• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    A cardiac prosthesis having an hydraulically actuated compressible blood pump (RV). An actuation chamber (116) adjacent the blood pump (RV) receives pulses of hydraulic actuation fluid from an actuator pump (120) through a fluid inlet path (126) to compress the blood pump (RV) during systole and eject blood therefrom. Between pulses the actuation fluid is permitted to drain from the actuation chamber (116) through an outlet path (132) into a reservoir (12). Discharge of fluid through the outlet path (132) is controlled by a dump valve (130) which is adapted to close or open the outlet path (132) primarily in response to forces which vary as a function of the flow of actuation fluid through the fluid inlet path (126).
    公开号:SU1438599A3
    申请号:SU833544251
    申请日:1983-01-18
    公开日:1988-11-15
    发明作者:С.Робинсон Томас；Китрилакис Сотирис；Б.Мартин Томас (Младший)
    申请人:Фокскрофт Ассошиэйтс (Фирма)；
    IPC主号:
    专利说明:

    by starting a 5- divided flexible bladder 6 or membrane on the chamber 7 of the Croi pump and the chamber 8 for the operating valve. Valve inlets 9, 10 and valve outlets 11, 12 serve to connect the HH chambers 3, 7 of the blood pump with the corresponding vessels. The motor 15 is connected to the drive pump 16, which, through the flexible channel 17, the malleable bag 14 is connected to the chamber 4, the pumps of the OLDs 16 and 20 are high-speed rotating

    8599
    diagonal pump. The bladder 2 of the blood pump is made of a single layer of high strength biocompatible elastomeric material. The body is made of hard metal or plastic. The alternating pulsation control is carried out by applying a control signal to the control valve, which is driven from the engine, which determines the direction and duration of each fluid pulse. 3 sec. and 2 z.p, f-ly. 13 il.

     The invention relates to medical equipment, in particular, to cardiac prosthesis devices, in particular, to a hydraulically driven artificial heart for replacement and full imitation of the heart and accessory devices of the circulatory system, including left ventricular auxiliary devices for implantation in the human body.
    The purpose of the invention is to simplify the design, reduce weight and increase reliability.
    FIG. I is given a schematic of a complete prosthetic heart; FIG. 2, the drive of the prosthetic heart of FIG. 1, general view; in fig. 3 - actuator with a three-way valve; embodiment; Fig "4 - the same, with a discharge valve; in fig. 5 the same, with a relief valve and a differential pressure regulator on its cap; FIG. 6 shows a discharge valve, vi, h from the top of the cap; in fig. 7. Discharge valve with collector; on fig B - the same, bottom view; in fig. 9 is a section A-A in FIG. 8; in fig. 10 - the same, with the valve open; Fig 11 - the same, with the valve closed ;; in fig. 12 pump blood; FIG. 13 is a block diagram of a complete prosthesis of the heart.
    FIG. 1 schematically depicts: 8: the preferred embodiment is the drive system for a prosthetic heart. Blood pumps contain the right ventricle of the RV and the left ventricle of the LV. Right ventricle K
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    The RV is formed by a rigid body 1, divided by a flexible bubble 2 or membrane into the chamber 3 of the blood pump and chamber 4 for the working fluid, and the left ventricle LV is formed by a rigid body 5 divided by the flexible bubble 6 by a membrane into the chamber 7 of the blood pump and chamber 8 for the working fluid . Valve1 | s inlets 9 and 10 and valve outlets 11 and 12 serve to connect the chambers 3 and 7 of the blood pump with the corresponding blood vessels.
    The elements of the blood pump bodies 1 and 5 are surrounded by a flexible membrane 3 forming a reservoir or a malleable bag 14. This bag faces the lung or other soft tissues of the chest cavity and contains working fluid under normal internal pressure.
