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WO1998000185A1 - Blood pump according to the rotary pump principle - Google Patents

Blood pump according to the rotary pump principle Download PDF

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Publication number
WO1998000185A1
WO1998000185A1 PCT/EP1997/002903 EP9702903W WO9800185A1 WO 1998000185 A1 WO1998000185 A1 WO 1998000185A1 EP 9702903 W EP9702903 W EP 9702903W WO 9800185 A1 WO9800185 A1 WO 9800185A1
Authority
WO
WIPO (PCT)
Prior art keywords
pump
blood
channel
bearing
pump wheel
Prior art date
Application number
PCT/EP1997/002903
Other languages
German (de)
French (fr)
Inventor
Günter RAU
Helmut Reul
Thorsten Siess
Rolf Eilers
Original Assignee
Rau Guenter
Helmut Reul
Thorsten Siess
Rolf Eilers
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 Rau Guenter, Helmut Reul, Thorsten Siess, Rolf Eilers filed Critical Rau Guenter
Publication of WO1998000185A1 publication Critical patent/WO1998000185A1/en

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
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/419—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being permanent magnetic, e.g. from a rotating magnetic coupling between driving and driven magnets
    • 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
    • A61M60/221—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
    • A61M60/20—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
    • A61M60/20—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
    • A61M60/80—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
    • A61M60/812—Vanes or blades, e.g. static flow guides
    • 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
    • A61M60/825—Contact bearings, e.g. ball-and-cup or pivot 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
    • A61M60/126—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 invention relates to a blood pump based on the rotation principle, that is, a blood pump with a rotating pump wheel.
  • Blood pumps generally have the problem of thrombus formation due to agglomeration of blood particles. This problem also exists with blood pumps based on the rotation principle, in particular in the area of the pump wheel, when there are narrow gaps in which dead water formation can occur.
  • the invention has for its object to provide a blood pump according to the rotary pump principle, in which the risk of thrombus formation in the area of the pump wheel is largely avoided.
  • the pump wheel has an axial channel which hydraulically connects the suction side of the pump wheel with its rear side. This allows blood to get into the rear gap of the pump wheel and rinse it. Due to the pressure difference between the pressure and suction side of the pump wheel, all unshoved surfaces of the pump wheel are washed around.
  • the pump wheel is provided on its rear side facing away from the inflow side with radially promoting auxiliary blades. These auxiliary blades cause an increased active flow through the axial channel and the rear of the pump wheel in the main flow direction. This creates a bypass flow, which is then fed back to the main flow.
  • a second flow path is provided through the pump wheel.
  • This second flow path which is a purge path close to the axis, is flowed through either in countercurrent to the main flow if no auxiliary blading is present, or as a bypass in the same flow direction as the main flow. In any case, dead water areas on the back of the paddle wheel are effectively avoided.
  • the invention is applicable to any form of rotary pump, e.g. Axial pumps, radial pumps and diagonal pumps.
  • Fig. 1 shows a longitudinal section through an embodiment of the blood pump.
  • the blood pump BP according to FIG. 1 has an elongated, tubular pump housing 10 which is provided with an inlet part 11 at one end.
  • the inlet part 11 has an inlet 12, the inner diameter of which is smaller than the inner diameter of the pump housing 10.
  • an annular transition part 13 is formed, which is designed in an arc shape and in an S-shaped curvature from the diameter of the inlet 12 to the inner diameter the pump housing 10 smoothly and smoothly transferred.
  • the motor housing 15 of a motor 16, which is an electric motor, is coaxially fastened in the pump housing 10.
  • the motor housing is completely sealed.
  • a pump wheel 22 is arranged in the inlet part 11 of the pump housing 10. This consists of a hub 23 from which blades 24 protrude.
  • the pump wheel 22 is driven by the motor 16 via a magnetic coupling, which can be designed as a front rotary coupling 25 or a central rotary coupling.
  • This has a first coupling part 25a, which is connected to the rotor of the motor 16 and is encapsulated in the interior of the motor housing 15, and a second coupling part 25b, which is arranged in the hub 23 of the pump wheel 22.
  • Both coupling parts 25a, 25b have magnets 28, which cause the second coupling part 25b to rotate when the first coupling part 25a rotates.
  • the motor housing 15 is closed with a non-magnetic, non-conductive cap 26, on which a combined axial / radial bearing 27 is supported in the form of a ball.
