US3663966A - Implantable artificial heart - Google Patents

Implantable artificial heart Download PDF

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US3663966A
US3663966A US100255A US3663966DA US3663966A US 3663966 A US3663966 A US 3663966A US 100255 A US100255 A US 100255A US 3663966D A US3663966D A US 3663966DA US 3663966 A US3663966 A US 3663966A
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Prior art keywords
piston
accordance
heart
artificial heart
valve
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US100255A
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English (en)
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Pierre Lavigne
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Commissariat a lEnergie Atomique et aux Energies Alternatives CEA
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Commissariat a lEnergie Atomique CEA
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/894—Passive valves, i.e. valves actuated by the blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/438—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical
    • A61M60/441—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being mechanical generated by an electromotor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices

Definitions

  • An implantable artificial heart (without extra-corporal circulation) includes a prime mover consisting of a Rankine or Him [30] Foreign Application Monty Data steam engine and a boiler heated by a radioisotopic source.
  • a Dec. 31, 1969 France ..6945780 relaxation mechanism is interposed between the piston of the Aug. 12, 1970 France ..7029726 engine and a hydraulic transmission device and comprises a spring enclosed between two components which are respec- [52] US. Cl.
  • Abutment means limit 51 Int. Cl ..A6lf 1/24, A61m 1/03, F04b 45/00 spreading apart of Said components to a value at which the [58] Field of Search ..3/1 DIG. 2; 128/l R, 214 R; compression of the spring corresponds maintenance of the 417/395 401 blood pressure normally prevailing at the end of the systole phase.
  • thermodynamic fluid that total reliability must be ensured despite the fact that it is impossible to lubricate some of the driving parts which are in contact with the thermodynamic fluid
  • the power cycle of the receiving machine which is intended to reconstitute approximately the pressure curve of the human heart is very different both in periodic time and power distribution from the cycle of conventional rotary driving machines.
  • Inertia, speed reduction or solid or fluid transmission must accordingly be introduced and have the effect of increasing the weight, reducing mechanical efficiency and making it more difficult to achieve reliability.
  • the object of the invention is to provide an implantable artificial heart which meets practical requirements more effectively than those of the prior art, especially insofar as the difficulties referred to above are reduced to a considerable extent.
  • an implantable artificial heart essentially comprising a hydraulic device for producing the blood-moving pressure which is driven by a rapid-expansion motor and a linear-displacement piston, a relaxation mechanism which is interposed between the driving piston and the hydraulic device and comprises an elastic member such as a spring enclosed between two components which are rigidly fixed in one case to the driving piston and in the other case to the driving member of the hydraulic device, abutment means for limiting the spacing of said components to a value at which the compression of the spring corresponds to maintenance of the pressure at the end of the systole phase by means of the pump, means for temporarily locking the component which is coupled to the driving piston in the state of maximum extension of said piston during the working stroke thereof and a member which initiates unlocking of said means at the end of expansion of the spring.
  • a hydraulic device for producing the blood-moving pressure which is driven by a rapid-expansion motor and a linear-displacement piston
  • a relaxation mechanism which is interposed between the driving piston and the hydraulic device and comprises an elastic member
  • the motor must be of a type which absorbs only a small amount of energy during the non-propelling portion of the cycle (systole). It is possible in particular to employ a Rankine or Him-cycle motor which provides in addition to its simplicity of adaptation to this purpose the advantage of readily obtaining a constant pressure (that of the condenser) within the casing of the device and consequently of permitting easy regulation during the diastole phase.
  • FIG. 1 is a general diagram of a group of four cardiac modules which carry out all the functions of the physiological heart;
  • FIG. 2 is a diagrammatic illustration of the motor and the device for transmitting the power generated by the motor to the cardiac modules;
  • FIG. 3 is a curve which is representative of the pressures delivered by the ventricular cardiac modules of the embodiment which is illustrated in FIGS. 1 and 2;