    The engine 15 is connected to the drive pump 16, which through the flexible channel 17 and the pliable bag 14 is connected to the chamber 4, the last flexible channel 18 through the inlet 19 is connected to the pump drive 16. Similarly, the pump, driven 20, driven by the engine 21, is connected through the flexible channel 22 and tags 14 with a chamber 8, and the latter with a flexible channel 23 through inlet 24 is connected to a drive pump 20. Tray-receiving valves 25 and 26 are installed adjacent to inlets 19 and 24 to regulate the flow of working fluid, outgoing and outgoing chambers 4 and 8 through outputs 27 and 28 n bag 14. Pump drives 16 and 20 is a high speed rotary diagonal (semi-axial) pump driven by a brushless DC motor (any type of motor and pump can be used).
    Pump and motor bearings are fully immersed in physiological saline, which serves as the working fluid that provides them
    lubricant. The controlled discharging clamps of Q two parts, the bladder 2 (membrane), the caps 29 (Fig. 2) are made integral with the corps 1 and 5 of the ventricles. Flexible ducts 17, 18 and 22 connect the drives of the actuators 16 and 20 to the unloading valves 29 and the compliant mark 1D,
    FIG. 3 given the design with a single engine 30 and pump drive 31, which is equipped with a three-way switching valve 32 with an electromagnetic motor 33.
    FIG. 4-6, a flow sensing relief valve 34 is provided, which consists of a mushroom-shaped bladder 35 made from an elastomeric material and has at least one opening 36 in the cap 37 of the bladder 35. The cap 37 is a section of a substantially rigid metal or plastic wall. To maintain blood level 3, the working chamber 4, the prosthesis of the outlet valve at outlet 11 and the inlet (not shown). An artificial valve (for example, of the Björk-Shayly type) can serve as a valve prosthesis.
    The blister 2 of the blood pump in the preferred embodiment is single-layer and made of a high-strength bio-compatible elastomeric material. Suitable materials for this use are polyurethane-based polymers, for example, Biomer and Avkotan. Materials of this
    25 types showed high durability and reliability when pumping blood. The blood pump membrane should have poor adhesion to the thrombus and low generation of thromboembolism. The body is made of
    the maximum differential pressure of a hard metal or plastic (for example, on the cap 37 it is equipped with a stainless steel, polyurethane, pressure-equalizing valve 38, which is made in the form of openings: 39 p; flat spring attached by fiber). Usually all internal to the cap 37 along its edge. The surfaces of blood pumps have a new or biocompatible coating or of glass fiber-reinforced plastic. 7 - P is given option perceiving flow relief valve. Its description is relative to the left ventricle. On housing 5 there is a manifold 41 with a nipple 42. The cavity, manifold 41. is connected to the cavity of the actuator chamber 8 through an elongated curved channel 43 in which there is an L-shaped valve plunger 44. In the latter there is a slot 45 forming channel and flanges 46. Plunger 44 is supported in channel 43 by two flat springs 47, which at one end are attached to the inner wall of the manifold 41, and the other to the upper section 48 of the valve plunger 44, Valve
    Ny plunger 44 and flat springs 47
    Transplanted sections of tissue of a compound or plastic (for example, stainless anastomosis from the rest of the arterial steel or reinforced with a glass part and the aorta or pulmonary artery fiber or carbon fiber) are made of the corresponding metal gg. before the pumps Dp connected to them, increase the efficiency of the pump of the blood drive 20. Left and right blood pumps
    there is a mechanism for maintaining a constant pressure on the plunger A, It consists of three holes A9, made on the upper surface of the plunger 44, which are closed by the flat spring 50 gates.
    FIG. 12 is given a pump, blood containing a rigid body 1 consisting of
    measure 3 for blood, working chamber 4, prosthetic exhaust valve at outlet 11 and inlet (not shown). Any artificial valve (for example, of the Bjork-Shilo type) can serve as a prosthetic valve.