  • This bearing 27 in turn supports the hub of the impeller 22.
  • the magnets 28 of the front rotary coupling 25 generate an axial holding force which is greater than the reaction force generated when the impeller 22 is rotated, so that the impeller 22 is pulled towards the motor 16 by the magnetic force and is pressed against the bearing 27.
  • the axial holding force of the coupling 25 is compensated centrally on the cap 26 by a further axial bearing support 25d in connection with the bearing 27, so that neither the bearing of the motor 26 nor the thin cap 26 this force in its peripheral wall 26b and on the end face 26a have to record.
  • an arm star 29 is fastened in the inlet 12.
  • the hub 23 also contains an axial flushing channel 32, which leads to the bearing 27. The leakage flow through the flushing channel 32 causes the gap 25c between the axis 60 and the pump wheel 22 to be continuously flushed in order to avoid thrombus formation.
  • the guide vanes 24 of the pump wheel 22 have an outer diameter at the inflow end 24a which corresponds essentially to the diameter of the inlet 12, so that the pump wheel here covers the entire diameter of the inlet channel. Following the inlet edges 24a there is a concave-arc around order area 24b, which follows the transition part 13 of the pump housing at a short distance. Subsequently, the pump blades 24 have a region 24c, the diameter of which is approximately as large as the outer diameter of the motor housing 15 at the end which faces the pump wheel 22. The outer diameter of the diagonal pump blades 24 is made as large as the overall diameter of the transition part 13 allows.
  • annular channel 35 which extends in the longitudinal direction.
  • This ring channel 35 is designed as a diffuser in that its cross-sectional area increases from the inlet to the outlet. This causes a slowdown in blood flow and thus an increase in pressure.
  • the cross-sectional area of the ring channel 35 is widened by correspondingly changing the wall thicknesses of the pump housing 10 and motor housing 15.
  • the motor 16 causes the pump wheel 22 to rotate, the paddle wheels 24 of which are screw-shaped. As a result, blood is sucked axially from the suction side 40 and conveyed to the pressure side 41 and from there and with a rotating peripheral component into the annular channel 25.
  • the impeller 22 is provided with an axle 60 which at one end in the bearing 27 of the cap 26 closing the motor housing 15 and at the other end in the Arm star 29 is mounted via a radial bearing 63.
  • the annular longitudinal channel 32 of the hub 23 is bridged by webs 61 which hold the hub 23 on the axis 60.
  • auxiliary blades 62 At the end of the hub 23 facing the motor there are auxiliary blades 62 which pump the liquid flowing in through the longitudinal channel 32 radially outwards and feed them to the main flow generated by the pump blades 24.
  • the auxiliary blades ensure that the gap between the impeller 22 and the motor housing 15 is continuously flowed through, so that thrombi cannot form there.
  • the longitudinal channel 32 is dimensioned such that the blood flow passing through it is significantly less than the main flow generated by the pump blades 24.
  • the bearings 27 and 63 are arranged such that they are at a sufficient distance from the channel 32. Although the transition between the stationary and the rotating part of the bearings 27 and 63 is integral - without a large abutting edge - on which thrombi could attach, it must be assumed that small ring thrombi may form at the transition point. If these do not close the channel 32 at a corresponding distance, then a degressive thrombus growth can be achieved due to adequate flushing with a ultimately stable size.

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

The blood pump has a channel (32) running centrally through the impeller (22) connecting the rear side of the impeller (22) with the suction side (40). Blood is continually pumped through the channel (32) so that no dead water areas can form in unbladed areas of the impeller (22). The rear side of the impeller (22) is fitted with auxiliary blades (62) which produce a current parallel to the main current.

Description

Blutpumpe nach dem Rotationspumpenprinzip Blood pump based on the rotary pump principle
Die Erfindung betrifft eine Blutpumpe nach dem Rotationsprinzip, also eine Blutpumpe mit einem rotierenden Pumpenrad.The invention relates to a blood pump based on the rotation principle, that is, a blood pump with a rotating pump wheel.