  • FIG. 4 is similar to FIG. 2 and is a vertical central sectional view showing an alternative form of construction.
  • the implantable artificial heart may be regarded as being constituted by four sub-assemblies which will be discussed successively: the blood-pumping sub-assembly which is constituted by cardiac modules and a pump for actuating said cardiac modules (as shown in FIG. 1), the motor and the relaxation mechanism for transferring energy (as shown in FIG. 2).
  • Pumping sub-assembly The pumping sub-assembly which is illustrated diagrammatically in FIG. 1 is intended to ensure both pulmonary circulation and general circulation.
  • the sub-assembly comprises four cardiac modules corresponding to the left and right auricles 106 and 10D and to the left and right ventricles 126 and 12D.
  • Each module which is shown is of a known type consisting of a shell 14 having an opening which provides a communication with a control fluid and an opening which provides a communication with a connecting duct 16 or 18.
  • a flexible diaphragm 20 provides within each shell 14 a separation between a compartment 22 containing the pressure-transmission liquid and a compartment 14 which contains the blood. Said diaphragm as well as that part of the shell which is in contact with the blood is lined with dacron velvet on which the fibrin is deposited.
  • the duct 18 is mounted between the vena cava and the pulmonary artery and connected to the right auricle 10D and to the right ventricle 12D.
  • Artificial ball valves 26 which are placed in the duct 18 have a function which is similar to that of the valves of a natural heart.
  • the duct 16 is mounted in a similar manner between the pulmonary vein and the aorta and connected to the left auricle 106 and to the left ventricle 12G.
  • the hydraulic control sub-assembly is associated with the modules. This sub-assembly actuates the ventricles and the au ricles in a wholly synchronous manner so that, on the one hand, the two ventricles are in a maximum blood-filling phase whereas the two auricles are in a minimum blood-filling phase and that, on the other hand, the sum of volumes of circulating blood contained in the ventricles and auricles is constant.
  • FIGS. 1 and 2 This result is achieved by means of the assembly which is illustrated in FIGS. 1 and 2 and comprises a double piston 28 which moves under the action of a rod 30 while displacing the same quantity of intermediate liquid within two concentric chambers 32 and 34.
  • the first chamber is cylindrical and the second chamber is annular and placed around the first.
  • the system is so designed that the supply of energy to the piston 28 takes place at the time of displacement of this latter in the direction of the arrow f.
  • the intermediate liquid contained in the chambers 32 and 34 is then put under pressure and discharges the blood contained in the ventricles 12D and 126.
  • the same intermediate liquid contained in a single chamber 36 which is limited by the other face of the piston 28 also draws blood at the same time from the auricles 10D and 106.
  • the sub-assemblies which are illustrated in FIG. 1 constitute an extremely complete pumping system. In some cases, it may be found necessary for practical reasons to adopt simplified solutions and in particular the following:
  • the right-hand circulation section (ventrical 12D, auricle D and compartment 34) can be dispensed with: the principle which has already been described remains the same.
  • the double piston is accordingly replaced by a single piston
  • the two auricles can be dispensed with and the intennediate liquid within the compartment 26 can be replaced by a fluid in which the liquid and vapor phases are brought together and which is such that the vapor pressure is substantially equal to the blood pressure in the diastole phase.
  • One of the drawbacks of this arrangement clearly lies in the fact that the equilibrium of the piston is no longer indifferent at the time of its return irrespective of the pressurization of the body. Fever can also destroy the indifferent equilibrium of the piston,
  • the auricles 10D and 100 can be dispensed with as well as the wall which isolates the chamber 36 from the mechanism at the pressure which prevails within the motor casing.
  • Said spring restores the indifferent equilibrium of the piston at the time of its return.
  • the equilibrium of the fluid is responsive to the blood pressure upstream of the heart and will be modified if the person who is carrying the heart moves to a higher altitude.
  • This spring can be dispensed with by establishing a pressure p which is close in value to that of the blood but in that case the efficiency of the device is appreciably reduced.
  • the pump which serves to actuate the cardiac modules can be constituted by two opposite pistons having symmetrical motion of the type designated by the reference 28.
