US3885251A - Artificial heart pump or assist - Google Patents

Artificial heart pump or assist Download PDF

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Publication number
US3885251A
US3885251A US338093A US33809373A US3885251A US 3885251 A US3885251 A US 3885251A US 338093 A US338093 A US 338093A US 33809373 A US33809373 A US 33809373A US 3885251 A US3885251 A US 3885251A
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United States
Prior art keywords
tube
sleeves
diameter
pump
sleeve
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US338093A
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English (en)
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Raul Ismael Pedroso
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Philips North America LLC
US Philips Corp
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US Philips Corp
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Priority to US338093A priority Critical patent/US3885251A/en
Priority to NL7402782A priority patent/NL7402782A/xx
Priority to BE141629A priority patent/BE811852A/xx
Priority to CA194,061A priority patent/CA1017904A/en
Priority to FR7407385A priority patent/FR2220279B1/fr
Priority to DE2410418A priority patent/DE2410418A1/de
Priority to CH309074A priority patent/CH571866A5/xx
Priority to JP49025633A priority patent/JPS5026397A/ja
Application granted granted Critical
Publication of US3885251A publication Critical patent/US3885251A/en
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    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/08—Machines, pumps, or pumping installations having flexible working members having tubular flexible members
    • F04B43/10—Pumps having fluid drive
    • F04B43/113—Pumps having fluid drive the actuating fluid being controlled by at least one valve
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • 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
    • A61M60/161—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 mechanically acting upon the outside of the patient's blood vessel structure, e.g. compressive structures placed around a vessel
    • 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
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • 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
    • A61M60/20—Type thereof
    • A61M60/289—Devices for mechanical circulatory actuation assisting the residual heart function by means mechanically acting upon the patient's native heart or blood vessel structure, e.g. direct cardiac compression [DCC] devices
    • 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
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/857—Implantable blood tubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/892—Active valves, i.e. actuated by an external force
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F02—COMBUSTION ENGINES; HOT-GAS OR COMBUSTION-PRODUCT ENGINE PLANTS
    • F02G—HOT GAS OR COMBUSTION-PRODUCT POSITIVE-DISPLACEMENT ENGINE PLANTS; USE OF WASTE HEAT OF COMBUSTION ENGINES; NOT OTHERWISE PROVIDED FOR
    • F02G1/00—Hot gas positive-displacement engine plants
    • F02G1/04—Hot gas positive-displacement engine plants of closed-cycle type
    • F02G1/043—Hot gas positive-displacement engine plants of closed-cycle type the engine being operated by expansion and contraction of a mass of working gas which is heated and cooled in one of a plurality of constantly communicating expansible chambers, e.g. Stirling cycle type engines
    • 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
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A61M60/279—Peristaltic pumps, e.g. roller pumps
    • A61M60/284—Linear peristaltic pumps
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F02—COMBUSTION ENGINES; HOT-GAS OR COMBUSTION-PRODUCT ENGINE PLANTS
    • F02G—HOT GAS OR COMBUSTION-PRODUCT POSITIVE-DISPLACEMENT ENGINE PLANTS; USE OF WASTE HEAT OF COMBUSTION ENGINES; NOT OTHERWISE PROVIDED FOR
    • F02G2280/00—Output delivery
    • F02G2280/005—Medical applications, e.g. for prosthesis or artificial hearts