    The blister 2 of the blood pump in the preferred embodiment is single-layer and made of high-strength biocompatible elastomeric material. Suitable materials for this use are polyurethane-based polymers, for example, Biomer and Avkotan. Materials of this
    The types showed high durability and reliability when pumping blood. The blood pump membrane should have poor adhesion to the thrombus and low generation of thromboembolism. The body is made of
    hard metal or plastic (for example, stainless steel with polyurethane fiber). Usually, all internal surfaces of blood pumps have a ponovy or other # 1 biocompatible coating or from plastic, reinforced with glass fiber.
    a cover of a suitable biocompatible material. The blood pump should be able to provide a functional state of the heart in the range of 2.8 to about 9.5 liters per minute using the full blow volume and a beat frequency of 35 to 120 beats per minute.
    Parts of the housing 1 and the bubble 2 are peripherally connected by a clamping ring 51. The blood supply and discharge units are connected to respective cuffs 52 of a known type and transplanted with arterial tissue (not shown) using quick-connectors 53 in the form of a latch of any appropriate design adopted in this areas of cardiac surgery. Cuffs
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    The ventricles do not differ in construction, with the exception of the orientation of the channels in the housing for the incoming and outgoing streams necessary for proper installation and implantation.
    In the proposed full prosthesis of the heart, the described blood pumps operate from a hydraulic drive, from which it is preferable to use an incompressible fluid compatible with the elements of the drive system, for example, physiological saline solution (0.9 w / w NaCl) very close to the blood plasma in salinity. The use of saline as a working fluid contributes to the maintenance of osmotic balance and posture for displacing the blood pump membrane and pushing the blood out. A relief valve that responds to the flow of working fluid entering the drive chamber serves to shut off the drive chamber exit during each fluid pulse, as well as to empty the chamber or completely discharge the chamber.
    10 drive at the end of each pulse with
    appropriate filling of the blood pump chamber,
    During operation, fluid flows from each ventricle into a supplement bag during diastole and is taken from this meps during systole. In a preferred embodiment, the ventricles work alternately, which allows
    extremely reduce volume changes. It maintains a constant amount of hydraulic working fluid in the working fluid. This is also a system, and consequently, common problems that arise when measuring a compliant bag. It is also possible to use other working gears at the same time as pulsation. Each hydro- (for example, silicone oil) and a blunt pump starts and acts with the diffusion of such oils during the systole phase of the corresponding or body fluids into the ventricular pump and is turned off or slowed down and shifted their work in the diastole phase of this liquid, which leads to degradation of the heart.
    polymeric materials flexible membrane. The drive camera also has a lock. In FIG. 3 is a block diagram of the prosthesis of a ventricular outflowing flow that is divided into an implantable part 54 and an external 55 sHeprHjis source containing a battery 56 (EB) and a power circuit 57 (PC) which is connected by the primary winding 58 (C1) of the foot transformer, and its secondary winding 59 (C2) is connected to the controlling circuit 60 (C), Last connected to the internal battery 61 (IB) and pumps the working fluid, right 62 (RA) and left 63 (LA), which are connected to blood pumps , right 64 (RV) and left 65 (LV). The right blood pump has access to the pulmonary circulatory system 66 (P), and the left one to the large circle 67 blood circulation, adena (S),
    The device works as follows.
    The drive system contains four main elements, namely; a reservoir or malleable bag for the working fluid; means for pumping working fluid; actuator chamber and flow sensing ventricular check valve. The operation of this system is reduced to transferring the impulses of the working fluid from the reservoir of the drive to the ventricular chamber to displace the membrane of the blood pump and push the blood out. A relief valve that responds to the flow of working fluid entering the drive chamber serves to shut off the drive chamber exit during each fluid pulse, as well as to empty the chamber or completely discharge the chamber.
    drive at the end of each pulse with
    appropriate filling of the blood pump chamber,
    In the course of operation, fluid flows from each ventricle into a ductile bag IN during diastole and is taken from this mevps during systole. In a preferred embodiment, the ventricles work alternately, which allows
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    Simple valve means for discharging hydraulic fluid from the actuator chamber at the End of systole. In this case, the definition of the perceiving flow includes valves that ensure the opening and closing of the output of the actuator chamber in response to the force from the flow of the working fluid entering the actuator chamber. Such a flow control valve has a normal displacement to the open position. Therefore, the valve is closed only after the forces generated by the flow entering the drive chamber exceed its threshold value. As long as the forces generated by the working fluid flow remain above the threshold value, the valve remains closed, i.e. throughout the systole phase. When the flow of the working fluid stops or decreases below the threshold level, the valve returns to the open position with the concomitant unloading of the chamber from the working fluid, i.e. in the diastole phase.
