WO1985001436A1 - Anti-thrombogenic blood pump - Google Patents

Anti-thrombogenic blood pump Download PDF

Info

Publication number
WO1985001436A1
WO1985001436A1 PCT/US1984/001558 US8401558W WO8501436A1 WO 1985001436 A1 WO1985001436 A1 WO 1985001436A1 US 8401558 W US8401558 W US 8401558W WO 8501436 A1 WO8501436 A1 WO 8501436A1
Authority
WO
WIPO (PCT)
Prior art keywords
blood
pump
bearing
fluid
purge
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US1984/001558
Other languages
English (en)
French (fr)
Inventor
John C. Moise
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Nimbus Inc
Original Assignee
Nimbus Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Nimbus Inc filed Critical Nimbus Inc
Priority to BR8407085A priority Critical patent/BR8407085A/pt
Priority to AT84903736T priority patent/ATE74776T1/de
Priority to DE8484903736T priority patent/DE3485662D1/de
Publication of WO1985001436A1 publication Critical patent/WO1985001436A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D29/00—Details, component parts, or accessories
    • F04D29/08—Sealings
    • F04D29/10—Shaft sealings
    • F04D29/106—Shaft sealings especially adapted for liquid pumps
    • F04D29/108—Shaft sealings especially adapted for liquid pumps the sealing fluid being other than the working liquid or being the working liquid treated
    • 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
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist 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
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • 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
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A61M60/221—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having both radial and axial components, e.g. mixed flow pumps
    • 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
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
    • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
    • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
    • 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
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/818—Bearings
    • A61M60/824—Hydrodynamic or fluid film bearings
    • 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
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/827—Sealings between moving parts
    • A61M60/829—Sealings between moving parts having a purge fluid supply
    • 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
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/827—Sealings between moving parts
    • A61M60/829—Sealings between moving parts having a purge fluid supply
    • A61M60/831—Sealings between moving parts having a purge fluid supply using filtered blood as purge fluid
    • 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
    • A61M25/00—Catheters; Hollow probes
    • 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