Definitions

  • a further problem area in typical heart assist devices utilizing valves is that some constituents of the blood may be damaged due to excessive pressure, velocity and shear forces occurring when a valve is being closed and the pressure drop through the reduced-size flow passage is substantially increased over normal values.
  • the new invention is a mechanism for use in a human or animal body to improve blood flow, the mechanism having structure and geometry which avoids or at least reduces significantly the above-mentioned problems.
  • the new device in communication with the high and low pressure variations occurring, in its preferred embodiment, in a pressure source such as an implantable Stirling or Rankin engine, using the gas working space, or oil pump, or the high and low pressure variations of a compressor driven by the engine.
  • the new device includes a tubular section that is joined to and between the severed ends of an artery, such that the blood will have a continuous and substantially uninterrupted flow path through the artery and the tube-section. At least two and preferably three sleeves axially spaced apart but adjacent, encircle this section.
  • Each sleeve has its diameter cyclically contracted and enlarged about the tube, such that the bore or flow passage through the tube is cyclically (a) constricted to reduce or stop blood flow and then (b) enlarged to permit normal flow therethrough.
  • the first sleeve (which would be designated as in the upstream position) is constricted; this is followed by the second sleeve being constricted while the first remains constricted, and then the third is constricted while the first and second remain constricted.
  • One possible sleeve configuration comprises a tubular member formed into a ring that has one end sealed and the other end connected to a source of fluid that is supplied either at a low or a high relative pressure.
  • the ring has a normal diameter, and application of the high pressure causes the ring to uncoil and enlarge its diameter; the rings resilience will return it to its normal diameter when pressure is reduced or discontinued.
  • the sleeves (rings) could be designed to contract or reduce in diametral dimension upon the application of high fluid pressure, with their resilience returning them to a normal enlarged diameter.
  • a valve or timing mechanism situated between the source of fluid and the sleeves, will control the selection of sleeves to be pressurized to alter the diameter of each relative to the others. Since these sleeves contact and operate on the outer surface of the tube, they are entirely external of the actual blood flow, which overcomes numerous disadvantages in prior art devices, as discussed below.
  • Another variation of the above invention would be to leave the artery unsevered, to omit the tube section, and position the sleeves directly upon the outer surface of the artery.
  • the pump mechanism of this invention has a variety of significant advantages over prior art pumps and heart assists.
  • this stagnation problem has been significant, and to avoid it is a considerable benefit and achievement.
  • Second, the pump mechanism is extremely uncomplicated and inexpensive, in comprising simple sleeves which change dimension but otherwise do not move and do not have to mate with other parts, and do not have close tolerances, and do not have seals, bearings, and. other parts which can wear out.
  • the sleeves will merely expand and constrict, and there are numerous materials available including metals, plastics and rubber which have proven ability to flex thousands or millions of cycles without deteriorating excessively or losing their necessary characteristics. Also, the sleeves would be secured together in some manner to maintain their axial spacing, such that the constriction of one sleeve effecting the blood flow therein would not be remote and unrelated to the application of pressure upon blood in the adjacent sections of the artery.
  • the number of sleeves can be increased to provide a smoother flow of the blood, however a minimum number of two sleeves is required, and presumably three would function reasonably well.
  • An implantable Stirling engine has a gas working space and also a lubricating oil pump that experience such appropriate high and low pressure differentials; this gas space or the oil pump can be connected directly to the sleeves through a valve which automatically selects the suitable pressure level for each sleeve.
  • a Stirling or other implantable power source can drive a compressor whose high and low pressure ducts are fed to the sleeves via a valve.
  • Stirling engines can operate over a long, extended period of time, by using an isotope heat source, and can run maintenance-and-adjustment-free.
  • the sleeves could be timed to operate at the same rate as the compressor and/or the engine, or could cycle at a multiple or fraction of the valve speed.
  • FIG. 1 is a schematic diagram of heart assist system including an artery pump and a Stirling engine providing high and low working gas pressure.
  • FIG. 2 is schematic diagram of another embodiment of a system similar to FIG. 1, wherein a Stirling engine drives a compressor which provides the high and low pressures.
  • FIG. 3 is a schematic diagram of another embodiment similar to FIGS. 1 and 2, with the oil pump in the crankcase providing high and low pressures.
  • FIG. 4 is a partial elevation view of the pump of the new invention.
  • FIG. 5 is a sectional view taken along line 55 of FIG. 4.
  • FIG. 6 is a sectional view taken along line 66 of FIG. 4.
  • FIG. 7 is a schematic view showing the pumping and suction cycles of the device of FIG. 4.
  • FIG. 8 is a pressure vs time diagram showing six periods for a complete (FIG. 7) cycle of the FIG. 4 embodiment.
  • FIG. 9 is a partial elevation view in section of a second embodiment of the invention with a center core.
  • FIG. 10 is a sectional view of another embodiment similar to FIG. 9.
  • FIG. 11 is an end view taken along line 1I11 in FIG. 10.
  • FIG. 12 is a sectional view taken along line 12-12 in FIG. 10.