    The hydraulic pump operates at a speed of (approximately) 7-15 thousand revolutions per minute during the phase of the pump and the pump can be stopped, but it is recommended to use a pump that can slow down to a speed in the range of about 1000 to 1200 rpm. At such a low speed, the flow created by the pump will not be sufficient to transfer the discharge valve, but at the same time
    ensure the presence of a continuous film of lubricating fluid on the bearings. The operation of an electric motor to drive hydraulic pumps is continuously controlled using reverse electromotive switching. In the operating state (Fig. 1), the drive pump 20 pumps the working fluid into the drive chamber 8 through the inlet 24. Under the action of this input stream, the valve 26 closes the outlet 28, preventing the release of the working fluid from the drive chamber 8. As the drive pump 20 operates, the volume of working fluid in the drive chamber 8 increases, as a result of which the blood pump chamber 7 is compressed and pushes blood out through outlet 12 into the large blood circulation of the drive. FIG. 4 inlets 19 and 24 for the liquid have a branch duct, the outlet 28 is closed by a valve 34, the working fluid, the valve 34, goes to the drive chamber 8 through the branch duct.
    rascheni. At the same time, a decrease in the activity of the drive pump 16 of the HZ output 27 is observed. The bubble can be pumped through the working fluid through rotating into the retracted (open) inlet 19 into the drive chamber 4. This was due to the natural elasticity of the elastomeric material and (or) through the use of a spring (not sweat, the valve 25 remains in the opening due to the natural elasticity of the elastomeric material and (or) due to the use of the spring (not later, position, providing unloading
    drive chambers with the operating fluid flow--jg cauldron).
    bones into a malleable bag 14. Exit FIG. 5 and 6, another variable fluid is shown provided by an appropriate arterial blood pressure pushing the blood through the inlet 9 into the right ventricular chamber 3 of the blood pump. Consequently, the filling of each chamber of the blood pump, as in the natural heart, is passive.
    character When starting the drive pump
    flow sensing relief valve with an expanding bladder for use in both the right and 40 in the left ventricles. The valve description is given in relation to the left ventricle. Similarly, this valve has a p-shaky mushroom-shaped bladder 35, expanding 1c with pressure to 16 and shutting down or slowing down g to exit 28 of camera 8 of the drive when filling pump 20 to drive it with working fluid supplied to the left ventricle replenishment with simultaneous compression of the right ventricle and pushing blood through exit 11 into the pulmonary system. Pumps can deisturb simultaneously, i.e. with simultaneous pulses, if there is a sufficient amount of working fluid for this. Due to the presence of two independent drive systems, sufficient flow restriction is maintained, independent control of whose fluid to pressurize the ventricles, as well as optimize the fluid in the bladder 35, works. After the qi of the engine and the pump, it works sufficiently on the cap 37. each of them, with maximization, the maximum pressure drop to overcome the drive pump 20. The displacement of the bubble into the retracted position can be accomplished by using a spring (not shown). B operating mode when applying using the pump drive 31 of the working fluid in the bubble 35, it passes into the chamber 8 of the drive through the hole 36. The latter provides
    The control of flow-controlled valves eliminates the electromechanical actuator for the valve, ultimately increasing the reliability of the complete prosthetic heart.
    FIG. 3 driven by the electromotor 33 a three-way switching valve 32 alternately ensures that the flow of the working fluid from the pump through the flexible channels 18 and 23 into the drive chamber 4 in response to the signals of the control circuit.