  • This invention relates to continuous delivery blood pumps, and more particularly an implantable blood pump having little or no thrombogenicity and high reliability.
  • Continuous delivery blood pumps used in heart assist applications have inherent size advantages over cyclic delivery blood pumps because they pump all the time and can operate at high speeds.
  • the cannula size is reduced due to the continuous delivery feature.
  • the smaller size of the pump itself eases anatomic placement constraints and allows placements which would otherwise be impossible.
  • Continuous delivery blood pumps do, however, have certain disadvantages.
  • the shear forces created by the relative motion of the impeller and housing may cause hemolysis (i.e. destruction of red cell membranes). Blood elements caught in eddies under the impeller shroud, or stagnating in unswept recesses, are prone to cause thrombosis (i.e. the formation of dangerous blood clots).
  • the present invention essentially eliminates the thrombogenicity of the interface between the rotating and stationary parts of the pump by providing a purge seal through which a blood-compatible fluid is introduced into the blood stream at the interface at a flow rate just sufficient to exceed, at all points along the perimeter of the interface, the blood flow rate into the interface caused by diffusion or other mechanisms.
  • Purge seal techniques are known in technologies relating to the pumping of particulate or abrasive slurries in industry, U.S. Patent No. 4,224,008 to Haentjens,
  • the purge fluid may be derived from the blood stream by membrane filtration, and the pressure built up in the blood str by the pump may be used to maintain an adequate purge flow.
  • the pump can be operated indefinitely in a purg seal mode without any external source of purge fluid. It is thus the object of the invention to provide a non-thrombogenie blood pump by using a purge seal to create a benign interface in the blood stream between rotating and stationary parts of the pump.
  • Fig. 1 is a partially schematic vertical section through a centrifugal-flow embodiment of the pump of this invention
  • Fig. 2 is an enlarged view of the portion of Fig. 1 lying within the line marked "Fig. 2" in Fig. 1;
  • Fig. 3 is an enlarged view, similar to Fig. 2, of an alternative embodiment of the punp of Fig. 1 using a face sea
  • Fig.4a is an enlarged view, similar to Fig. 2, of an alternative embodiment of the pump of Fig. 1 using spherical bearings;
  • Fig. 4b is an end view of the spherical bearing of Fig. showing the groove pattern therein;
  • Fig. 5 is a fragmentary axial section through an axial flow embodiment of the invention using spherical bearings
  • Fig. 6 is a schematic diagram illustrating the derivat of the purge fluid from the blood stream. Description of the Preferred Embodiment
  • a centrifugal-flow embodiment of the pump of this invention is generally shown at 10.
  • the basic components of the pump are the housing 12, the motor 14 (which is symbolically shown as an electric motor but which may equally well be another type of rotary power device, e.g. driven rotor), and the impeller chamber 16.
  • the impeller 18, a portion of which is shown in more detail in Fig. 2 is driven by the shaft 20 and is shaped to complement the shape of the impeller chamber 16.
  • the impeller 13 has a hub 22 whose surface 24 is curved in such a way as to form a continuation of the curved surface 26 of the interior wall 28 of the impeller chamber 16.
  • the hub 22, which forms the impeller end of shaft 20, carries a plurality of impeller blades 30 of generally conventional design except for the elimination of any shroud on either the front or back of the blades and the fact that their interior edge 32 parallels the curved surface 26 bat is spaced therefrom beginning at a point 34 on the hub 22 just short of the interface 36 at which the rotating hub 22 meets the stationary interior wall 28.
  • Blood flows from the central blood inlet 37 to the blood outlet volute 39 in the direction arrow 38 through the impeller chamber 16. Because of the fact that there is no recess in the hub 22 in which blood can be trapped, the blood stream is continuously swept along the hub surface 24 and the interior wall surface 26.
  • the bearing 40 is of the hydrodynamic type and rotates on a thin cushion of fluid supplied to it from the cylindrical bearing plenum 42 fed by conduits 44 from the bearing fluid inlet 43.
  • a single bearing fed directly from motor cavity 41 mav be used.
  • a cylindrical equalizing plenum 46 is provided at the impeller chamber end of the bearing 40 to permit the recirculating end flow of bearing fluid which is characteristic of hydrodynamic bearings.
  • the equalizing plenum 46 may be connected to a low-impedance source of bearing fluid by a conduit 47 if desired.
  • the impeller chamber wall 28 has a shaft opening 49 (Fig. 2) so dimensioned as to restrict the flow of bearin fluid and to minimize the area of interface 36; however, the axial length of the restricted opening 49 is not sufficient for it to induce significant recirculating flow as a result of bearing action.
  • the bearing clearances typically on the order of 2.5 ⁇ m
  • the bearing fluid pressures are adj-usted in such a manner as to create a purge flow P (Fig. 2) toward the impeller chamber 16 at the interface 36 with a velocity on the order of 0.01 to 0.1 mm/sec.
  • the flow rat should be just sufficient, at all points along the circular interface 36, to overcome any inward flow of blood or blood elements toward the bearing 40.
  • This inward flow is determined by the diffusion rate of the blood elements into the bearing fluid, as well as by other parameters which vary slightly along the perimeter of interface 36. Some of this variation is due to the fact that if the density of the bearing fluid is less than that of the blood, gravity will tend to force more blood toward the bearing on the bottom side of the shaft 20.
