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EP1047462A2 - Hemopompe sans joint amelioree - Google Patents

Hemopompe sans joint amelioree

Info

Publication number
EP1047462A2
EP1047462A2 EP99901437A EP99901437A EP1047462A2 EP 1047462 A2 EP1047462 A2 EP 1047462A2 EP 99901437 A EP99901437 A EP 99901437A EP 99901437 A EP99901437 A EP 99901437A EP 1047462 A2 EP1047462 A2 EP 1047462A2
Authority
EP
European Patent Office
Prior art keywords
pump
housing
rotor
blood pump
magnetic bearings
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.)
Withdrawn
Application number
EP99901437A
Other languages
German (de)
English (en)
Inventor
Enrique J. Klein
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.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Publication of EP1047462A2 publication Critical patent/EP1047462A2/fr
Withdrawn legal-status Critical Current

Links

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
    • A61M60/82—Magnetic 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
    • A61M60/226—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 radial components
    • A61M60/232—Centrifugal 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
    • A61M60/40—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
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/562—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow
    • 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
    • A61M60/81—Pump housings
    • 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

  • the present invention relates generally to medical devices and methods. More particularly, the present invention relates to an implantable blood pump having a sealless fully magnetically suspended rotor.
  • a sealless centrifugal blood pump is described in published PCT application WO 97/29795 and U.S. Patent No. 5,695,471.
  • the pump is driven by an electric motor and incorporates radial magnetic bearings and stationary axial thrust bearings having contacting surfaces with the shaft or rotor.
  • the purpose of the pump is to provide a left ventricular assist device operating over extended periods of time for the treatment of congestive heart failure.
  • the shaft with the radial magnetic bearings, carrying the cantilevered pump impeller and motor/rotor combination may become misaligned (angled) causing problems with the motor gap(s).
  • the second case there would be constant contact between the shaft end(s) and the axial bearing(s), potentially giving rise to additional thrombus formation and hemolysis.
  • Combination of an axial motor with a centrifugal pump imposes some additional constraints on the optimum design of both. Compromises are mainly due to the small width of the motor gap(s), needed for improved efficiency, and the need to provide magnetic components as well as flat motor-pump impeller combination.
  • the present invention is an improved design for a sealless rotary blood pump.
  • the design separates the motor from the hydraulic impeller, where the motor is of the coaxial and/or concentric stator and rotor type and is preferably located in the left ventricle while the impeller which is mounted on the same shaft, remains external to the heart.
  • the support of the shaft carrying the rotor and the pump impeller has been improved by using a combination of magnetical cylindrical and conical end bearings that can suspend the shaft in a floating configuration.
  • the pump impeller includes a combination of axial and radial vanes to improve performance.
  • the motor is suspended by bearings at each end and is not cantilevered.
  • the impeller is cantilevered relative to bearings.
  • the blood flow into the pump is divided in two paths in order to provide a large entry duct for the primary path and a smaller secondary flow path through the decreased motor gap to optimize the motor design.
  • a hollow shaft or an external intake are used for the primary blood path.
  • the shape of the pump casing has been further improved to fit within the apex of the heart.
  • Pulsatile flow can be achieved by varying the angular velocity of the rotor shaft, at a preferred frequency of from 0.5 Hz to 1.5 Hz, more preferably from 1 Hz to 1.3 Hz.
  • the direction (sense) of rotation of the pump can be chosen so that the reaction torque of the heart to which the pump is attached mimics the pulsatile torque of a normal heart. Additionally, the sound of a pulsatile flow rotary pump would likely be less objectionable than the sound of a continuously operating pump.
  • Fig. 1 illustrates a first embodiment of a sealless blood pump constructed in accordance with the principles of the present invention.
  • Figs. 2A and 2B illustrate the magnetic bearing utilized in the pump of Fig. 1.
  • Fig. 3 is an external perspective view of the blood pump of Fig. 1.
  • Fig. 4 illustrates an alternative magnetic bearing.
  • Fig. 5 illustrates an alternative blood pump constructed in accordance with the principles of the present invention.
  • Fig. 6 is a schematic illustration of a gating system for achieving pulsatile flow.
  • Fig. 7 illustrates certain flow characteristics of the pulsatile flow blood pump.