  • FIG. 13 is a diagrammatic view of a rotary control valve to selectively provide high and low pressure to the three sleeves in selective sequence of the device in FIGS. 4, 9 and 10.
  • FIG. 1 where a Stirling engine 1 has a working or compression space that experiences high and low pressures available at ports 2 and 3 respectively, which are connected via ducts and corresponding high and low pressure buffer tanks h and h; to a valve 4; one embodiment of this valve is shown in detail in FIG. 13.
  • the valve selectively feeds high and low pressure to sleeves 5, 6, and 7 which encircle tube 8 connected between the severed ends 9 and 9' of an artery as a continuous blood flow duct, the valve being controlled by a connection 4 with engine.
  • the sleeves and tube 8 together form the pump component 10 which pumps blood in the direction of the arrows.
  • the operation of the pump and valve components will be described in detail below, while the operation of a Stirling engine is known and described in numerous publications such as US. Pat. Nos. 3,443,079, 2,885,855, 3,318,089 and 3,318,100.
  • FIG. 2 shows schematically a variation from FIG. 1 with similar components given the same reference numerals but modified, for example, from 1 to la.
  • a Stirling engine 1a has a mechanical or hydraulic power output 1b that drives compressor 1c which has a low pressure connection 3a feeding a buffer tank 3b to valve 4a, and a high pressure connection 2a which also feeds valve 4a via a buffer tank 1d for storing high pressure working fluid.
  • the valve 4a automatically feeds the appropriate high and low pressure fluid to sleeves 5a, 6a and 7a about tube 8a of pump 10a.
  • FIG. 3 shows a third variation wherein the heart assist system comprises the lubricating oil pump la in the crankcase 1f of Stirling engine lg.
  • High pressure oil is fed to a high pressure buffer tank 3c and then to the control valve 4b for sleeves 5b, 6b. and 7b.
  • a spring bellows expander may be situated inside of the buffer tank (see FIG. 3a) will help maintain a generally constant tank pressure when valve 4a opens and draws vfluid from the tank.
  • the spring-loaded or gas-pressure biased bellows in the tank would maintain an oil supply pressure substantially constant.
  • a radioactive isotope capsule is suggested to supply heat for long-term operation of the engine.
  • FIG. 4- The pump 10 of FIG. 1 is shown in FIG. 4- where a section of tubing is surrounded by three sleeves l1, l2 and 13. The direction of flow is from left to right as indicated by arrow 14, and the tube has a nominal undisturbed diameter d as compared to a constricted diameter d resulting from reducing the diameter of the sleeves.
  • FIG. 5 shows the tube 10c and sleeve 11 in an expanded state
  • FIG. 6 shows the tube and sleeve 13 or 12 in a contracted state.
  • Each sleeve is normally constricted as in FIG. 6 and is expanded when a fluid pressure is applied to the internal chamber of the hollow sleeve causing it to expand as indicated in FIG. 5.
  • stage 1 of FIG. 7 the first sleeve is expanded while the second and third sleeves are constricted; this corresponds to the chart of FIG. 8 which shows sleeve 1 at high pressure, namelythat it is expanded and blood can fill the space it encloses, in contrast to sleeves 2 and 3 which are indicated to be energized with low fluid pressure or that they are constricted resulting in greater resistance to the blood flow.
  • Stage 2 of FIG. 7 shows that the first two sleeves are expanded while the third remains constricted;
  • FIG. 8 in stage 2 corresponds by showing sleeves l and 2 energized with high fluid pressure while sleeve 3 is still at low pressure.
  • FIG. 6 shows all three sections to be expanded such that all three sleeves are being energized with high pressure fluid, and this corresponds to FIG. 8 stage 3 where all three sleeves are indicated to be at high pressure.
  • Stage 4 in FIG. 7 shows the first section to be constricted by corresponding action of sleeve 1;
  • FIG. 8 shows the corresponding diagram whereby only sleeve 1 is constricted, whereas sleeves 2 and 3 remain expanded, that is, subjected to high energizing fluid pressure.
  • Stage 5 shows that the first sleeve has remained constricted and the second is constricted thus forcing net flow in the direction of the arrow to the right out through section 3.
  • stage 6 shows all sleeves to be constricted thus forcing the net flow from section 3 further outward, while the first two closed sections prevent to some extent the fluid from moving backward.
  • stage 1 we return to stage 1 where section 1 is opened while sections 2 and 3 remain closed. This permits fluid to enter section 1 while it substantially prevents fluid from flowing backwards into sections 2 and 3.
  • section 2 is opened which allows more net fluid flow to move to the right into the pump and in fact draws the fluid in because resilience of the section causes it to open creating a partial vacuum therein.
  • all three sections are opened 'in stage 3. Again in stage 4 the first section is closed which forces net fluid flow toward the right in the direction of the arrows in FIG. 7.
  • FIGS. 7 and 8 demonstrate a pumping action comprising a suction or priming cycle in stages 1, 2 and 3, and a pumping forcing cycle in stages 4, 5, and 6. It would be possible to use only two sleeves but the efficiency of the pump would be considerably reduced.
  • FIG. 9 shows another embodiment of the invention which is similar to but modified from that in FIG. 4.
  • the pumping device is in a housing 16 with a section of tubing 17 axially disposed in a housing.
  • the entire pumping device is to be attached to the severed ends l8, 19 of an artery along junction lines 18 and 19'.
  • the three sleeves for producing the pumping action are shown as 20, 21 and 22 with each being connected to a fluid port 20, 21' and 22' which feeds energizing fluid under pressure to the sleeves for expanding same according to the method earlier described.
  • FIG. 9 is center core 23 which is fixedly positioned in the center or thereabouts of the tube section 17;
  • FIG. 11 shows streamlined webs 29 at the entrance and exit of the tube for supporting the core element.
