WO1990001347A1 - Chronic ventricular assist system - Google Patents

Chronic ventricular assist system Download PDF

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Publication number
WO1990001347A1
WO1990001347A1 PCT/US1989/003385 US8903385W WO9001347A1 WO 1990001347 A1 WO1990001347 A1 WO 1990001347A1 US 8903385 W US8903385 W US 8903385W WO 9001347 A1 WO9001347 A1 WO 9001347A1
Authority
WO
WIPO (PCT)
Prior art keywords
pump
blood
stator
rotor
motor
Prior art date
Application number
PCT/US1989/003385
Other languages
French (fr)
Inventor
John C. Moise
Richard C. Wampler
Kenneth C. Butler
Original Assignee
Nimbus Medical, 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 Medical, Inc. filed Critical Nimbus Medical, Inc.
Publication of WO1990001347A1 publication Critical patent/WO1990001347A1/en

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Classifications

    • 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
    • A61M60/10—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
    • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial 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
    • A61M60/422—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being electromagnetic, e.g. using canned motor 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
    • A61M60/10—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
    • 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
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S415/00—Rotary kinetic fluid motors or pumps
    • Y10S415/90—Rotary blood pump

Definitions

  • This invention relates to an implantable continuous delivery ventricular assist system for patients with chronic cardiac disease, and more particularly to a system which does not require a discontinuity in the blood path wall for power transmission into the pump.
  • Background of the invention Currently available ventricular assist systems using a continuous delivery blood pump, whether intravascular or implanted, have a common problem: somewhere in the system, the drive for the pump blades has to traverse the wall of the blood path. This is equally true of the shaft which drives the impeller of a centrifugal pump such as disclosed in
  • the present invention provides an implantable axial flow blood pumping system suitable for chronic ventricular assist which overcomes the above-described problems, yet whose construction and operation uses existing technology to advantage, and which can function with only a small percutaneous access for purge fluid and electrical power.
  • the pump of this invention avoids the need for a purge fluid supply to traverse the wall of the blood path by introducing the purge fluid into the pump stator through the interior of a stator blade.
  • the need for torque transmission through the blood path wall is avoided by placing a permanent magnet rotor on the pump rotor (i.e. integrating the motor rotor with the rotatable pump element), and placing all motor windings outside the blood path.
  • the inventive pump is an order of magnitude lighter and smaller, and less subject to motion or vibration, than previously known implantable blood pumps of the same capacity. Also, the small diameter (on the order of 3mm) of the percutaneous access tube required minimizes the physiological stresses from that source.
  • the pump of this invention consists of a cylindrical blood tube in which a pump stator is coaxially suspended by a set of stator blades, one of which also serve as a conduit to convey purge fluid from the outside of the blood tube through the pump stator to the pump bearings.
  • a hermetically sealed motor stator provides power to the pump rotor which is supported in the pump stator for rotation coaxially therewith.
  • the relative positions of the motor stator and rotor provide a very good heat conduction path from the motor stator iron into the blood. This is important for thermal management: tolerance of the implant is considerably improved by driving the heat generated by the motor into the blood rather than into the surrounding tissues.
  • the use of the short, straight blood tube and the use of an axial flow pump with common pump and motor bearings gives the inventive device a compactness, even at flow rates of 6 L/min or more, which greatly enhances its anatomic compatibility and allows it to be placed adjacent to the heart. Also, the absence of any eddy-causing obstructions or changes in flow direction throughout the device greatly reduces the likelihood of thrombus formation. It is therefore the object of the invention to provide a very compact, high-flow implantable axial flow blood pump which is well tolerated by the body.
  • Fig. 1 is an axial section of one embodiment of the pump of this invention
  • Fig. 2 is a transverse section along line 2-2 of Fig. 1;
  • Fig. 3 is an axial section of another embodiment of the pump of this invention.
  • Fig. 4 is a schematic illustration showing the percutaneous purge fluid and power supplies of the preferred embodiment of the invention.
  • the pump 10 depicted in Figs. 1 and 2 essentially consists of a blood tube 12 surrounded by a hermetically sealed motor stator 14.
  • An axial flow blood pump 16 is disposed coaxially within the blood tube 12 and forms therewith an annular blood duct which is a part of the blood path of the inventive system.