Bei Blutpumpen besteht generell das Problem der Thrombenbildung durch Agglomeration von Blutteilchen. Dieses Problem besteht auch bei Blutpumpen nach dem Rotationsprinzip, insbesondere im Bereich des Pumpenrades, wenn dort enge Spalte sind, in denen Totwasserbildung auftreten kann.Blood pumps generally have the problem of thrombus formation due to agglomeration of blood particles. This problem also exists with blood pumps based on the rotation principle, in particular in the area of the pump wheel, when there are narrow gaps in which dead water formation can occur.
Der Erfindung liegt die Aufgabe zugrunde, eine Blut- pumpe nach dem Rotationspumpenprinzip zu schaffen, bei der die Gefahr von Thrombenbildung im Bereich des Pumpenrades weitgehend vermieden wird.The invention has for its object to provide a blood pump according to the rotary pump principle, in which the risk of thrombus formation in the area of the pump wheel is largely avoided.
Die Lösung dieser Aufgabe erfolgt erfindungsgemäß mit den im Patentanspruch 1 angegebenen Merkmalen. Bei der erfindungsgemäßen Blutpumpe weist das Pumpenrad einen axialen Kanal auf, der die Saugseite des Pumpenrades mit dessen Rückseite hydraulisch verbindet. So kann Blut in den rückseitigen Spalt des Pumpenrades gelangen und diesen spülen. Durch die Druckdifferenz zwischen Druck- und Saugseite des Pumpenrades erfolgt somit eine Umspülung aller ungeschaufelten Flächen des Pumpenrades .This object is achieved according to the invention with the features specified in claim 1. In the blood pump according to the invention, the pump wheel has an axial channel which hydraulically connects the suction side of the pump wheel with its rear side. This allows blood to get into the rear gap of the pump wheel and rinse it. Due to the pressure difference between the pressure and suction side of the pump wheel, all unshoved surfaces of the pump wheel are washed around.
Gemäß einer bevorzugten Weiterbildung der Erfindung ist das Pumpenrad auf seine der Anströmseite abgewandten Rückseite mit radialfördernden Hilfsschaufeln versehen. Diese Hilfsschaufeln bewirken eine verstärkte aktive Durchströmung des axialen Kanals und der Rückseite des Pumpenrades in Hauptströmungsrichtung. Dadurch wird ein Bypaßstrom erzeugt, der anschließend der Hauptströmung wieder zugeführt wird.According to a preferred development of the invention, the pump wheel is provided on its rear side facing away from the inflow side with radially promoting auxiliary blades. These auxiliary blades cause an increased active flow through the axial channel and the rear of the pump wheel in the main flow direction. This creates a bypass flow, which is then fed back to the main flow.
Bei der erfindungsgemäßen Blutpumpe ist ein zweiter Strömungsweg durch das Pumpenrad hindurch vorgesehen. Dieser zweite Strömungsweg, bei dem es sich um einen achsnahen reinen Spülweg handelt, wird entweder im Gegenstrom zum Haup ström durchströmt, wenn keine Hilfsbeschaufelung vorhanden ist, oder als Bypaß in gleicher Strömungsrichtung wie der Hauptstrom. In jedem Fall werden Totwasserbereiche an der Rückseite des Schaufelrades wirksam vermieden.In the blood pump according to the invention, a second flow path is provided through the pump wheel. This second flow path, which is a purge path close to the axis, is flowed through either in countercurrent to the main flow if no auxiliary blading is present, or as a bypass in the same flow direction as the main flow. In any case, dead water areas on the back of the paddle wheel are effectively avoided.
Die Erfindung ist bei jeder Form von Rotationspumpen verwendbar, wie z.B. Axialpumpen, Radialpumpen und Diagonalpumpen.The invention is applicable to any form of rotary pump, e.g. Axial pumps, radial pumps and diagonal pumps.
Im folgenden wird unter Bezugnahme auf die Zeichnung ein Ausführungsbeispiel der Erfindung näher erläutert. Es zeigt :In the following an embodiment of the invention will be explained with reference to the drawing. It shows :
Fig. 1 einen Längsschnitt durch eine Ausfuhrungsform der Blutpumpe .Fig. 1 shows a longitudinal section through an embodiment of the blood pump.