    If it is desired to apply pulses simultaneously, the valve 32 and the electric motor 33 can be excluded from the design. The unloading valves 25 and 26 used in such a system do not differ from those described in FIG. one.
    When filled with compressed working fluid pumped by pumps of drives 16 and 20, the bubbles 35 expand with pressing to the outlets 27 and 28 of the chamber
    drive. FIG. 4 inlets 19 and 24 for the liquid have a branch duct, the outlet 28 is closed by a valve 34, the working fluid, the valve 34, goes to the drive chamber 8 through the branch duct.
    Exit 27 is open. The bubble may return to the retracted (open)
    Exit 27 is open. The bubble may return to the retracted (open)
    This is due to the natural elasticity of the elastomeric material and / or through the use of a spring (it is not the case of a flow sensing valve with an expanding bladder for use in both the right and left ventricles. Valve description is applied to the left ventricle. Similar to that described has a p-shaky mushroom-shaped bubble 35 that expands 1c with pressure to the outlet 28 of the actuator chamber 8 when it is filled with the working fluid, supplied sufficiently restricting the flow of working fluid for pressure the fluid in the bubble 35. After the cap 37 has sufficient pressure drop to overcome the drive pump 20. The bubble can be displaced to the retracted position by using a spring (not shown). B operating mode when feeding using the drive pump 31 the working fluid in the bubble 35, it passes into the chamber 8 of the actuator through the hole 36. The latter provides
    Neither the displacement of the bubble, the bubble expands with a clamp to the outlet 28, closing it and preventing the release of working fluid from the drive chamber 8. When the flow of the working fluid entering the bubble 35 either overlaps, the pressure drop on the cap 37 decreases and the displacement force pushes the bubble to the open position, i.e. Exit 28 is opened, the working fluid passes into the flexible bag 4,
    It is also possible to use several small orifices 36, provided that the use of a well will restrict fluid flow with an accompanying rapid increase in the pressure drop on the cap 37, which expands the bubble 35. To optimize the operation of the actuator 20, a mechanism has been created to maintain an almost constant maximum pressure drop on the cap 37 By increasing the pressure of the fluid in the bubble 35, the offset value is overcome by the shifting action of the plug 40 and the flow through the valves 38 begins to flow into the chamber 8 iodine The amount of fluid flowing through the valves 38 is defined as a function of the deflection of the closures 40. The latter should open as much as is necessary to maintain a practically constant maximum pressure difference on the cap 37. The aperture 36 can have a shutter that only partially closes it.
    Figs 7-11 show another variant of the flow sensing discharging valve. Its description is given in relation to the left ventricle. A slot 45 on the inner radius and sides of the valve plunger 44 forms a channel that allows fluid to pass from the manifold 41 to the actuator chamber 8. One flange 46 of the plunger 44 is designed to close the exit 28 with a bend formed in the manifold 41 when the valve plunger is controlled by a control system that provides
    44, 7. Flat springs 47 move the valve plunger 44 upwards, i.e., to a position in which the outlet 28 remains open. When a working fluid is supplied from the pump drive 20 to the collector 4, the liquid passes into the drive chamber 8 through a narrow slot surrounding the valve puyuker 44 "After
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    the valve plunger 44 creates a sufficient pressure drop to overcome the displacement force of the flat springs 47, the valve plunger 44 shifts down and closes the outlet 28. As the flow of the working fluid entering the collector 41 decelerates or decreases, the pressure drop on the valve plunger 44 and the force of the springs 47 pushes the valve plunger 44 back to the open position, i.e. the outlet 28 opens, skipping the working fluid into the bag 14.