  • Sleeve 20 as shown constricts the flexible tube 17, until it closes substantially or completely about core 23; subsequent closing of sleeve 21 would force fluid flow in the direction to the right, past sleeve 22.
  • the presence of the core allows the constricted tube to nearly completely close off flow in contrast to the prior embodiment where there is no core and the constriction of the first sleeve would only tend to restrict flow, but obviously there would be considerable leakage backward because the passage within the tube remains open.
  • this pump device of FIG. 9 would be embedded as a unit within the body while the two ends thereof are attached to the severed artery at 19 and 18, and the fluid ports 20', 21' and 22' would be attached to pressurized fluid means to be discussed later.
  • FIG. 10 shows a more detailed view of an embodiment similar to that of FIG. 9.
  • the sleeves 24, 25 and 26 are indicated as coil sections of hollow tubing each connected to a port through which pressurized fluid is directed. It is necessary to support the center core 27 centrally of tubing 28, and this is done by webs 29 shown in FIG. 11 which is a right end view of FIG. 10.
  • the webs are thin and streamlined and represent minimum obstruction to the flow of blood in the annular space 29 about the center core and within tube section 28.
  • FIG. 12 includes a sectional view of the port 30 for energizing a sleeve 24.
  • the inner rotor permits communication of high pressure inlet P with outlet P and low pressure inlet P with outlets P and P
  • the exit ports are positioned around the housing of the valve such that rotation of the rotor exposes appropriate exit ports at the correct timing to provide a cyclic pressure variation for'the three sleeves, or any number that is chosen, according to FIGS. 7 and 8.
  • each sleeve is resilient member which tends to hold its constricted shape at low energizing pressure.
  • the opening of- 'the first and second sections of the tube while the third section remains closed acts as a suction or priming" phase of the device.
  • the sleeve creates a greater volume and a partial vacuum such that blood will flow into these open sections mainly in the pumping direction; and during later phases of the cycle the blood will be pumped out mainly in the same direction.
  • valve shown in FIG. 13 can be designed to control the flow to as many sleeves as desired, except that the diameter .of the valve would increase as the number of flow connections increased. In general, if the pump has N number of sleeves, then it would have to have N7number of flow outlets, and the angle 6 in the valve according to FIG. 13 would be 1r/N radians. When one or more sleeves constrict the central tube, wrinkles in the constricted portion can be avoided by axially fixing the opposite ends of the tube", then the constricted part of the tube is also stretched lengthwise, and Jwill not experience compression on bending.
  • An implantable heart pump for pumping and controlling the flow of blood through an artery which is severable to expose two adjacent ends to accommodate the pump therebetween, this pump being operable with first and second sources of high and low pressure fluid respectively, the pump comprising a tube securable between said severed ends of said artery to form a continuous blood flow passage, at least two sleeves each having a generally cylindrical bore at least partially surrounding and contacting said tube, the sleeves being axially spaced apart but adjacent to each other, a core element formed as a rod fixedly positioned generally centrally within the bore of said tube and adjacent the inner surface thereof, the tube having a bore diameter that is variable between large and small, each sleeve being responsive to a pressure change whereby its diameter is variable between large and small corresponding to said tube bore diameters, and valve means for communicating selectively said high and low pressure sources to said sleeves, whereby each sleeve periodically has a. a small diameter for constricting the tube to have a small bore diameter at the area of the tube adjacent said sleeve
  • the apparatus further comprising an implantable Stirling engine including a heat source for operating the engine, the engine having a working space wherein working gas experiences a cyclic pressure variation between high and low, the apparatus further comprising duct means communicating said high and low pressure gas to said valve means.
  • An implantable heart pump for pumping and controlling the flow of blood through an artery which is severable to expose two adjacent ends to accomodate the pump therebetween, this pump being operable with first and second sources of high and low pressure fluid respectively, the pump comprising a tube securable between said severed ends of said artery to form a continuous blood flow passage, at least two sleeves each at least partially surrounding said tube, the sleeves being axiallysp'aced apart but adjacent to each other, the tube having a bore diameter that is variable between large and small, each sleeve being responsive to a pressure change whereby its diameter is variable between large and small corresponding to said tube bore diameters, valve means for communicating"selectively said high and low pressure sources to said sleeves, whereby each sleeve periodically has a small diameter for constricting the tube to have a small bore diameter adjacent said sleeve, and a large diameter permitting a corresponding large bore diameter of said tube, the valve providing a predetermined sequence of constrictions and expansions of the sleeves and therefore of