Die Blutpumpe BP nach Fig. 1 weist ein langgestrecktes, rohrförmiges Pumpengehäuse 10 auf, das an einem Ende mit einem Einlaßteil 11 versehen ist. Der Einlaßteil 11 weist einen Einlaß 12 auf, dessen Innendurchmesser kleiner ist als der Innendurchmesser des Pumpengehäuses 10. Im Einlaßteil 11 ist ein ringförmiger Übergangsteil 13 ausgebildet, der bogenförmig gestaltet ist und in einer S-förmigen Krümmung von dem Durchmesser des Einlasses 12 auf den Innendurchmesser des Pumpengehäuses 10 glatt und knickfrei überleitet.The blood pump BP according to FIG. 1 has an elongated, tubular pump housing 10 which is provided with an inlet part 11 at one end. The inlet part 11 has an inlet 12, the inner diameter of which is smaller than the inner diameter of the pump housing 10. In the inlet part 11 an annular transition part 13 is formed, which is designed in an arc shape and in an S-shaped curvature from the diameter of the inlet 12 to the inner diameter the pump housing 10 smoothly and smoothly transferred.
In dem Pumpengehäuse 10 ist koaxial das Motorgehäuse 15 eines Motors 16 befestigt, bei dem es sich um einen Elektromotor handelt. Das Motorgehäuse ist vollständig abgedichtet .The motor housing 15 of a motor 16, which is an electric motor, is coaxially fastened in the pump housing 10. The motor housing is completely sealed.
In dem Einlaßteil 11 des Pumpengehäuses 10 ist ein Pumpenrad 22 angeordnet. Dieses besteht aus einer Nabe 23, von der Schaufeln 24 abstehen. Der Antrieb des Pumpenrades 22 erfolgt von dem Motor 16 über eine magnetische Kupplung, die als Stirndrehkupplung 25 oder Zentral - drehkupplung ausgebildet sein kann. Diese weist ein erstes Kupplungsteil 25a auf, das mit dem Rotor des Motors 16 verbunden und im Innern des Motorgehäuses 15 gekapselt angeordnet ist, und ein zweites Kupplungteil 25b, das in der Nabe 23 des Pumpenrades 22 angeordnet ist. Beide Kupplungsteile 25a, 25b haben Magnete 28, die bewirken, daß bei einer Drehung des erstes Kupplungs- teils 25a das zweite Kupplungsteil 25b mitdreht. Das Motorgehäuse 15 ist mit einer amagnetischen nichtleitenden Kappe 26 verschlossen, an welcher ein kombiniertes Axial/Radiallager 27 in Form einer Kugel abgestützt ist. Dieses Lager 27 stützt seinerseits die Nabe des Pumpenrades 22 ab. Die Magnete 28 der Stirndrehkupplung 25 erzeugen eine axiale Haltekraft, die größer ist als die beim Drehen des Pumpenrades 22 erzeugte Reaktionskraft, so daß das Pumpenrad 22 durch die Magnetkraft in Richtung auf den Motor 16 gezogen und gegen das Lager 27 gedrückt wird. Die axiale Haltekraft der Kupplung 25 wird zentral auf der Kappe 26 durch eine weitere axiale Lagerabstützung 25d in Verbindung mit dem Lager 27 kompensiert, so daß weder die Lager des Motors 26 noch die dünne Kappe 26 diese Kraft in ihrer Umfangswand 26b und auf der Stirnfläche 26a aufnehmen müssen.A pump wheel 22 is arranged in the inlet part 11 of the pump housing 10. This consists of a hub 23 from which blades 24 protrude. The pump wheel 22 is driven by the motor 16 via a magnetic coupling, which can be designed as a front rotary coupling 25 or a central rotary coupling. This has a first coupling part 25a, which is connected to the rotor of the motor 16 and is encapsulated in the interior of the motor housing 15, and a second coupling part 25b, which is arranged in the hub 23 of the pump wheel 22. Both coupling parts 25a, 25b have magnets 28, which cause the second coupling part 25b to rotate when the first coupling part 25a rotates. The motor housing 15 is closed with a non-magnetic, non-conductive cap 26, on which a combined axial / radial bearing 27 is supported in the form of a ball. This bearing 27 in turn supports the hub of the impeller 22. The magnets 28 of the front rotary coupling 25 generate an axial holding force which is greater than the reaction force generated when the impeller 22 is rotated, so that the impeller 22 is pulled towards the motor 16 by the magnetic force and is pressed against the bearing 27. The axial holding force of the coupling 25 is compensated centrally on the cap 26 by a further axial bearing support 25d in connection with the bearing 27, so that neither the bearing of the motor 26 nor the thin cap 26 this force in its peripheral wall 26b and on the end face 26a have to record.