  • This design solution entails the use either of two motors and two synchronized relaxation mechanisms of the type mentioned hereinafter or of a single motor and a single relaxation system to which should be added a transmission device for producing the symmetrical movements.
  • the motor will be described only very briefly since it is of the conventional Rankine-cycle type.
  • the motor is illustrated diagrammatically in FIG. 2 and comprises a boiler which is heated by an alpha radioisotope source. It is possible in particular to employ a plutonium-238 source containing approximately 30 g of radioactive material. Said source 40 is placed within the boiler 42 proper.
  • the boiler 42 communicates with a cylindrical expansion chamber 44 via an admission valve 46 which is thrust back towards its seat by elastic restoring means represented by a spring.
  • a piston 48 which is placed within the cylinder 44 uncovers ports 50 through which the expanded vapor is exhausted into the casing 52 which contains the motor and the relaxation mechanism.
  • the top end-wall of said casing constitutes a capillary condenser 54 which is cooled by the intermediate liquid (this liquid being in turn cooled by the blood).
  • the walls of the casing 52 are also provided with a capillary network in order to return any trace of condensation to the condenser 54.
  • the use of this arrangement permits operation in all orientations of the heart.
  • the condensed liquid is returned to the boiler 42 through a suction tube 56 fitted with check valves 57 and a lift and force pump which will be described hereinafter.
  • the boiler 42 and the cylinder 44 are heat-insulated by means of layers 58 of thermal insulation material.
  • the motor is of known type and therefore does not call for any extended description. It need only be noted in addition that, although some organic liquids can be contemplated, water appears to be the most suitable working fluid at the present time. In the case of water, a pressure at the condenser of the order of O. bar is preferably adopted.
  • the piston 48 can be fitted with a mechanism for maintaining the admission valve 46 in the open position. Once the valve has been dislodged from its seat by the piston during the return stoke of this latter, it is in fact an advantage to complete the force of attraction produced by the armatures 76 and the magnets 78 (which will be described later) by means of an elastic force which is produced by a complementary mechanism. Said mechanism can be arranged as illustrated in FIGS. 5 and 6.
  • the magnetic spring is a magnet 110 carried by the piston and a magnet 112 carried by the guide rod of valve 108, the opposed poles of magnets 110 and 112 having opposite polarity.
  • the structure comprises a push-rod 122 which is capable of moving within the piston between a position in which said rod projects from this latter (as shown in full lines in FIG. 6) and a position in which it penetrates into the piston.
  • Elastic means is constituted in the embodiment illustrated in FIG. 6 by a magnet 124 which is carried by the piston 48 and by a ferromagnetic washer 126 of the push-rod tend to bring this latter to a projecting position. Leak-tightness is ensured by the plug 130 which is held in position by means of the circlip 132.
  • the operation of the mechanism accordingly takes place as follows: when the piston reaches the end of its return stroke, the push-rod 122 comes into contact with the valve and penetrates into the piston since the stiffness of the magnetic spring which maintains said push-rod in the projecting position is not sufiicient to overcome the pressure forces which are exerted on the valve 46. The boss 134 then comes into contact with the valve 46 and unseats this latter. The pressures are balanced on each side of the valve 46 and the push-rod 122 returns to the projecting position, lifts the valve 46 to a further extent and maintains it in the open position until the piston 48 has again moved away from the valve.
  • the driving piston 48 is coupled with the double piston 28 by means of the relaxation mechanism.
  • This mechanism comprises a first supporting member 60 which is rigidly fixed to the driving piston, a second supporting member 62 which is rigidly fixed to the rod 30 of the piston 28 and a spring 64 which is compressed between the members 60 and 62.
  • These two members are provided with abutment flanges 66 and 68 which cooperate with each other in order to limit the expansion of the spring 64 to a value at which its residual compression force corresponds to establishment of the blood pressure at the end of the systole phase.
  • the members 60 and 62 therefore constitute two components of a cage which encloses the spring.
  • the member 60 carries a resilient catch 70 which is intended to engage a bearing stop 72 provided on the casing 52 when the piston 48 completes its working stroke which is accompanied by the compression of the spring 64. So far as the member 62 is concerned, said member carries an arm 74 which releases the catch 70 when the expansion of the spring 64 is completed.