  • the pump 16 is composed of a pump rotor 18 which includes the motor rotor 19 and blades 24, 26, and a pump stator 20 including a stator housing 21 which is fixedly mounted in the tube 12 by stator blades 22.
  • the pump rotor 18 has a hub 23 which carries one or more sets of rotor blades 24, 26,.
  • journal bearing 28 is slidably mounted in the cavity 35 formed by sleeve 36 within stator housing 21.
  • the sleeve 36 is preferably made of a compatible bearing material because it can touch bearings 28 and 30 under startup or severe loading conditions.
  • Spring 38 has a dual function: it biases bearing 30 into engagement with the inwardly directed end of sleeve 36, and the surfaces of face seal 34 against each other; and its torque also causes bearing 28 to rotate with shaft 27 even though it is not attached to the shaft 27.
  • a blood-compatible purge fluid e.g. saline solution
  • a blood-compatible purge fluid for the hydrodynamic surfaces 28, 30 and 34 is supplied to the pump 10 from outside the patient's body through a lumen of the percutaneous conduit 40 which is connected to a passage 41 extending through one of the stator blades 22 and through housing 21 and sleeve 36 into the cavity 35.
  • the purge fluid is discharged into the blood at face seal 34.
  • the motor stator 14 is enclosed in a hermetically sealed motor housing 42.
  • the motor formed by motor stator 14 and motor rotor 19 is preferably a 3 -phase brushless DC motor.
  • Power is preferably supplied to the windings 44, 46 of the motor stator 14 from an extracorporeal power source, e.g. a power supply package carried by the patient, through appropriate wiring 48 extending through a second lumen of the percutaneous tube 40, and into the motor housing 42 through a fluid-tight seal 49.
  • the purge fluid supply connection 50 is preferably located outside the housing 42 to prevent accidental leakage of saline fluid into the motor housing 42.
  • the motor Inasmuch as most of the heat developed in the operation of the motor is generated in the motor and conveyed by the stator iron, the motor is effectively cooled by the blood and therefore imposes little thermal load on the tissues in which it is implanted. For that reason, and also because of the relatively vibration-free operation of an axial flow pump, the pump 10 is physiologically much more tolerable than prior art devices.
  • Fig. 2 illustrates the disposition of the stator blades 22. It will be understood that although four stator blades are shown, the number of stator blades used will depend upon the circumstances of a particular design and is not part of this invention.
  • Fig. 3 shows an alternative embodiment of the device of this invention.
  • the motor rotor is axially positioned within the pump stator housing 21, and the pump rotor portion axially outside the stator housing 21 merely carries the rotor blades.
  • the rotational torque is transferred directly from the motor rotor to the rotor blades, and the bearings in the stator need only support the overhang load.
  • the overhang bending moment is greater in the Fig. 1 embodiment because of the weight of the motor rotor and its distance from the bearings .
  • the embodiment of Fig. 3 features a reduced overhang bending moment, and therefore imposes less load on the bearings.
  • a significant clearance must be maintained in the configuration of Fig. 3 between the motor rotor 19 and the stator housing 21 to minimize fluid losses. This increases the magnetic gap between the motor stator and rotor, and the electromagnetic losses associated therewith.
  • the structure of the pump 10 is the same as that described above in connection with Fig. 1, except that the motor rotor 20 is positioned at the left end of shaft 27 within the stator housing 21. This allows the overhanging rotor hub 23 to be made shorter, thus providing a better balance and imposing less of a bending moment on shaft 27.
  • the sources of purge fluid and electrical power for the motor may, as shown in Fig. 4, be a constant-volume fluid supply and delivery device 60 and a motor power supply 62 including a power source and the necessary electronics for controlling the motor.
  • the devices 60 and 62 may be carried by the patient on an appropriate belt 64.

Abstract

An implantable ventricular assist system uses a small high-speed axial flow blood pump (16) which may be grafted into the patient's circulatory system. The pump includes a blood tube (12) in which the pump rotor (18) and stator (20) are coaxially contained, and a motor stator (14) surrounding the blood duct. A permanent magnet motor rotor (19) is integral with the pump rotor (18). Purge fluid for the hydrodynamic bearings (28, 30) of the device and power for the motor are preferably percutaneously introduced from extracorporeal sources worn by the patient. The purge fluid is introduced into the pump stator blades (22). This construction avoids the creation of discontinuities in the blood path wall due to the routing of drive power and/or fluid supply elements through the blood path wall. The described construction greatly reduces the size of the implant needed for a given blood flow rate and enhances its physiological compatibility with the body.