  • Figs. 3 through 5 depict alternative types of purge seals embodying the invention.
  • Fig. 3 illustrates the application of the invention to a face seal.
  • the seal in the pump of Figs. 1 and 2 is generally cylindrical, and thus requires an axial purge flow using a face seal (in which the purge flow is rad ally outward into the blood stream) would also be practical.
  • the face seal can optionally also act as a thrust bearing.
  • the face seal arrangement is also frequently useful in axial pumps.
  • Figs. 4a, 4b, and 5 illustrate a third type of seal usable with both centrifugal and axial blood pumps. This third type is a hybrid seal formed at the end of a spherical bearing which serves as a combination journal and thrust bearing. The principles of this invention are equally applicable to all of these seal configurations.
  • a rotor 50 is mounted in a stator 52 for rotation about the axis 54.
  • the rotor 50 is positioned with respect to stator 52 by a pair of spherical bearings 56, 58.
  • the bearings 56, 58 ride against a movable bearing block 57 and a stationary bearing block 59, respectively.
  • Pins 60 prevent rotation of bearing block 97 but allow it to move axially under the bias of spring 61 to maintain close tolerances both in bearing 56 and (by pushing the entire rotor 50 to the left) in bearing 58.
  • Bearing fluid under pressure is supplied to the pump through cannula 62, which also contains the drive shaft 63 for rotor 50.
  • the bearing fluid flows as a lubricant through bearing 56, and on into the plenum 64 in which the spring 61 is positioned. From there, the bearing fluid flows outwardly through bearing 58, and particularly its seal portion 70, into the blood stream 66 at interface 67.
  • the blood stream 66 is propelled axially through the pump by the interaction of rotor blades 68 and stator blades 69.
  • Fig. 5 depicts a single-stage pump, the invention is of course equally applicable to multistage pumps.
  • the spherical purge seal 70 of this invention is formed by the outer portion of the bearing 58 nearest the blood stream.
  • a very small bearing clearance is essential at the seal 70.
  • a greater volume of bearing fluid can be handled for bearin lubrication and hydrodynamic recirculation by providing the bearing block 59 with radial grooves 71 and an annular recirculating channel 72.
  • Adequate bearing fluid flow through bearing 56 can be assured by extending channels 73 radially throughout the surface of bearing block 57.
  • a face seal instead of the cylindrical seal of Fig. 2 is illustrated in a centrifugal pump of the general type shown in Fig. 1.
  • the inner end of hub 74 is substantially wider than the outer end of shaft 76 to which it is attached.
  • the disc-shaped face seal 78 can, if desired, also serve as a thrust bearing for the shaft 76.
  • Fluid is supplied to the journal bearing 80 and the face seal 78 from an annular plenum 82 fed by a duct 84 in the impeller chamber wall 86.
  • the radial interface 88 is continuously swept by the blood flow from the hub 74 to the impeller blades 90.
  • the blood pump of this invention may utilize other accepted techniques for minimizing thrombus generation such as the use of thromboresistant surfaces and avoidance of stagnation areas throughout the pump.
  • the use of anticoagulants is not normally necessary with the construction of this invention as it is with most prior art devices, and that the pump of this invention may be of significant benefit in patients who have bleeding problems or in which the use of anticoagulants is contraindicated for some other reason.
  • the purge fluid is also used to lubricate hydrodynamic bearings
  • the purge seal may be isolated from the bearings, and the purge fluid used only for seal purposes without departing from the invention.
  • rolling contact bearings may be used instead of hydrodynamic bearings if desired.
  • Each of the aforementioned purge fluids must be supplied to the pump 10 from some external reservoir or source (not shown) which can be replenished from time to time, albeit infrequently due to the slow purge flow rate.
  • the need for such an external fluid supply can be eliminated entirely by the use of a membrane recirculator 100 as illustrated by the schematic diagram of Fig. 6.
  • the blood stream 102 on the outlet side of the pump is exposed to the high-pressure side 104 of a filtration membrane 106.
  • the membrane 106 which passes small molecules such as urea and glucose but excludes proteins, produces a protein-induced osmotic potential of about 22 mmHg.
  • a bearing fluid in the nature of a proteinfree blood filtrate consisting of water, small molecules (e.g. glucose, urea, and amino acids) and ions capable of penetrating the membrane 106) is recovered.
  • the recovered bearing fluid will have a pressure head, on the low-pressure side 108 of membrane 106, of approximately 78 mmHg.
  • the invention provides an effective continuous delivery blood pump with minimum tendency to thrombus generation which, if desired, can be implanted in a patient for extended periods of time with minimum risk of blood clots or malfunction.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Mechanical Engineering (AREA)
  • Cardiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Anesthesiology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • General Engineering & Computer Science (AREA)
  • External Artificial Organs (AREA)
  • Structures Of Non-Positive Displacement Pumps (AREA)
PCT/US1984/001558 1983-09-28 1984-09-26 Anti-thrombogenic blood pump Ceased WO1985001436A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
BR8407085A BR8407085A (pt) 1983-09-28 1984-09-26 Bomba de sangue anti-trombogenica
AT84903736T ATE74776T1 (de) 1983-09-28 1984-09-26 Antithrombose blutpumpe.
DE8484903736T DE3485662D1 (de) 1983-09-28 1984-09-26 Antithrombose blutpumpe.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US06/537,243 US4704121A (en) 1983-09-28 1983-09-28 Anti-thrombogenic blood pump
US537,243 1990-06-13