  • An implantable heart pump for pumping and controlling the flow of blood through an artery which is severable to expose two adjacent ends to accommodate the pump therebetween, this pump being operable with first and second sources of high and low pressure fluid respectively, the pump comprising an implantable Stirling engine including a heat source for operating the engine and a mechanical power output of the engine a compressor driven by said power output, the compressor having a high pressure output port and a low pressure inlet port which constitute said high and low pressure sources of fluid, duct means communicating said ports to a valve means, and corresponding high and low pressure buffer chambers respectively intermediate said valve and said ports, a tube securable between said severed ends of said artery to form a continuous blood flow passage, at least two sleeves each at least partially surrounding said tube, the sleeves being axially spaced apart but adjacent to each other, the tube having a bore diameter that is variable between large and small, each sleeve being responsive to a pressure change whereby its diameter is variable between large and small corresponding to
  • a small diameter for constricting the tube to have a small bore diameter adjacent said sleeve, and b. a large diameter permitting a corresponding large bore diameter of said tube, the valve providing a predetermined sequence of constrictions and expansions of the sleeves and therefor of the tube to produce a pumping action in one direction on the blood flow therein.
  • An implantable heart pump for pumping and controlling the flow of blood through an artery which is severable to expose two adjacent ends to accommodate the pump therebetween, this pump being operable with first and second sources of high and low pressure fluid respectively, the pump comprising a tube securable between said severed ends of said artery to form a continuous blood flow passage, at least two sleeves each at least partially surrounding said tube, the sleeves being axially spaced apart but adjacent to each other, the tube having a bore diameter that is variable between large and small, each sleeve being responsive to a presthat is expandable to a large diameter when high pressure fluid is communicated to said inlet-outlet port, each ring having resilience to return to its normal small diameter when.
  • each sleeve periodically has a small diameterfor constricting the tube to have a small bore diameter'adjacent said sleeve, and a large diameter permittingga corresponding large bore diameter of said tube, the valve providing a predetermined sequence of constrictions and expansions of the sleeves and therefor of the tube to produce a pumping action in one direction on the blood flow therein.
  • An implantable heart pump for pumping and controlling the flow of blood through an artery which is severable to expose two adjacent ends to accommodate the pump therebetween, this pump being operable with first and second sources of high and low pressure fluid respectively, the pump comprising a tube securable between said severed ends of said artery to form a continuous blood flow passage, a core element formed as a rod fixedly positioned generally centrally within the bore of said tube and adjacent the inner surface thereof, at least two sleeves each at least partially surrounding said tube, the sleeves being axially spaced apart but adjacent to each other, the tube having a bore diameter that is variable between large and small, each sleeve being responsive to a pressure change whereby its diameter is variable between large and small corresponding to said tube bore diameter, valve means for communicating selectively said high and low pressure sources to said sleeves, the pump further comprising an implantable Stirling engine including a heat source for operating the engine, the engine having a working space wherein working gas experiences a cyclic pressure variation between high and low, the apparatus further comprising duct means communicating
  • the valve providing a predetermined sequence of constrictions and expansions of the sleeves and therefor of the tube to produce a pumping action in one direction on the blood flow therein.
  • a heart pump for attachment between the severed ends of a severed artery comprising an implantable Stirling engine including a fluid therein that is cyclically under high and low pressure, a tube securable between said severed ends to form a continuous blood flow path, three sleeves axially spaced and having generally cylindrical bores positioned about and in contact with said tube, a core element formed as a rod fixedly positioned generally centrally within the bore of said tube and adjacent the inner surface thereof, valve means for cyclically and sequentially communicating said high and low pressure fluid to said sleeves, a buffer tank between said valve and each of said high and low pressure sources, means interconnecting said engine and said valve for cyclically controlling said valve according to the operation cycle of the engine, said sleeves designated first, second and third moving downstream of the flow, each having its diameter reduced when said high pressure is communicated thereto and expanded when said low pressure is communicated thereto and the tube in the areas surrounded by the sleeves having corresponding diameter constrictions and expansions with the tubes inner surface at each of said areas being urged closely against said core
  • each sleeve being responsive to a pressure change whereby its diameter is variable between large and small corresponding to said tube bore diameters, and valve means for communicating selectively said high and low pressure sources to said sleeves, whereby each sleeve periodically has a.
  • a small diameter for constricting the tube to have a small bore diameter at the area of the tube adjacent said sleeve with the tubes s inner surface at the area being urged closely against said core to prevent blood flow in that area, and b. a large diameter permitting a corresponding large bore diameter of said tube, and thereby permitting blood flow, the valve providing a predetermined sequence of constrictions and expansions of the sleeves and therefor of the tube to produce a pumping action in one direction on the blood flow therein.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Mechanical Engineering (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Anesthesiology (AREA)
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US338093A 1973-03-05 1973-03-05 Artificial heart pump or assist Expired - Lifetime US3885251A (en)