Zur Zentrierung des Pumpenrades 22 auf der Einlaßseite ist in dem Einlaß 12 ein Armstern 29 befestigt. An dem Armstern 29 befindet sich ein zentrisches Kopfstück 31, das den Lagerzapfen 60 umgibt und die axial einströmende Strömung geringfügig radial in Richtung der Nabe 23 ableitet. Ferner enthält die Nabe 23 einen axialen Spülkanal 32, der zum Lager 27 führt. Der Leckagestrom durch den Spülkanal 32 bewirkt eine ständige Umspülung des Spaltes 25c zwischen der Achse 60 und dem Pumpenrad 22, um Thrombenbildung zu vermeiden.To center the pump wheel 22 on the inlet side, an arm star 29 is fastened in the inlet 12. There is a central head piece 31 on the arm star 29, which surrounds the bearing journal 60 and derives the axially inflowing flow slightly radially in the direction of the hub 23. The hub 23 also contains an axial flushing channel 32, which leads to the bearing 27. The leakage flow through the flushing channel 32 causes the gap 25c between the axis 60 and the pump wheel 22 to be continuously flushed in order to avoid thrombus formation.
Die Leitschaufeln 24 des Pumpenrades 22 haben an dem Anströmende 24a einen Außendurchmesser, der im wesentlichen dem Durchmesser des Einlasses 12 entspricht, so daß das Pumpenrad hier den gesamten Durchmesser des Einlaßkanals erfaßt. Im Anschluß an die Einlaßkanten 24a erfolgt ein konkav-bogenförmiger Um angsbereich 24b, der dem Übergangsteil 13 des Pumpengehäuses mit geringem Abstand folgt. Daran anschließend haben die Pumpenschaufeln 24 einen Bereich 24c, dessen Durchmesser etwa so groß ist wie der Außendurchmesser des Motorgehäuses 15 an demjenigen Ende, das dem Pumpenrad 22 zugewandt ist. Der Außendurchmesser der diagonalen Pumpenschaufeln 24 wird so groß ausgeführt, wie es der Gesamtdurchmesser des Übergangsteils 13 erlaubt. Hierdurch kann die erforderliche, hydraulische Leistung bei einer vergleichsweisen geringen Drehzahl (beispielhaf n≡=7000U/min für V/t=5l/min und ΔP≤lOOmmHg) erzielt werden, was die Standzeiten der lagernden Komponenten der Pumpe erhöht .The guide vanes 24 of the pump wheel 22 have an outer diameter at the inflow end 24a which corresponds essentially to the diameter of the inlet 12, so that the pump wheel here covers the entire diameter of the inlet channel. Following the inlet edges 24a there is a concave-arc around order area 24b, which follows the transition part 13 of the pump housing at a short distance. Subsequently, the pump blades 24 have a region 24c, the diameter of which is approximately as large as the outer diameter of the motor housing 15 at the end which faces the pump wheel 22. The outer diameter of the diagonal pump blades 24 is made as large as the overall diameter of the transition part 13 allows. As a result, the required hydraulic power can be achieved at a comparatively low speed (for example, n≡ = 7000rpm for V / t = 5l / min and ΔP≤lOOmmHg), which increases the service life of the bearing components of the pump.
Zwischen dem Pumpengehäuse 10 und dem Motorgehäuse 15 besteht ein Ringkanal 35, der sich in Längsrichtung erstreckt. Dieser Ringkanal 35 ist als Diffusor ausgebildet, indem sich seine Querschnittsfläche vom Einlaß zum Auslaß vergrößert. Dadurch entsteht eine Verlangsamung des Blutflusses und somit eine Druckerhöhung. Die Erweiterung der Querschnittsfläche des Ringkanals 35 wird durch entsprechende Veränderung der Wandstärken von Pumpengehäuse 10 und Motorgehäuse 15 erreicht .Between the pump housing 10 and the motor housing 15 there is an annular channel 35 which extends in the longitudinal direction. This ring channel 35 is designed as a diffuser in that its cross-sectional area increases from the inlet to the outlet. This causes a slowdown in blood flow and thus an increase in pressure. The cross-sectional area of the ring channel 35 is widened by correspondingly changing the wall thicknesses of the pump housing 10 and motor housing 15.