  • FIG. 1 A blood pump according to present invention is illustrated in Fig. 1.
  • the blood pump incorporates a brushless radial motor 1 flanked by modified magnetic bearings 2 having lateral ferromagnetic pole pieces 3 that provide for balanced axial constraint.
  • a primary blood flow path is through an eccentric intake nozzle 4, and a hydraulic impeller 5 may be of the thick web type or may be a modified Kaplan turbine- type pump impeller, having both axial and radial flow components, as shown.
  • the intake nozzle 4 is preferably provided with a large cross-section and a short length, e.g. just longer than the muscle thickness of the apex of the heart, in order to reduce the hydraulic losses of the intake flow when compared to the annular path along the radial magnetic bearings of the prior art. Since the primary blood flow is through intake nozzle 4, radial gap 4a between the rotor and stator for both the motor and the radial magnetic bearings, may be substantially reduced when compared to the prior art. This design improves the magnetic efficiency and allows for a more compact design. Decreasing the size of the radial gap will also improve the stiffness of the radial bearing making the device less susceptible to shock and vibration while minimally impacting hemolysis or thrombus formation in the gap.
  • the radial annular gap 4a provides a secondary parallel blood flow path for the pump.
  • the cross sectional area of this decreased annular gap will have a much reduced blood flow capacity both due to the reduced cross sectional area of the smaller annulus and due to the greater effect of the boundary layers.
  • gap 4a mainly allows for the design of a floating rotor with no contacting surfaces between the rotor magnetic bearings or the shaft, against any of the stationary components of the pump for all operating conditions.
  • the magnetic bearings 2 may be similar to those described in U.S. Patent
  • the disks 2a in Fig. 1 are axially magnetized permanent magnets assembled next to pole pieces, with equal poles facing each other resulting in a flux pattern wherein the poles of the stator and the rotor repel each other.
  • the inner pole pieces on each side of the motor also provide magnetic shielding so that the magnetic bearing flux will not significantly interfere with the magnetic motor flux.
  • FIG. 2A shows one bearing cell with the modified lateral pole pieces 2b.
  • the pole pieces Pi and P are both shown as magnetic South poles and will repel each other with a force F a which has a radial component F r (Fig.
  • the cross-section of the outer end pole piece is shown with more material toward the outer end, and the gap is shown with a slight conical angle mismatch to even out the flux repulsion across the gap.
  • An alternate axial bearing design is shown hereinafter.
  • an intake nozzle 4b need not be axisymmetric. It may also be preferably oriented toward the free wall of the left ventricle.
  • Another feature of the present device is that it permits forming a "waist" or annular constriction in radially narrowed region 6a in the main housing to provide improved anchoring in the muscle at the apex of the heart.
  • the base of the impeller housing may better conform to the shape of the apex of the heart.
  • loops or anchors will be provided in the housing (not shown) to permit suturing to hold the pump in place.
  • the hydraulic impeller design is no longer constrained by the need to serve also as the rotor of a flat motor as in the prior art.
  • impellers such as a ship's screw rotor or a modified Kaplan turbine-type impeller having both axial and radial flow, while still inside a centrifugal pump housing.
  • Such designs would have less surface exposed to the blood than the thick web impeller of the prior art.
  • hemostasis should become a problem between the end of the impeller shaft and the secondary housing 6, it is possible to drill one or more holes in the impeller to provide leakage paths 7 for the blood. While this would minimally decrease pumping efficiency, it may be an advantageous compromise.
  • titanium will be used for all housings because of its high strength and low weight, as well as its natural damping characteristics and biocompatibility.
  • the principal housing 8, secondary housing 6, and end cap 9 can all be formed from titanium by investment casting and machining, or in the case of end cap 9, by machining from stock.
  • the permanent magnets 10 can be made of a high energy rare earth, such as iron-neodymium or samarium-cobalt. Pole pieces can be made from pure or very low-carbon iron and then plated or coated to inhibit corrosion and enhance biocompatibility.
  • the blood pump can be assembled in stages as follows.
  • the stator (motor and magnetic bearings) could be installed in the principal housing 8, all except for pole piece 3 which is pre-assembled within cap 9.
  • the impeller and shaft is then introduced in the stator assembly and the motor and bearing portions of the rotor are assembled onto the impeller shaft.
  • the end cap subassembly (components 9 and 3) is then assembled onto the principal housing 8.