Priority Applications (8)

Application Number Priority Date Filing Date Title
US338093A US3885251A (en) 1973-03-05 1973-03-05 Artificial heart pump or assist
NL7402782A NL7402782A (de) 1973-03-05 1974-03-01
BE141629A BE811852A (fr) 1973-03-05 1974-03-04 Pompe cardiaque
FR7407385A FR2220279B1 (de) 1973-03-05 1974-03-05
CA194,061A CA1017904A (en) 1973-03-05 1974-03-05 Artificial heart pump or assist
DE2410418A DE2410418A1 (de) 1973-03-05 1974-03-05 Kunstherzpumpe
CH309074A CH571866A5 (de) 1973-03-05 1974-03-05
JP49025633A JPS5026397A (de) 1973-03-05 1974-03-05

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US338093A US3885251A (en) 1973-03-05 1973-03-05 Artificial heart pump or assist

Publications (1)

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US3885251A true US3885251A (en) 1975-05-27

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ID=23323382

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US338093A Expired - Lifetime US3885251A (en) 1973-03-05 1973-03-05 Artificial heart pump or assist

Country Status (8)

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US (1) US3885251A (de)
JP (1) JPS5026397A (de)
BE (1) BE811852A (de)
CA (1) CA1017904A (de)
CH (1) CH571866A5 (de)
DE (1) DE2410418A1 (de)
FR (1) FR2220279B1 (de)
NL (1) NL7402782A (de)

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4015590A (en) * 1976-04-12 1977-04-05 Baylor College Of Medicine Balloon activated blood pump
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
US4809676A (en) * 1987-12-28 1989-03-07 Freeman Maynard L Heart assist device and method of implanting it
US4838889A (en) * 1981-09-01 1989-06-13 University Of Utah Research Foundation Ventricular assist device and method of manufacture
US5006111A (en) * 1985-04-05 1991-04-09 Kureha Kagaku Kogyo Kabushiki Kaisha Medical pump device and a method for compensating a deviation of a measured blood flow rate
US5139517A (en) * 1989-11-08 1992-08-18 Corral David F Orthotopic intraventricular heart pump
US5222980A (en) * 1991-09-27 1993-06-29 Medtronic, Inc. Implantable heart-assist device
US5269811A (en) * 1989-11-30 1993-12-14 National Research Council Of Canada Primary fluid actuated, secondary fluid propelling system
AU648984B2 (en) * 1989-06-20 1994-05-12 British Technology Group Limited Improving blood flow
US6200260B1 (en) 1997-10-09 2001-03-13 Fore Flow Corporation Implantable heart assist system
US6387037B1 (en) 1997-10-09 2002-05-14 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6390969B1 (en) 1997-10-09 2002-05-21 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6406422B1 (en) 2000-03-02 2002-06-18 Levram Medical Devices, Ltd. Ventricular-assist method and apparatus
US20030069468A1 (en) * 1997-10-09 2003-04-10 Bolling Steven F. Implantable heart assist system and method of applying same
US6610004B2 (en) 1997-10-09 2003-08-26 Orqis Medical Corporation Implantable heart assist system and method of applying same
US20050085683A1 (en) * 2003-10-15 2005-04-21 Bolling Steven F. Implantable heart assist system and method of applying same
US20050131385A1 (en) * 2003-12-12 2005-06-16 Bolling Steven F. Cannulae for selectively enhancing blood flow
US20050277870A1 (en) * 2004-06-10 2005-12-15 Robert Pecor Cannula having reduced flow resistance
US20050277803A1 (en) * 2004-06-10 2005-12-15 Robert Pecor Cannulae having reduced flow resistance
WO2006037519A1 (de) * 2004-10-01 2006-04-13 Universitätsklinikum Freiburg Peristaltische pumpe
US20060184199A1 (en) * 2005-02-14 2006-08-17 O'leary Shawn Apparatus and methods for reducing bleeding from a cannulation site
US20060224110A1 (en) * 2005-03-17 2006-10-05 Scott Michael J Methods for minimally invasive vascular access
US20080234536A1 (en) * 2007-03-21 2008-09-25 Yossi Gross Implantable peristaltic pump to treat erectile dysfunction
US20090198097A1 (en) * 2008-01-31 2009-08-06 Ed Tech Medical Ltd. Peristaltic pump for treatment of erectile dysfunction
US20100145299A1 (en) * 2006-05-30 2010-06-10 Yossi Gross Implantable Pump for Drug Delivery to Treat Erectile Dysfunction