    The apertures 49 are closed by flat spring valves 50, which are bent downward, passing fluid into the actuator chamber 8 if the pressure of the working fluid in the collector 41 exceeds a certain predetermined value. The greater the pressure in the manifold 41, the greater the deviation of the valves 50, which ensures the maintenance of a practically constant maximum differential
    5 pressure on the valve plunger 44. The design of the valve described can ensure that it closes when the pressure on the plunger decreases in accordance with the minimum speeds
    0 flow in the range of about 3-7 l / min. Typically, the full closure time of such a valve should be about 10 to 50 ms. Valve opening time is determined by how fast
    By pushing the plunger through, the volume of fluid can flow in the opposite direction through the slit into the actuator chamber. In the phase of closing the valve, the fluid fills the ventricular drive chamber, and in the phase of its opening it is provided that the reverse flow of fluid into the pump is prevented. Typically, the duration of the opening phase (to the fully open position) for such a valve design is about 20 to 80 ms.
    The advantage of the proposed complete heart prosthesis is the ability of its interaction with the electronic system.
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    functioning in accordance with the actions i ") of the natural heart of man. In fact, the only means by which the gg pump perceives the blood of the physiological needs of the recipient of the implant is the modified Frank-S garlic mechanism. Each pump of blood pushes the entire volume of blood filling it.
    therefore, the relationship of arterial hypertension to the functional state of the heart is similar to the Frank-Stirling relationship for a normal heart. According to this mechanism, the functional state of the heart is equal to the venous return flow. Since the functional state of the heart is equal to the frequency of the beat multiplied by the stroke volume of the heart, its change is achieved by changing the frequency of the heart beat or stroke volume. According to the invention, it is recommended that the magnitude of the stroke volume be kept constant, and changes in the functional state of the heart be realized by changing the frequency of the heartbeat. Maintaining a constant impact volume can be provided by an internal means, i.e. a volume-limiting membrane, or an external means of controlling the deviation of the membrane, which is known.
    In the embodiment shown in FIG. I variant of the means to control the frequency of the heartbeat is performed by supplying adjustable, intermittent pulses of working fluid to the actuator chamber in response to a control signal from the control circuit C (Fig. 13) to each pump motor for pumping working fluid. With such a control signal, the pumps are started or stopped (or they turn or decrease the speed of rotation), ensuring the closing and opening of the ventricular relief valves at the beginning and at the end of the systole phase. Such a control signal can be generated in response to any of the known measured variables that provide information that can be used to drive a blood pump in accordance with physiological requirements. One of these variables is blood pressure, measured by a known method using pressure sensors.
    In the embodiment shown in FIG. In the third embodiment, the variable pulsation control is performed by applying a control signal to the switching valve driven from the engine, which determines the direction and duration of each fluid pulse.
    In the preferred embodiment, the complete heart prosthesis of the heart functions TaKifM in such a way that the ventricular ejections are carried out alternately, which reduces the number of working fluids. However, as mentioned, simultaneous pulsation can lead to an increase in throughput of the hydraulic reservoir. One of the advantages of the preferred option of an artificial heart prosthesis is the ability to optimally control each ventricle separately by using separate drive mechanisms.
    The energy for powering the electrical and electronic control system is provided by electromagnetic induction through the patient's intact skin. In the same way, telemetry signals are transmitted in the opposite direction for the display system and patient status information. Power supply and telemetry systems of this type are known and contain mainly a high-frequency communication transformer, including a small flat internal coil. Implanted under the skin, and a flat outer coil of large size, mounted on top of the implanted coil. Outside the catupt can be kept in a vest pocket, in a belt or in another piece of toilet. In use, this energy transfer system allows for significant mobility of the outer coil relative to the inner coil, without negatively affecting the transfer of energy or information to or from CHCTENry. The power for supplying the outer coil can be obtained from an electronics unit containing, for example, batteries, an electronic battery charging circuit, or other electronic circuits for controlling the system and patient functions. Signaling devices (of visual or audible type) are included in the control electronic circuit to warn of failures or the occurrence of any interference.
    The design of the outdoor battery pack can provide patient mobility for several hours. When such a unit is exhausted, it can be replaced with a fully charged one or recharged from an AC network when the patient is plugged into a wall outlet or from a car DC battery en route.
    the patient has another battery pack.