  • the secondary housing 6 is assembled onto the principle housing, to complete the construction. All joints should be permanent and preferably done with press fits and adhesives in a manner similar to assembly techniques used in the disk drive motor industry.
  • the implantable device will usually be coated with an anti- thrombotic coating.
  • FIG. 4 an alternate magnetic bearings design is illustrated.
  • the bearing cell in Fig. 4 differs from that in Fig. 2A by the addition of an annular permanent magnet 22 and annular end pole 20 which jointly may augment the axial repulsion forces between angled pole pieces 24 in the static and the rotating portions of the pump.
  • the actual forces can be verified first analytically by using magnetic Finite Element Analysis (FEA) and then experimentally.
  • FEA magnetic Finite Element Analysis
  • a similar arrangement with added permanent magnet and pole piece is used at the opposite end of the magnetic bearing (not shown) to balance the axial forces.
  • An alternative implantable pump design is illustrated in Fig. 5 (where like components are numbered the same as in Fig. 1).
  • This design incorporates many of the features of the previously described pump, but differs in that a primary blood flow path 30 is routed to the impeller 5 through a hollow shaft 11, thus eliminated the need for a separate entry nozzle 4 or 4b as shown in Figs. 1 and 3.
  • This embodiment takes advantage of the shaft 11 and the entire rotor assembly being truly floating (i.e., having no physical contact during rotation). It is furthermore advantageous because the efficiency of the motor is minimally impacted by the loss of magnetic material in the center of the rotor. Such a design could not be implemented in a configuration incorporating axial contacting bearings acting on a shaft as taught by the prior art.
  • the centrifugal pumps of the present invention can be modified to operate so as to provide pulsatile blood flow into the aorta, which may be clinically advantageous in certain respects.
  • pulsatile flow more closely matches or mimics the natural cycle of a beating heart.
  • rotary pumps as proposed in the prior art and including temporary pumps placed in the aorta, are normally associated with continuous (non-pulsatile) flow.
  • Pulsatile flow can be achieved with a rotary pump, however, by varying the rotational speed, preferably at a frequency between 0.5 Hz to 1.5 Hz, more preferably at 1 Hz and 1.3 Hz, which corresponds to heart rates in the range from 30 to 90 and 60 to 80 beats per minute, respectively.
  • the frequency of rotational pulsatility can be gated to the output of the coronary sinus node through the use of appropriate sensors.
  • a modified pacemaker can be used to gate or pace the pump through pacemaker leads as shown schematically in Fig. 6.
  • the pulsatile cycle of the rotary pump will be triggered a fraction of a second ahead of the ventricles in order to best synchronize the output of the pump into the aorta with the pulsation of the ventricles since the acceleration of the rotary pump may be slower than the contraction of the ventricles.
  • it may not be practical to exactly match the pulsatile flow rate of a normal heart with an electrically controlled rotary pump it may be possible to approximate the average flow rate when using a pacemaker as shown in Fig. 6 together with the appropriate pump motor drivers.
  • the aortic flow velocity and the volume stroke in a healthy heart is depicted by a solid line.
  • the peak flow rate may be increased, as shown in a broken line 40, or the delivery cycle may be lengthened, as shown in the broken line 42, or some combination of both as shown in the broken line 44.
  • the objective will be to mimic the stroke volume per cycle, i.e., the area under the curves as illustrated in Fig. 7.
  • Another advantage to gating the rotary pump with a pacemaker if the pacemaker is a rate-responsive device, is that the pacemaker in combination with the pump motor drivers can control the actual cardiac output through separate sets of algorithms. Such rate- responsive pacemakers are currently made to control heart rate only.
  • a normal heart contracts and expands with every cycle, and also twists around an axis running approximately through the apex and the root of the aorta.
  • Such periodic twisting motion would be partly mimicked by a left ventricular assist device having a rotary pump with a shaft aligned with the axis of the heart and controlled to deliver pulsatile flow.
  • the housing which is tied into the apex of the heart, experiences a reaction torque which is transmitted to the heart. This reaction is opposite to the shaft sense of rotation.
  • the sound of a pulsatile rotary pump may also be less objectionable to a patient than the constant hum of the constant velocity pump, particularly if the pulsatile action mimics the normal heartbeat.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Anesthesiology (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Structures Of Non-Positive Displacement Pumps (AREA)

