 2007-03-16 2008-09-19 Francois Dufay Open wound treating equipment for e.g. cosmetic field, has envelope placed around part of body to be treated and constituted of lower and upper shells that define cavity whose section is greater than that of body to be treated
US9387146B2 (en) 2007-04-09 2016-07-12 Covidien Lp Compression device having weld seam moisture transfer
US20080249443A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device Having Weld Seam Moisture Transfer
US8034007B2 (en) 2007-04-09 2011-10-11 Tyco Healthcare Group Lp Compression device with structural support features
US8021388B2 (en) 2007-04-09 2011-09-20 Tyco Healthcare Group Lp Compression device with improved moisture evaporation
US8016779B2 (en) 2007-04-09 2011-09-13 Tyco Healthcare Group Lp Compression device having cooling capability
US8070699B2 (en) 2007-04-09 2011-12-06 Tyco Healthcare Group Lp Method of making compression sleeve with structural support features
US8992449B2 (en) 2007-04-09 2015-03-31 Covidien Lp Method of making compression sleeve with structural support features
US20080249444A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device with Structural Support Features
US9808395B2 (en) 2007-04-09 2017-11-07 Covidien Lp Compression device having cooling capability
US8109892B2 (en) 2007-04-09 2012-02-07 Tyco Healthcare Group Lp Methods of making compression device with improved evaporation
US20080249442A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Breathable Compression Device
US8740828B2 (en) 2007-04-09 2014-06-03 Covidien Lp Compression device with improved moisture evaporation
US8128584B2 (en) 2007-04-09 2012-03-06 Tyco Healthcare Group Lp Compression device with S-shaped bladder
US8162861B2 (en) 2007-04-09 2012-04-24 Tyco Healthcare Group Lp Compression device with strategic weld construction
US8721575B2 (en) 2007-04-09 2014-05-13 Covidien Lp Compression device with s-shaped bladder
US8029450B2 (en) 2007-04-09 2011-10-04 Tyco Healthcare Group Lp Breathable compression device
US20080245361A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression Device with S-Shaped Bladder
US8506508B2 (en) 2007-04-09 2013-08-13 Covidien Lp Compression device having weld seam moisture transfer
US20080249441A1 (en) * 2007-04-09 2008-10-09 Tyco Healthcare Group Lp Compression device with strategic weld construction
US8597215B2 (en) 2007-04-09 2013-12-03 Covidien Lp Compression device with structural support features
US8016778B2 (en) 2007-04-09 2011-09-13 Tyco Healthcare Group Lp Compression device with improved moisture evaporation
US8622942B2 (en) 2007-04-09 2014-01-07 Covidien Lp Method of making compression sleeve with structural support features
US9084713B2 (en) 2007-04-09 2015-07-21 Covidien Lp Compression device having cooling capability
US9114052B2 (en) 2007-04-09 2015-08-25 Covidien Lp Compression device with strategic weld construction
US9107793B2 (en) 2007-04-09 2015-08-18 Covidien Lp Compression device with structural support features
US20080319248A1 (en) * 2007-06-20 2008-12-25 Michael Paul Lewis Hydraulically Actuated External Pulsation Treatment Apparatus
US8114037B2 (en) 2007-06-20 2012-02-14 Michael Paul Lewis Hydraulically actuated external pulsation treatment apparatus
US20090177184A1 (en) * 2008-01-09 2009-07-09 Christensen Scott A Method and apparatus for improving venous access
US10137052B2 (en) 2008-04-07 2018-11-27 Kpr U.S., Llc Compression device with wear area
US20100081975A1 (en) * 2008-09-30 2010-04-01 Tyco Healthcare Group Lp Compression Device with Removable Portion
US8632840B2 (en) 2008-09-30 2014-01-21 Covidien Lp Compression device with wear area
US8235923B2 (en) 2008-09-30 2012-08-07 Tyco Healthcare Group Lp Compression device with removable portion
US8114117B2 (en) 2008-09-30 2012-02-14 Tyco Healthcare Group Lp Compression device with wear area
US8657864B2 (en) 2008-12-16 2014-02-25 Otivio As Portable patient temperature adjustment apparatus and method
US20100152821A1 (en) * 2008-12-16 2010-06-17 Thermanor As Portable patient temperature adjustment apparatus and method
US20100152633A1 (en) * 2008-12-16 2010-06-17 Thermanor As Portable patient temperature adjustment apparatus and method
US20110098616A1 (en) * 2009-10-13 2011-04-28 Mego Afek Ac Ltd. Compression bag
US8622943B2 (en) * 2009-10-13 2014-01-07 Mego Afek Ac Ltd. Compression bag
US20110172749A1 (en) * 2010-01-08 2011-07-14 Christensen Scott A Methods and apparatus for enhancing vascular access in an appendage to enhance therapeutic and interventional procedures
US8771329B2 (en) 2010-01-08 2014-07-08 Carefusion 2200, Inc. Methods and apparatus for enhancing vascular access in an appendage to enhance therapeutic and interventional procedures
US8652079B2 (en) 2010-04-02 2014-02-18 Covidien Lp Compression garment having an extension
US10751221B2 (en) 2010-09-14 2020-08-25 Kpr U.S., Llc Compression sleeve with improved position retention
CN103889387A (en) * 2011-10-25 2014-06-25 黑泽谅 Medical treatment device and medical treatment method
CN103889387B (en) * 2011-10-25 2016-07-27 黑泽谅 Therapy equipment and Therapeutic Method
US9205021B2 (en) 2012-06-18 2015-12-08 Covidien Lp Compression system with vent cooling feature
CN103908400A (en) * 2014-04-01 2014-07-09 山东梁山三利树脂有限公司 Blood circulation promoting instrument
US10071011B2 (en) 2014-06-30 2018-09-11 Kpr U.S., Llc Compression garment inflation
CN105662808A (en) * 2016-03-29 2016-06-15 孙香莲 Upper limb massager after breast cancer operation
US10940075B2 (en) 2017-09-29 2021-03-09 Otivio As Medical pressure therapy device and components thereof
US11110021B2 (en) 2017-09-29 2021-09-07 Otivio As Medical pressure therapy device and components thereof
US11259985B2 (en) 2017-09-29 2022-03-01 Otivio As Medical pressure therapy device and components thereof
USD900996S1 (en) 2017-10-16 2020-11-03 Otivio As Pressure chamber
USD901670S1 (en) 2018-08-10 2020-11-10 Otivio As Pressure control unit
USD889634S1 (en) 2018-08-10 2020-07-07 Otivio As Pressure control unit
US20230240691A1 (en) * 2018-11-28 2023-08-03 Steve Eugene Everett Compression exertion device
US11871936B2 (en) * 2018-11-28 2024-01-16 Steve Eugene Everett Compression exertion device
CN109464272A (en) * 2018-12-12 2019-03-15 江苏美德愈医疗科技有限公司 The negative high voltage diabetes Wound treating device and operating method of segmented