Der Motor 16 bewirkt eine Rotation des Pumpenrades 22, dessen Schaufelräder 24 schrauben örmig gestaltet sind. Dadurch wird Blut von der Saugseite 40 axial angesaugt und zur Druckseite 41 und von dort und mit einer rotierenden Umfangskomponente in den Ringkanal 25 gefördert.The motor 16 causes the pump wheel 22 to rotate, the paddle wheels 24 of which are screw-shaped. As a result, blood is sucked axially from the suction side 40 and conveyed to the pressure side 41 and from there and with a rotating peripheral component into the annular channel 25.
Das Pumpenrad 22 ist mit einer Achse 60 versehen, die an einem Ende in dem Lager 27 der das Motorgehäuse 15 verschließenden Kappe 26 und am anderen Ende in dem Armstern 29 über ein Radiallager 63 gelagert ist. Der ringförmige Längskanal 32 der Nabe 23 ist durch Stege 61 überbrückt, die die Nabe 23 an der Achse 60 festhalten. An dem dem Motor zugewandten Ende der Nabe 23 befinden sich Hilfsschaufeln 62, die die durch den Längskanal 32 einströmende Flüssigkeit radial nach außen pumpen und sie dem von den Pumpenschaufeln 24 erzeugten Hauptstrom zuführen. Durch die Hilfsschaufeln wird erreicht, daß der Spalt zwischen dem Pumpenrad 22 und dem Motorgehäuse 15 ständig durchströmt ist, so daß sich dort keine Thromben bilden können. Der Längskanal 32 ist so bemessen, daß der durch ihn hindurchgehende Blutstrom deutlich geringer ist als der von den Pumpenschaufeln 24 erzeugte Hauptstrom. Die Lager 27 und 63 sind derart angeordnet, daß sie einen ausreichenden Abstand zum Kanal 32 aufweisen. Obwohl der Übergang zwischen dem stationären und dem rotierenden Teil der Lager 27 und 63 integral - ohne große Stoßkante - erfolgt, an der sich Thromben anlagern könnten, muß davon ausgegangen werden, daß sich gegebenenfalls kleine Ringthromben an der Übergangsstelle bilden. Verschließen diese bei entsprechendem Abstand den Kanal 32 nicht, so kann ein degressives Thrombenwachstum aufgrund hinreichender Umpülung mit letztendlich stabiler Größe erreicht werden. The impeller 22 is provided with an axle 60 which at one end in the bearing 27 of the cap 26 closing the motor housing 15 and at the other end in the Arm star 29 is mounted via a radial bearing 63. The annular longitudinal channel 32 of the hub 23 is bridged by webs 61 which hold the hub 23 on the axis 60. At the end of the hub 23 facing the motor there are auxiliary blades 62 which pump the liquid flowing in through the longitudinal channel 32 radially outwards and feed them to the main flow generated by the pump blades 24. The auxiliary blades ensure that the gap between the impeller 22 and the motor housing 15 is continuously flowed through, so that thrombi cannot form there. The longitudinal channel 32 is dimensioned such that the blood flow passing through it is significantly less than the main flow generated by the pump blades 24. The bearings 27 and 63 are arranged such that they are at a sufficient distance from the channel 32. Although the transition between the stationary and the rotating part of the bearings 27 and 63 is integral - without a large abutting edge - on which thrombi could attach, it must be assumed that small ring thrombi may form at the transition point. If these do not close the channel 32 at a corresponding distance, then a degressive thrombus growth can be achieved due to adequate flushing with a ultimately stable size.

Claims

PATENTANSPRÜCHE PATENT CLAIMS
1. Blutpumpe nach dem Rotationspumpenprinzip, mit einem in Blut laufenden Pumpenrad (22) , d a d u r c h g e k e n n z e i c h n e t , daß das Pumpenrad (22) einen die Saugseite (40) mit der Rückseite verbindenden durchgehenden Kanal (32) aufweist.1. Blood pump according to the rotary pump principle, with a pump wheel (22) running in blood, so that the pump wheel (22) has a continuous channel (32) connecting the suction side (40) with the rear side.
2. Blutpumpe nach Anspruch 1, dadurch gekennzeichnet, daß das Pumpenrad (22) an seiner Rückseite mit radial fördernden Hilfsschaufeln (62) verbunden ist .2. Blood pump according to claim 1, characterized in that the pump wheel (22) is connected on its rear side with radially conveying auxiliary blades (62).