Publications (1)

Publication Number Publication Date
WO1985001436A1 true WO1985001436A1 (en) 1985-04-11

Family

ID=24141832

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1984/001558 Ceased WO1985001436A1 (en) 1983-09-28 1984-09-26 Anti-thrombogenic blood pump

Country Status (7)

Country Link
US (1) US4704121A (https=)
EP (1) EP0157859B1 (https=)
JP (1) JPS61500058A (https=)
BR (1) BR8407085A (https=)
CA (1) CA1222355A (https=)
DE (1) DE3485662D1 (https=)
WO (1) WO1985001436A1 (https=)

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0396575A4 (en) * 1987-11-24 1990-12-05 Nimbus Medical, Inc. Single-stage axial flow blood pump
DE4105278A1 (de) * 1991-02-20 1992-08-27 Rau Guenter Blutpumpe als kreiselpumpe
EP0371985B1 (en) * 1987-06-12 1994-08-17 KLETSCHKA, Harold D. Rotary pump with a coupling section
EP0768091A1 (en) * 1995-10-16 1997-04-16 Sun Medical Technology Research Corporation Artificial heart
WO1998050089A1 (en) * 1997-05-02 1998-11-12 University Of Pittsburgh Rotary pump having a bearing which dissipates heat
US6858001B1 (en) 1997-07-11 2005-02-22 A-Med Systems, Inc. Single port cardiac support apparatus
US7182727B2 (en) 1997-07-11 2007-02-27 A—Med Systems Inc. Single port cardiac support apparatus
WO2009157840A1 (en) * 2008-06-23 2009-12-30 Cardiobridge Gmbh Catheter pump for circulatory support
RU2629054C1 (ru) * 2016-08-10 2017-08-24 Федеральное государственное бюджетное учреждение "Национальный исследовательский центр "Курчатовский институт" Осевой насос вспомогательного кровообращения
JP2020501740A (ja) * 2016-12-19 2020-01-23 アビオメド インコーポレイテッド 受動的パージシステムを備えた心臓ポンプ
US10610626B2 (en) 2012-02-16 2020-04-07 Abiomed Europe Gmbh Intravascular blood pump
US11874225B2 (en) 2018-07-26 2024-01-16 The University Of Tokyo Measurement device, measurement system, measurement program, and measurement method
CN117771537A (zh) * 2024-01-11 2024-03-29 上海焕擎医疗科技有限公司 叶轮组件及机械循环辅助装置

Families Citing this family (150)