  • the locking system comprising a resilient catch and bearing stop as illustrated in FIG. 2, it would be possible to employ a system comprising magnets and backplates which casing 52.
  • the member 60 further carries magnetic back-plates 76 which are attracted on completionof the return stroke of the piston 48 by magnets 78 which are secured to the casing 52.
  • the lift and force pump for re-injecting condensate into the boiler makes use of the relative displacements of the members 60 and 62.
  • Said pump comprises a plunger 80 and a cylinder 82.
  • the plunger 80 is connected to an enlarged end portion of the rod 30 by means of one or a number of rods 84 (only one of these latter being shown in FIG. 2).
  • the cylinder 82 which is secured to the cylinder 44 by means of a jacket 86 having open portions also constitutes a guide bearing for the rods 84.
  • leak-tightness between two media having different functions within the pumping sub-assembly must in all cases be absolute.
  • flexible rolling seals are contemplated for this purpose, other means may be adopted by way of alternative. ln FIGS. 2 and 4, these seals are designated by the reference numerals 31, 33, 35, 37 and 31', 33', 35', 37 and 39.
  • FIGS. 1 and 2 The operation of the artificial heart which is illustrated in FIGS. 1 and 2 will now be described with reference also to FIG. 3. Since cardiac modules are known per se, only the operation of the assembly consisting of motor and relaxation mechanism will be discussed in detail.
  • the following stage of operation corresponds to the expansion of the spring 64.
  • the driving piston 48 and associated components are rendered motionless by the catch 70 which is held in position under the pressure of the spring 64.
  • the initial part of said phase corresponds to the exhaust of vapor through the ports 50 which, in a standard cycle, remain uncovered for approximately onethird of a second.
  • the spring 64 is applied against the member 60, drives the double piston 28 downwards and discharges the intermediate liquid contained in the chambers 32 and 34.
  • this phase of operation corresponds to the systole.
  • the duration of this phase is set on the one hand by the resistance offered by the circulatory system of the human body and on the other hand by the force-compression characteristic of the spring 64.
  • the device is capable of providing a systole period t, t, (as shown in FIG. 3) which is practically equal to that of the human heart and a decrease in pressure during the systole period which is similar to the shape of the corresponding curve in the case of the human heart.
  • the pressures which prevail within the ventricles 12G and 12D are in a ratio which is imposed by the resistances of the circulatory systems as is the case throughout the duration of the phase.
  • the moving system as thus constituted then returns as a single unit towards its initial position under the action of the resultant of the pressure forces, especially by virtue of the passage (to be chosen accordingly) of the rod 30 and if necessary of the elasticity which is given to the shell diaphragms.
  • the addition of a light spring may prove necessary.
  • a complementary restoring action can be provided by the magnets 78 and the magnetic back-plates 76 when these elements move towards each other although the essential function of these latter is thermodynamic.
  • the phase last mentioned corresponds to recompression of the working fluid which remains within the cylinder 44.
  • the moving system causes forcible opening of the admission valve 46 at the end of the return travel of said system. Accordingly, the bottom face of the piston 48 is provided with an abutment extension 88. The initial conditions are thus restored.
  • the phase just mentioned corresponds to the diastole period (filling of the ventricles owing to the displacements of the intermediate fluid and to the action of the artificial valves 26).
  • the blood pressure is imposed by the body itself.
  • Condensation of the vapor which is discharged through the port 50 takes place continuously within the capillary condenser 54.
  • the small drops which may appear on the walls of the casing 52 are returned to the condenser by capillarity.
  • FIG. 3 shows that the pressure curve provided by the implantable artificial heart which has just been described reconstitutes the curve of the real cardiac beat to a sutficient degree of approximation to be acceptable.
  • the relaxation mechanism can be associated with a motor having an expansion within the range of 50 bars to l bar approximately, thereby resulting in a force at the beginning of projection of the piston 48 which is'of the order of 150 kgs. The relaxation mechanism reduces this initial force to a value which is wholly compatible with the strength of the arteries.