Description

CHRONIC VENTRICULAR ASSIST SYSTEM
Field of the invention
This invention relates to an implantable continuous delivery ventricular assist system for patients with chronic cardiac disease, and more particularly to a system which does not require a discontinuity in the blood path wall for power transmission into the pump. Background of the invention Currently available ventricular assist systems using a continuous delivery blood pump, whether intravascular or implanted, have a common problem: somewhere in the system, the drive for the pump blades has to traverse the wall of the blood path. This is equally true of the shaft which drives the impeller of a centrifugal pump such as disclosed in
U.S. Patent No. 4,704,121 and of the drive cable of U.S. Patent No. 4,625,712 which must traverse the wall of the femoral artery.
Wherever the drive traverses the wall of the blood path, a discontinuity exists which involves a danger of thrombus formation. Although this danger is substantially alleviated in centrifugal pumps by the invention disclosed in U.S. Patent No. 4,704,121, it still exists in the physiologically much more desirable axial flow pumps. Ideally, this problem can be solved by an axial flow pump with a magnetically suspended rotor, such as that proposed in copending application Serial No. 07/036,304, which requires no bearing purge fluid supply and no penetration of the blood path wall; nor, for that matter, any percutaneous device. However, magnetically suspended blood pumps belong to a developing technology, and their commercial viability is still in the future.
A major problem with implanted cardiac assist devices is the almost universal emergence of infection when a device has been implanted for several months. It is believed that infection is related not only to sepsis of the percutaneous access, but also to the weight, relative motion and surface area of the device itself. Summary of the invention
The present invention provides an implantable axial flow blood pumping system suitable for chronic ventricular assist which overcomes the above-described problems, yet whose construction and operation uses existing technology to advantage, and which can function with only a small percutaneous access for purge fluid and electrical power. The pump of this invention avoids the need for a purge fluid supply to traverse the wall of the blood path by introducing the purge fluid into the pump stator through the interior of a stator blade. The need for torque transmission through the blood path wall is avoided by placing a permanent magnet rotor on the pump rotor (i.e. integrating the motor rotor with the rotatable pump element), and placing all motor windings outside the blood path. The incidence of infection is reduced because the inventive pump is an order of magnitude lighter and smaller, and less subject to motion or vibration, than previously known implantable blood pumps of the same capacity. Also, the small diameter (on the order of 3mm) of the percutaneous access tube required minimizes the physiological stresses from that source.
The pump of this invention consists of a cylindrical blood tube in which a pump stator is coaxially suspended by a set of stator blades, one of which also serve as a conduit to convey purge fluid from the outside of the blood tube through the pump stator to the pump bearings. A hermetically sealed motor stator provides power to the pump rotor which is supported in the pump stator for rotation coaxially therewith.
The relative positions of the motor stator and rotor provide a very good heat conduction path from the motor stator iron into the blood. This is important for thermal management: tolerance of the implant is considerably improved by driving the heat generated by the motor into the blood rather than into the surrounding tissues. The use of the short, straight blood tube and the use of an axial flow pump with common pump and motor bearings gives the inventive device a compactness, even at flow rates of 6 L/min or more, which greatly enhances its anatomic compatibility and allows it to be placed adjacent to the heart. Also, the absence of any eddy-causing obstructions or changes in flow direction throughout the device greatly reduces the likelihood of thrombus formation. It is therefore the object of the invention to provide a very compact, high-flow implantable axial flow blood pump which is well tolerated by the body.
It is another object of the invention to provide an implantable ventricular assist system which has no drive or fluid supply elements traversing the wall of the blood path, and in which the heat generated by the motor is largely absorbed by the pumped blood.
It is a further object of the invention to provide an implantable blood pump system with percutaneous access in which the diameter of the required percutaneous access is minimized.
Brief description of the drawing
Fig. 1 is an axial section of one embodiment of the pump of this invention; Fig. 2 is a transverse section along line 2-2 of Fig. 1;
Fig. 3 is an axial section of another embodiment of the pump of this invention; and
Fig. 4 is a schematic illustration showing the percutaneous purge fluid and power supplies of the preferred embodiment of the invention.