* Cited by examiner, † Cited by third party
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US4994078A (en) * 1988-02-17 1991-02-19 Jarvik Robert K Intraventricular artificial hearts and methods of their surgical implantation and use
US5092879A (en) * 1988-02-17 1992-03-03 Jarvik Robert K Intraventricular artificial hearts and methods of their surgical implantation and use
US4908012A (en) * 1988-08-08 1990-03-13 Nimbus Medical, Inc. Chronic ventricular assist system
US4944722A (en) * 1989-02-23 1990-07-31 Nimbus Medical, Inc. Percutaneous axial flow blood pump
US4995857A (en) * 1989-04-07 1991-02-26 Arnold John R Left ventricular assist device and method for temporary and permanent procedures
US5324177A (en) * 1989-05-08 1994-06-28 The Cleveland Clinic Foundation Sealless rotodynamic pump with radially offset rotor
US5049134A (en) * 1989-05-08 1991-09-17 The Cleveland Clinic Foundation Sealless heart pump
US4927407A (en) * 1989-06-19 1990-05-22 Regents Of The University Of Minnesota Cardiac assist pump with steady rate supply of fluid lubricant
US5044897A (en) * 1989-07-10 1991-09-03 Regents Of The University Of Minnesota Radial drive for implantable centrifugal cardiac assist pump
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US5098256A (en) * 1989-11-21 1992-03-24 The Cleveland Clinic Foundation Viscous seal blood pump
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US5145333A (en) * 1990-03-01 1992-09-08 The Cleveland Clinic Foundation Fluid motor driven blood pump
US5112200A (en) * 1990-05-29 1992-05-12 Nu-Tech Industries, Inc. Hydrodynamically suspended rotor axial flow blood pump
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IT1243345B (it) * 1990-07-16 1994-06-10 Dideco Spa Pompa centrifuga per liquido, in particolare sangue in circolazione extracorporea
US5055005A (en) * 1990-10-05 1991-10-08 Kletschka Harold D Fluid pump with levitated impeller
US5205721A (en) * 1991-02-13 1993-04-27 Nu-Tech Industries, Inc. Split stator for motor/blood pump
US6346120B1 (en) * 1992-06-23 2002-02-12 Sun Medical Technology Research Corporation Auxiliary artificial heart of an embedded type
US5300112A (en) * 1992-07-14 1994-04-05 Aai Corporation Articulated heart pump
US5399074A (en) * 1992-09-04 1995-03-21 Kyocera Corporation Motor driven sealless blood pump
DE69229964T2 (de) * 1992-10-19 2000-01-27 The Cleveland Clinic Foundation, Cleveland Unversiegelte rotodynamische pumpe
US5376114A (en) * 1992-10-30 1994-12-27 Jarvik; Robert Cannula pumps for temporary cardiac support and methods of their application and use
US5947892A (en) * 1993-11-10 1999-09-07 Micromed Technology, Inc. Rotary blood pump
US5613935A (en) * 1994-12-16 1997-03-25 Jarvik; Robert High reliability cardiac assist system
US5707218A (en) * 1995-04-19 1998-01-13 Nimbus, Inc. Implantable electric axial-flow blood pump with blood cooled bearing
JP2928875B2 (ja) * 1995-06-05 1999-08-03 セイコーエプソン株式会社 人工心臓ポンプのシール機構
US5824070A (en) * 1995-10-30 1998-10-20 Jarvik; Robert Hybrid flow blood pump
US5840070A (en) 1996-02-20 1998-11-24 Kriton Medical, Inc. Sealless rotary blood pump
US5695471A (en) * 1996-02-20 1997-12-09 Kriton Medical, Inc. Sealless rotary blood pump with passive magnetic radial bearings and blood immersed axial bearings
DE19613565C1 (de) * 1996-04-04 1997-07-24 Guenter Prof Dr Rau Intravasale Blutpumpe
US5911685A (en) * 1996-04-03 1999-06-15 Guidant Corporation Method and apparatus for cardiac blood flow assistance
DE19613564C1 (de) * 1996-04-04 1998-01-08 Guenter Prof Dr Rau Intravasale Blutpumpe
US5746709A (en) * 1996-04-25 1998-05-05 Medtronic, Inc. Intravascular pump and bypass assembly and method for using the same
US5814011A (en) * 1996-04-25 1998-09-29 Medtronic, Inc. Active intravascular lung
US5810758A (en) * 1996-05-23 1998-09-22 Sun Medical Technology Research Corporation Purge solution circulating apparatus for artificial organ
US6244835B1 (en) 1996-06-26 2001-06-12 James F. Antaki Blood pump having a magnetically suspended rotor
US6015272A (en) * 1996-06-26 2000-01-18 University Of Pittsburgh Magnetically suspended miniature fluid pump and method of designing the same
US5851174A (en) * 1996-09-17 1998-12-22 Robert Jarvik Cardiac support device
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EP0157859B1 (en) 1992-04-15
JPS61500058A (ja) 1986-01-16
EP0157859A4 (en) 1987-09-02
DE3485662D1 (de) 1992-05-21
EP0157859A1 (en) 1985-10-16
CA1222355A (en) 1987-06-02
JPH0472551B2 (https=) 1992-11-18
US4704121A (en) 1987-11-03
BR8407085A (pt) 1985-08-13

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