  • a further advantage of the device should also be noted and this is related to the fact that the moving system comprising the double pistons 28 and the driving piston 48 is in substantially indifferent equilibrium at the time of its return travel and that the resultant of the forces can readily be adjusted. This property permits of easy regulation and results in a stable device.
  • FIG. 4 differs essentially from that of FIG. 2 in the arrangement of the lift and force pump for re-injecting the condensate into the boiler.
  • the corresponding components of the embodiments of FIGS. 2 and 4 are designated by the same reference numerals followed by the prime index in FIG. 4.
  • a member 82' which, in this case, does not constitute the cylinder of the lift and force pump but only a guide bearing for an extension 90 of the rod 30; this makes it possible to dispense with the guide bearing 92 of the rod 30 which was provided in the embodiment of FIG. 2.
  • the rod is provided above the double piston 28 with an extension 94 which is rendered leak-tight by means of a seal 39, said extension being guided by a bearing 96 which is rigidly fixed to the casing and by a piston 98 which moves within a reinjection pump cylinder 100, said cylinder being also rigidly fixed to the casing.
  • the condensate is supplied to the pump through a pipe 102 fitted with a check valve and then discharged to the boiler through a second pipe 104 which is also fitted with a check valve.
  • a small pipe 106 permits pressure balancing between the two parts of the mechanism.
  • FIGS. 2 and 4 a number of assemblies of the type shown in FIGS. 2 and 4 can be associated in order to prevent shocks which give rise to inertia forces having a component parallel to the axis and which could not be tolerated by the patient.
  • a symmetrical arrangement which can comprise two motors for driving by means of relaxation mechanisms two hydrauliccontrol sub-assemblies which are grouped together in a single central block. The movements are made strictly symmetrical by means of a link-rod system. The arrangement can be reversed and provision accordingly made for two motors in a central block, with the result that only one admission valve is required for both motors.
  • An implantable artificial heart comprising: a hydraulic transmission device for imparting a moving pressure to the blood; a prime mover having a linear displacement driving piston having a rapid working stroke; and a relaxation mechanism mechanically coupling the driving piston and the hydraulic device, said mechanism having resilient means which is compressed between a first and a second components respectively secured to said driving piston and to a driving member of the hydraulic device and whose compression corresponds to the blood pressure at the beginning of systole when said two components are in their position closest to each other, abutment means for limiting the spreading of said components to a distance at which the compression of said resilient means corresponds to the pressure at the end of the systole phase, means for temporarily locking said first component upon arrival of said piston at the end of the working stroke thereof, and a member for releasing said locking means upon substantially complete expansion of the resilient means.
  • a heart in accordance with claim 1, wherein the hydraulic device comprises a single piston which is linearly movable within a cylinder and separates two compartments in said cylinder, diaphragm means for separating one of said compartments in two chambers, means for communicating the pressure in said two chambers to left and right ventricular blood, respectively, and means for communicating the liquid pressure in the other of said compartments to auricular blood.
  • the temporary-locking means comprise a catch carried by an elastic blade rigidly fixed to the component which is coupled to the driving piston and a stop which is rigidly fixed to the heart casing.
  • unlocking means are constituted by a stud rigidly fixed to the component which is coupled to the pump and releases the catch from the stop at the end of the expansion travel of the spring.
  • the magnetic spring comprises a magnet carried by the piston and a magnet carried by a guide rod of the valve and the opposite poles of the two magnets have the same polarity.
  • said elastic means comprise a push-rod which is capable of moving axially within the piston and is returned by a magnetic spring to a position in which said push-rod projects from the piston towards the admission valve.
  • said two assemblies being disposed symmetrically along a are grouped together in a central block and have a common common axis. admission valve.
  • An artificial heart in accordance with claim 15 wherein An tifi i l heart in accordance with claim 5 wherein the two motors are placed on each side of hydraulic devices which are g p mgether within a single block. a lmk rod system provided for synchronizing the operation 17.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Anesthesiology (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Prostheses (AREA)
US100255A 1969-12-31 1970-12-21 Implantable artificial heart Expired - Lifetime US3663966A (en)