Description of the preferred embodiment
The pump 10 depicted in Figs. 1 and 2 essentially consists of a blood tube 12 surrounded by a hermetically sealed motor stator 14. An axial flow blood pump 16 is disposed coaxially within the blood tube 12 and forms therewith an annular blood duct which is a part of the blood path of the inventive system. The pump 16 is composed of a pump rotor 18 which includes the motor rotor 19 and blades 24, 26, and a pump stator 20 including a stator housing 21 which is fixedly mounted in the tube 12 by stator blades 22. The pump rotor 18 has a hub 23 which carries one or more sets of rotor blades 24, 26,. and which is mounted on a shaft 27 supported for rotation in pump stator 20 by a hydrodynamic journal bearing 28, and by a combined hydrodynamic journal and thrust bearing 30 fixed to the shaft 27. The outer surfaces of bearings 28 and 30 are preferably grooved for hydrodynamic reasons. Journal bearing 28 is slidably mounted in the cavity 35 formed by sleeve 36 within stator housing 21. The sleeve 36 is preferably made of a compatible bearing material because it can touch bearings 28 and 30 under startup or severe loading conditions. Spring 38 has a dual function: it biases bearing 30 into engagement with the inwardly directed end of sleeve 36, and the surfaces of face seal 34 against each other; and its torque also causes bearing 28 to rotate with shaft 27 even though it is not attached to the shaft 27.
A blood-compatible purge fluid (e.g. saline solution) for the hydrodynamic surfaces 28, 30 and 34 is supplied to the pump 10 from outside the patient's body through a lumen of the percutaneous conduit 40 which is connected to a passage 41 extending through one of the stator blades 22 and through housing 21 and sleeve 36 into the cavity 35. The purge fluid is discharged into the blood at face seal 34.
The motor stator 14 is enclosed in a hermetically sealed motor housing 42. the motor formed by motor stator 14 and motor rotor 19 is preferably a 3 -phase brushless DC motor.
Power is preferably supplied to the windings 44, 46 of the motor stator 14 from an extracorporeal power source, e.g. a power supply package carried by the patient, through appropriate wiring 48 extending through a second lumen of the percutaneous tube 40, and into the motor housing 42 through a fluid-tight seal 49. The purge fluid supply connection 50 is preferably located outside the housing 42 to prevent accidental leakage of saline fluid into the motor housing 42.
Inasmuch as most of the heat developed in the operation of the motor is generated in the motor and conveyed by the stator iron, the motor is effectively cooled by the blood and therefore imposes little thermal load on the tissues in which it is implanted. For that reason, and also because of the relatively vibration-free operation of an axial flow pump, the pump 10 is physiologically much more tolerable than prior art devices.
Fig. 2 illustrates the disposition of the stator blades 22. It will be understood that although four stator blades are shown, the number of stator blades used will depend upon the circumstances of a particular design and is not part of this invention.
Fig. 3 shows an alternative embodiment of the device of this invention. In the embodiment of Fig. 3, the motor rotor is axially positioned within the pump stator housing 21, and the pump rotor portion axially outside the stator housing 21 merely carries the rotor blades.
In comparing the structures of Figs. 1 and 3, it should be noted that in the embodiment of Fig. 1 , where the motor rotor 19 is on the part of the pump rotor 18 which is cantilevered in the front of pump stator 20 (blood flows from right to left in
Figs. 1 and 3) and which is in direct contact with the blood, the rotational torque is transferred directly from the motor rotor to the rotor blades, and the bearings in the stator need only support the overhang load. On the other hand, the overhang bending moment is greater in the Fig. 1 embodiment because of the weight of the motor rotor and its distance from the bearings .
By contrast, the embodiment of Fig. 3 features a reduced overhang bending moment, and therefore imposes less load on the bearings. On the other hand, a significant clearance must be maintained in the configuration of Fig. 3 between the motor rotor 19 and the stator housing 21 to minimize fluid losses. This increases the magnetic gap between the motor stator and rotor, and the electromagnetic losses associated therewith. In the embodiment of Fig. 3, the structure of the pump 10 is the same as that described above in connection with Fig. 1, except that the motor rotor 20 is positioned at the left end of shaft 27 within the stator housing 21. This allows the overhanging rotor hub 23 to be made shorter, thus providing a better balance and imposing less of a bending moment on shaft 27.
The pump of this invention can be used in several different ways. In its preferred embodiment, the sources of purge fluid and electrical power for the motor may, as shown in Fig. 4, be a constant-volume fluid supply and delivery device 60 and a motor power supply 62 including a power source and the necessary electronics for controlling the motor. The devices 60 and 62 may be carried by the patient on an appropriate belt 64.