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
IT1131170B (it) * 1980-05-12 1986-06-18 Consiglio Nazionale Ricerche Pompa cardiaca per la circolazione extracorporea del sangue con rallentamento del flusso sanguigno durante la circolazione extracorporea
US4957504A (en) * 1988-12-02 1990-09-18 Chardack William M Implantable blood pump
US5429584A (en) * 1990-11-09 1995-07-04 Mcgill University Cardiac assist method and apparatus

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2455859A (en) * 1946-05-13 1948-12-07 Frederic E B Foley Artificial sphincter and method
US3429266A (en) * 1967-04-27 1969-02-25 Charles B Jones Jr Peristaltic pumping system
US3597766A (en) * 1968-07-11 1971-08-10 Atomic Energy Commission Artificial heart pumping system powered by a modified stirling cycle engine-compressor having a freely reciprocable displacer piston
US3720485A (en) * 1971-07-01 1973-03-13 N Holman Artificial heart
US3744063A (en) * 1971-10-12 1973-07-10 Kendall & Co Artifical sphincter for controlling urinary incontinence

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3305097A (en) * 1963-05-27 1967-02-21 Scientific Industries High pressure peristaltic pump for separation apparatus
US3478695A (en) * 1968-02-13 1969-11-18 Mc Donnell Douglas Corp Pulsatile heart pump

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2455859A (en) * 1946-05-13 1948-12-07 Frederic E B Foley Artificial sphincter and method
US3429266A (en) * 1967-04-27 1969-02-25 Charles B Jones Jr Peristaltic pumping system
US3597766A (en) * 1968-07-11 1971-08-10 Atomic Energy Commission Artificial heart pumping system powered by a modified stirling cycle engine-compressor having a freely reciprocable displacer piston
US3720485A (en) * 1971-07-01 1973-03-13 N Holman Artificial heart
US3744063A (en) * 1971-10-12 1973-07-10 Kendall & Co Artifical sphincter for controlling urinary incontinence