Abstract

L'invention porte sur une hémopompe rotative sans joint implantable présentant plusieurs caractéristiques qui en améliorent le fonctionnement par rapport à la technique antérieure, dont notamment: un arbre entièrement flottant sur paliers magnétiques afin d'éviter la formation de thrombus, un double cheminement du sang améliorant le rendement du moteur, un moteur sans collecteur placé dans le ventricule gauche indépendamment de l'impulseur, un impulseur à flux axial/radial monté sur l'axe du moteur et placé dans une partie du boîtier extérieure au coeur, et des moyens permettant de pulser le flux sortant de la pompe.
EP99901437A 1998-01-12 1999-01-11 Hemopompe sans joint amelioree Withdrawn EP1047462A2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US7112398P 1998-01-12 1998-01-12
US71123P 1998-01-12
PCT/US1999/000636 WO1999034847A2 (fr) 1998-01-12 1999-01-11 Hemopompe sans joint amelioree

Publications (1)

Publication Number Publication Date
EP1047462A2 true EP1047462A2 (fr) 2000-11-02

Family

ID=22099375

Family Applications (1)

Application Number Title Priority Date Filing Date
EP99901437A Withdrawn EP1047462A2 (fr) 1998-01-12 1999-01-11 Hemopompe sans joint amelioree

Country Status (3)

Country Link
EP (1) EP1047462A2 (fr)
JP (1) JP2002512821A (fr)
WO (1) WO1999034847A2 (fr)

Families Citing this family (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA2374989A1 (fr) * 2002-03-08 2003-09-08 Andre Garon Dispositif d'assistance ventriculaire comprenant une pompe a sang hybride a double entree
DE50308717D1 (de) * 2002-06-21 2008-01-17 Helmut Mueckter Blutpumpe mit einem Impeller
KR20080016863A (ko) 2005-05-17 2008-02-22 페더럴-모걸 코오포레이숀 Ｂｌｄｃ 모터 및 캡슐화된 회로 보드를 가진 펌프어셈블리
KR101621486B1 (ko) * 2008-02-08 2016-05-16 하트웨어, 인코포레이티드 심실내 배치용 심실보조장치
FR2955499B1 (fr) 2010-01-28 2013-06-14 Fineheart " pompe cardiaque autonome, et procede mis en oeuvre dans une telle pompe".
US9731057B2 (en) 2011-07-28 2017-08-15 Fineheart Removable heart pump, and method implemented in such a pump
US9597205B2 (en) 2012-06-06 2017-03-21 Magenta Medical Ltd. Prosthetic renal valve
US10583231B2 (en) 2013-03-13 2020-03-10 Magenta Medical Ltd. Blood pump
EP2967361B1 (fr) 2013-03-13 2019-12-18 Magenta Medical Ltd. Pompe rénale
US10111994B2 (en) 2013-05-14 2018-10-30 Heartware, Inc. Blood pump with separate mixed-flow and axial-flow impeller stages and multi-stage stators
US9764113B2 (en) 2013-12-11 2017-09-19 Magenta Medical Ltd Curved catheter
US11291824B2 (en) 2015-05-18 2022-04-05 Magenta Medical Ltd. Blood pump
US11039915B2 (en) 2016-09-29 2021-06-22 Magenta Medical Ltd. Blood vessel tube
EP3532120B1 (fr) 2016-10-25 2024-05-01 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
AU2017364359B2 (en) 2016-11-23 2022-12-01 Magenta Medical Ltd. Blood pumps
US10905808B2 (en) 2018-01-10 2021-02-02 Magenta Medical Ltd. Drive cable for use with a blood pump
EP3854444B1 (fr) 2018-01-10 2024-09-18 Magenta Medical Ltd. Élément d'extrémité distale pour pompe à sang
US10893927B2 (en) 2018-03-29 2021-01-19 Magenta Medical Ltd. Inferior vena cava blood-flow implant
EP3858422B1 (fr) 2019-01-24 2022-11-02 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
JP7216206B2 (ja) * 2019-03-25 2023-01-31 ボストン サイエンティフィック サイムド，インコーポレイテッド 腐食防止機構付き機械的循環補助ポンプドライブ
CN114040794A (zh) 2019-05-23 2022-02-11 马真塔医药有限公司 血液泵
EP3984589B1 (fr) 2020-04-07 2023-08-23 Magenta Medical Ltd. Détection de phase magnétique

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US4688998A (en) * 1981-03-18 1987-08-25 Olsen Don B Magnetically suspended and rotated impellor pump apparatus and method
US4994078A (en) * 1988-02-17 1991-02-19 Jarvik Robert K Intraventricular artificial hearts and methods of their surgical implantation and use
US5470208A (en) * 1990-10-05 1995-11-28 Kletschka; Harold D. Fluid pump with magnetically levitated impeller
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Also Published As

Publication number Publication date
WO1999034847A3 (fr) 1999-12-09
WO1999034847A2 (fr) 1999-07-15
JP2002512821A (ja) 2002-05-08

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