    The internal implanted unit is also a temporary energy source completely independent of the external energy supply. This gives the patient freedom of action, for example, when bathing, etc. and sufficient time to replace I external energy sources, i.e. re-dressing or replacing the battery pack. Such an internal battery should be placed close to the skin.
    invention formula
    权利要求:
    Claims (3)
    [1]
    1. A prosthetic heart with a hydraulic drive, containing a pump for a blood drive, a reservoir for
    in and
    the working fluid, the means for pumping, the working fluid from the reservoir to the blood pump, on the blood pump has two chambers with an inlet and a blood outlet for each chamber, on which valve prostheses are installed to allow blood to flow in one direction, and the drive system It has two chambers with an inlet and an outlet for a working fluid for each chamber.
    in this case, each blood chamber is connected to an external valve controlled by the flow of the working fluid with a corresponding chamber.
    yes common to both chambers membrane 4, Device according to claims. 1-3, of the biologically compatible elastomeric, in that the barrier material, a distinctive element of the controllable reverse u and, in order to simplify the valve, is designed as a shell.
    Neither design, weight reduction, or increased reliability, the output of the actuator chamber is provided with a shut-off element and forms with it a flow-controlled return flow valve.
    2. A blood pump containing a blood chamber with an inlet and an outlet for blood on which valve prostheses are fitted to allow passage of
    [2]
    five
    blood in one direction, a reservoir for the working fluid, a drive system with a drive chamber with an inlet and an outlet for the working fluid, the blood chamber connected to the drive chamber and provided with a common for both chambers, a membrane of biologically compatible elastomeric material and means for pumping working fluid from the reservoir into the actuator chamber, characterized in that, in order to simplify the design, reduce weight and increase reliability, the output of the actuator chamber is provided with a shut-off element and forms with it a flow controlled working whose fluid check valve.
    3. An implantable drive system comprising a drive chamber with an inlet and an outlet for the working fluid, a reservoir for the working fluid and means for pumping the working fluid from the reservoir to the drive chamber 5, which, in order to simplify the design, reduce the weight and increase reliability, the output of the actuator chamber is equipped with a locking element and forms with it
    [3]
    0
    which is hydraulically connected to the means for pumping the working fluid, -.
    5. The device according to claim 4, characterized by the fact that the shut-off element of the controlled check valve in the working part has at least one hole and a spring-loaded gate with a predetermined force to work.
    29
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    for inventions and discoveries 113035, Moscow, Zh-35, Raushsk nab., 4/5
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    同族专利:
    公开号 | 公开日
    JPS58500793A|1983-05-19|
    WO1982003980A1|1982-11-25|
    EP0079373A1|1983-05-25|
    DE3274794D1|1987-02-05|
    EP0079373B1|1986-12-30|
    EP0079373A4|1984-07-05|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US3541612A|1968-07-11|1970-11-24|Homer C Carney|Fluid actuated and regulated artificial implantable heart system|
    US3568214A|1968-07-24|1971-03-09|Univ Utah|Artificial heart system and method of pumping blood by electromagnetically pulsed fluid|
    US3550162A|1969-02-06|1970-12-29|Thermo Electron Corp|Blood pump control system|
    US3783453A|1971-12-23|1974-01-08|V Bolie|Self-regulating artificial heart|
    US3919722A|1973-03-06|1975-11-18|Us Health|Totally implantable artificial replacement heart|
    US4173796A|1977-12-09|1979-11-13|University Of Utah|Total artificial hearts and cardiac assist devices powered and controlled by reversible electrohydraulic energy converters|
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    EP3634528A4|2017-06-07|2021-03-10|Shifamed Holdings, LLC|Intravascular fluid movement devices, systems, and methods of use|
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    US06/265,100|US4369530A|1981-05-19|1981-05-19|Hydraulically actuated cardiac prosthesis and method of actuation|
    US06/265,199|US4376312A|1981-05-19|1981-05-19|Hydraulically actuated cardiac prosthesis|
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