Also Published As

Publication number Publication date
JPS5025082A (en) 1975-03-17
JPS6021739B2 (en) 1985-05-29

Similar Documents

Publication Publication Date Title
US3878839A (en) Cardiac assist apparatus
CA2357737C (en) Body pulsating apparatus
US5743864A (en) Method and apparatus for performing cardio-pulmonary resuscitation with active reshaping of chest
US6846294B2 (en) External counterpulsation cardiac assist device
US4453538A (en) Medical apparatus
US3654919A (en) Process and apparatus for synchronous assisting of blood circulation
US8043239B2 (en) External counterpulsation (ECP) device for use in an ambulance or the like for heart attack patients to limit heart muscle damage
US5971910A (en) Method and apparatus for assisting a heart to pump blood by applying substantially uniform pressure to the ventricles
US5437610A (en) Extremity pump apparatus
US9795532B2 (en) CPR compression device and method
US5569170A (en) Pulsator
JP2004526538A5 (en)
US3734087A (en) External pressure circulatory assist
US8900168B2 (en) Body surface compression with pneumatic shortening element
US3865102A (en) External cardiac assist apparatus
CA2379184A1 (en) Brace
JPH08507459A (en) Active pressure / vacuum cardiac assist / maintenance apparatus and method
JPS6033509B2 (en) heart stimulator
US8142372B2 (en) External left ventricular assist device for treatment of congestive heart failure
GB1599607A (en) Device for applying presure to a patients limb
CN87106511A (en) Push-plate type cover bag in a kind of external counterpulsation apparatus