Claims

1. An implantable ventricular assist system for patients with chronic cardiac disease, comprising: a) a blood pump including a blood tube which forms post of a blood path within said patient; b) a pump stator mounted coaxially within said blood tube to form an annular blood duct within said tube, said pump stator being mounted within said blood tube by a plurality of stator blades; c) a pump rotor supported for rotation in said pump stator on hydrodynamic bearings; d) a permanent magnet motor rotor integral with said pump rotor; and e) a motor stator positioned on the outside of said blood tube; and f) whereby power transmission component creates any discontinuity in the wall of said blood path.
2. The system of Claim 1, farther comprising: g) means for supplying purge fluid to said bearings from the outside of said blood tube through one of said stator blades; h) whereby no purge fluid supply component creates any discontinuity in the wall of said blood path.
3. The system of Claim 1, in which the iron of said motor stator has a major surface in thermally conductive relation with the blood in said blood tube, whereby said motor stator is cooled by said blood.
4. An implantable chronic ventricular assist system, comprising: a) an axial flow pump including: i) a substantially cylindrical blood duct; ii) a substantially cylindrical pump stator, said pump stator including a plurality of stator blades, said stator blades being fixed to said blood tube and said pump stator so as to support said pump stator coaxially within said blood duct; iii) a pump rotor including a shaft journalled in said pump stator on hydrodynamic bearings so as to support said pump rotor coaxially within said blood tube, said pump rotor carrying a motor rotor and a plurality of rotor blades within said blood tube; iv) a sealed motor housing surrounding a portion of said blood tube, and v) a motor stator disposed within said housing; and b) means for supplying purge fluid to said bearings, and electrical power to said motor stator, said purge fluid supplying means including a purge fluid supply passage from the outside of said blood duct to the interior of said pump stator through one of said stator blades.
5. The system of Claim 4, in which said purge fluid is discharged into said blood tube at an interface between said pump stator and said pump rotor.
6. The system of Claim 5, in which the outside entrance to said supply passage is located outside said motor housing.
7. The system of Claim 4, in which said purge fluid supply means include i) an extracorporeal purge fluid source; ii) percutaneous fluid connection means connectable to said purge fluid source to convey purge fluid from said source into the patient's body; and iii) implanted purge fluid conduit means connected to said percutaneous fluid connection means and said supply passage for conveying purge fluid from said source to said pump stator.
8. The system of Claim 4, in which said electrical power supply means include implanted cabling means extending from an extracorporeal location to said pump, said cabling means entering said motor housing through a fluid-tight seal for connection to said motor stator.
9. The system of Claim 4, in which said purge fluid and power supply means include a single percutaneous conduit for percutaneously conveying both power and purge fluid.
10. The system of Claim 1, in which said motor rotor is positioned on a portion of said pump rotor which is in direct contact with the blood in said annular blood duct.
1 1 . The system of Claim 10, in which said pump rotor portion is cantilevered in front of said pump stator.
12. The system of Claim 1, in which said motor rotor is positioned on a portion of said pump rotor located inside said stator.
PCT/US1989/003385 1988-08-08 1989-08-07 Chronic ventricular assist system WO1990001347A1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US229,624 1988-08-08
US07/229,624 US4908012A (en) 1988-08-08 1988-08-08 Chronic ventricular assist system

Publications (1)

Publication Number Publication Date
WO1990001347A1 true WO1990001347A1 (en) 1990-02-22

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US (1) US4908012A (en)
AU (1) AU4062789A (en)
CA (1) CA1327677C (en)
WO (1) WO1990001347A1 (en)

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CN104379185A (en) * 2012-05-11 2015-02-25 海德威公司 Silver motor stator for implantable blood pump

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US4908012A (en) 1990-03-13
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