Cited By (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4015590A (en) * 1976-04-12 1977-04-05 Baylor College Of Medicine Balloon activated blood pump
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
US5006111A (en) * 1985-04-05 1991-04-09 Kureha Kagaku Kogyo Kabushiki Kaisha Medical pump device and a method for compensating a deviation of a measured blood flow rate
US4809676A (en) * 1987-12-28 1989-03-07 Freeman Maynard L Heart assist device and method of implanting it
AU648984B2 (en) * 1989-06-20 1994-05-12 British Technology Group Limited Improving blood flow
US5372573A (en) * 1989-06-20 1994-12-13 British Technology Group Limited Blood flow
US5139517A (en) * 1989-11-08 1992-08-18 Corral David F Orthotopic intraventricular heart pump
US5269811A (en) * 1989-11-30 1993-12-14 National Research Council Of Canada Primary fluid actuated, secondary fluid propelling system
US5222980A (en) * 1991-09-27 1993-06-29 Medtronic, Inc. Implantable heart-assist device
US20050256363A1 (en) * 1997-10-09 2005-11-17 Bolling Steven F Implantable heart assist system and method of applying same
US20060276681A1 (en) * 1997-10-09 2006-12-07 Bolling Steven F Implantable heart assist system and method of applying same
US6387037B1 (en) 1997-10-09 2002-05-14 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6390969B1 (en) 1997-10-09 2002-05-21 Orqis Medical Corporation Implantable heart assist system and method of applying same
US7591778B2 (en) 1997-10-09 2009-09-22 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6428464B1 (en) 1997-10-09 2002-08-06 Orqis Medical Corporation Implantable heart assist system
US20030069468A1 (en) * 1997-10-09 2003-04-10 Bolling Steven F. Implantable heart assist system and method of applying same
US6610004B2 (en) 1997-10-09 2003-08-26 Orqis Medical Corporation Implantable heart assist system and method of applying same
US20040019251A1 (en) * 1997-10-09 2004-01-29 Anthony Viole Implantable heart assist system and method of applying same
US6685621B2 (en) 1997-10-09 2004-02-03 Orois Medical Corporation Implantable heart assist system and method of applying same
US20040116768A1 (en) * 1997-10-09 2004-06-17 Bolling Steven F. Implantable heart assist system and method of applying same
US20040236172A1 (en) * 1997-10-09 2004-11-25 Bolling Steven F. Implantable heart assist system and method of applying same
US7588531B2 (en) 1997-10-09 2009-09-15 Orqis Medical Corporation Implantable heart assist system and method of applying same
US7993260B2 (en) 1997-10-09 2011-08-09 Thoratec Corporation Implantable heart assist system and method of applying same
US6889082B2 (en) 1997-10-09 2005-05-03 Orqis Medical Corporation Implantable heart assist system and method of applying same
US7513863B2 (en) 1997-10-09 2009-04-07 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6200260B1 (en) 1997-10-09 2001-03-13 Fore Flow Corporation Implantable heart assist system
US7458929B2 (en) 1997-10-09 2008-12-02 Orqis Medical Corporation Implantable heart assist system and method of applying same
US8900115B2 (en) 1997-10-09 2014-12-02 Thoratec Corporation Implantable heart assist system and method of applying same
US7614997B2 (en) 1997-10-09 2009-11-10 Orqis Medical Corporation Implantable heart assist system and method of applying same
US7144365B2 (en) 1997-10-09 2006-12-05 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6299575B1 (en) 1997-10-09 2001-10-09 Orqis Medical Corporation Implantable heart assist system
US7125376B2 (en) 1997-10-09 2006-10-24 Orqis Medical Corporation Implantable heart assist system and method of applying same
US20060270892A1 (en) * 1997-10-09 2006-11-30 Bolling Steven F Implantable heart assist system and method of applying same
US6406422B1 (en) 2000-03-02 2002-06-18 Levram Medical Devices, Ltd. Ventricular-assist method and apparatus
US7331921B2 (en) 2002-02-15 2008-02-19 Orqis Medical Corporation Implantable heart assist system and method of applying same
US20040236173A1 (en) * 2002-02-15 2004-11-25 Anthony Viole Implantable heart assist system and method of applying same
US20050085683A1 (en) * 2003-10-15 2005-04-21 Bolling Steven F. Implantable heart assist system and method of applying same
US20050131385A1 (en) * 2003-12-12 2005-06-16 Bolling Steven F. Cannulae for selectively enhancing blood flow
US20050277803A1 (en) * 2004-06-10 2005-12-15 Robert Pecor Cannulae having reduced flow resistance
US7445592B2 (en) 2004-06-10 2008-11-04 Orqis Medical Corporation Cannulae having reduced flow resistance
US20050277870A1 (en) * 2004-06-10 2005-12-15 Robert Pecor Cannula having reduced flow resistance
WO2006037519A1 (de) * 2004-10-01 2006-04-13 Universitätsklinikum Freiburg Peristaltische pumpe
US20060184199A1 (en) * 2005-02-14 2006-08-17 O'leary Shawn Apparatus and methods for reducing bleeding from a cannulation site
US20060224110A1 (en) * 2005-03-17 2006-10-05 Scott Michael J Methods for minimally invasive vascular access
US20100145299A1 (en) * 2006-05-30 2010-06-10 Yossi Gross Implantable Pump for Drug Delivery to Treat Erectile Dysfunction
US8273063B2 (en) 2006-05-30 2012-09-25 Yossi Gross Implantable pump for drug delivery to treat erectile dysfunction
US8152711B2 (en) 2007-03-21 2012-04-10 Yossi Gross Implantable peristaltic pump to treat erectile dysfunction
US20080234536A1 (en) * 2007-03-21 2008-09-25 Yossi Gross Implantable peristaltic pump to treat erectile dysfunction
US7818062B2 (en) 2008-01-31 2010-10-19 Ed Tech Medical Ltd. Peristaltic pump for treatment of erectile dysfunction
US20090198097A1 (en) * 2008-01-31 2009-08-06 Ed Tech Medical Ltd. Peristaltic pump for treatment of erectile dysfunction

Also Published As

Publication number Publication date
NL7402782A (de) 1974-09-09
BE811852A (fr) 1974-09-04
JPS5026397A (de) 1975-03-19
FR2220279B1 (de) 1978-11-17
CA1017904A (en) 1977-09-27
CH571866A5 (de) 1976-01-30
DE2410418A1 (de) 1974-09-19
FR2220279A1 (de) 1974-10-04

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