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FR6945780A FR2082034A5 (OSRAM) 1969-12-31 1969-12-31

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Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4427470A (en) 1981-09-01 1984-01-24 University Of Utah Vacuum molding technique for manufacturing a ventricular assist device
US4473423A (en) * 1982-05-03 1984-09-25 University Of Utah Artificial heart valve made by vacuum forming technique
US4838889A (en) * 1981-09-01 1989-06-13 University Of Utah Research Foundation Ventricular assist device and method of manufacture
US6527698B1 (en) 2000-05-30 2003-03-04 Abiomed, Inc. Active left-right flow control in a two chamber cardiac prosthesis
US6540658B1 (en) 2000-05-30 2003-04-01 Abiomed, Inc. Left-right flow control algorithm in a two chamber cardiac prosthesis
GB2400561A (en) * 2003-04-14 2004-10-20 Martin Lister Perpetual pumping heart

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3379191A (en) * 1964-04-02 1968-04-23 Thermo Electron Eng Corp Nuclear powered mechanical heart
US3434162A (en) * 1966-12-13 1969-03-25 Us Health Education & Welfare Totally implanted artificial heart power system utilizing a rechargeable thermal energy source
US3534409A (en) * 1968-06-10 1970-10-20 Atomic Energy Commission Implantable circulatory support system
US3563028A (en) * 1968-07-22 1971-02-16 Mc Donnell Douglas Corp Implantable radioisotope-fueled stirling engine

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3379191A (en) * 1964-04-02 1968-04-23 Thermo Electron Eng Corp Nuclear powered mechanical heart
US3434162A (en) * 1966-12-13 1969-03-25 Us Health Education & Welfare Totally implanted artificial heart power system utilizing a rechargeable thermal energy source
US3534409A (en) * 1968-06-10 1970-10-20 Atomic Energy Commission Implantable circulatory support system
US3563028A (en) * 1968-07-22 1971-02-16 Mc Donnell Douglas Corp Implantable radioisotope-fueled stirling engine

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4427470A (en) 1981-09-01 1984-01-24 University Of Utah Vacuum molding technique for manufacturing a ventricular assist device
US4838889A (en) * 1981-09-01 1989-06-13 University Of Utah Research Foundation Ventricular assist device and method of manufacture
US4473423A (en) * 1982-05-03 1984-09-25 University Of Utah Artificial heart valve made by vacuum forming technique
US6527698B1 (en) 2000-05-30 2003-03-04 Abiomed, Inc. Active left-right flow control in a two chamber cardiac prosthesis
US6540658B1 (en) 2000-05-30 2003-04-01 Abiomed, Inc. Left-right flow control algorithm in a two chamber cardiac prosthesis
GB2400561A (en) * 2003-04-14 2004-10-20 Martin Lister Perpetual pumping heart

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Publication number Publication date
FR2082034A5 (OSRAM) 1971-12-10
SU404196A3 (OSRAM) 1973-10-26

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