3. Blutpumpe nach Anspruch 1 oder 2, dadurch gekennzeichnet, daß das Pumpenrad (22) eine in Lagern (27,63) gelagerte Achse (60) aufweist, wobei die3. Blood pump according to claim 1 or 2, characterized in that the pump wheel (22) has a bearing (27,63) mounted axis (60), the
Lager (27,63) zur Vermeidung von größeren Thromben direkt von Blut umströmt sind und der Übergang zwischen stationärem und rotierendem Lagerteil kontinuierlich und frei von Stoßkanten ausgeformt ist .Bearing (27, 63) to prevent larger thrombi from which blood flows directly and the transition between the stationary and rotating bearing part is formed continuously and free of abutting edges.
4. Blutpumpe nach Anspruch 3, dadurch gekennzeichnet, daß die Lager (27,63) im Abstand von dem zentral angeordneten axialen Kanal (32) angeordnet sind, so daß kleine Thromben im Lagerbereich den Kanal (32) nicht versperren können. 4. Blood pump according to claim 3, characterized in that the bearings (27, 63) are arranged at a distance from the centrally arranged axial channel (32), so that small thrombi in the bearing area cannot block the channel (32).
PCT/EP1997/002903 1996-06-29 1997-06-04 Blood pump according to the rotary pump principle WO1998000185A1 (en)

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DE19626224A DE19626224A1 (en) 1996-06-29 1996-06-29 Blood pump based on the rotary pump principle
DE19626224.0 1996-06-29

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US6984201B2 (en) 2000-09-23 2006-01-10 Harefield Cardiac Limited Blood circulation assistance device
US11241569B2 (en) 2004-08-13 2022-02-08 Procyrion, Inc. Method and apparatus for long-term assisting a left ventricle to pump blood
US11642511B2 (en) 2004-08-13 2023-05-09 Procyrion, Inc. Method and apparatus for long-term assisting a left ventricle to pump blood
US12078192B2 (en) 2015-09-25 2024-09-03 Procyrion, Inc. Non-occluding intra vascular blood pump providing reduced hemolysis
US11235138B2 (en) 2015-09-25 2022-02-01 Procyrion, Inc. Non-occluding intravascular blood pump providing reduced hemolysis
EP3165782A1 (en) 2015-11-04 2017-05-10 Heraeus Deutschland GmbH & Co. KG Cermet bearing, in particular for an implantable medical device
US10156256B2 (en) 2015-11-04 2018-12-18 Heraeus Deutschland GmbH & Co. KG Cermet bearing, in particular for an implantable medical device
US11517736B2 (en) 2019-12-03 2022-12-06 Procyrion, Inc. Blood pumps
US11857777B2 (en) 2019-12-03 2024-01-02 Procyrion, Inc. Blood pumps
JP7709438B2 (en) 2019-12-03 2025-07-16 プロシリオン インコーポレイテッド Blood pump
US12161854B2 (en) 2019-12-03 2024-12-10 Procyrion, Inc. Blood pumps
US11452859B2 (en) 2019-12-03 2022-09-27 Procyrion, Inc. Blood pumps
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US11324940B2 (en) 2019-12-03 2022-05-10 Procyrion, Inc. Blood pumps
WO2021113389A1 (en) * 2019-12-03 2021-06-10 Procyrion, Inc. Blood pumps
US11779751B2 (en) 2019-12-03 2023-10-10 Procyrion, Inc. Blood pumps
US11571559B2 (en) 2019-12-13 2023-02-07 Procyrion, Inc. Support structures for intravascular blood pumps
US12017060B2 (en) 2019-12-13 2024-06-25 Procyrion, Inc. Support structures for intravascular blood pumps
US11697017B2 (en) 2019-12-13 2023-07-11 Procyrion, Inc. Support structures for intravascular blood pumps
US11351359B2 (en) 2019-12-13 2022-06-07 Procyrion, Inc. Support structures for intravascular blood pumps
US11471665B2 (en) 2019-12-13 2022-10-18 Procyrion, Inc. Support structures for intravascular blood pumps
CN116870356A (en) * 2023-06-28 2023-10-13 安徽通灵仿生科技有限公司 Catheter pump assembly and control system thereof

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