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WO2004098677A1 - Pompe a fluide - Google Patents

Pompe a fluide Download PDF

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Publication number
WO2004098677A1
WO2004098677A1 PCT/AU2004/000600 AU2004000600W WO2004098677A1 WO 2004098677 A1 WO2004098677 A1 WO 2004098677A1 AU 2004000600 W AU2004000600 W AU 2004000600W WO 2004098677 A1 WO2004098677 A1 WO 2004098677A1
Authority
WO
WIPO (PCT)
Prior art keywords
impeller
cavity
fluid
axis
fluid pump
Prior art date
Application number
PCT/AU2004/000600
Other languages
English (en)
Inventor
Daniel Lee Timms
Original Assignee
Queensland University Of Technology
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 Queensland University Of Technology filed Critical Queensland University Of Technology
Priority to JP2006504034A priority Critical patent/JP2006525460A/ja
Priority to AU2004236369A priority patent/AU2004236369A1/en
Publication of WO2004098677A1 publication Critical patent/WO2004098677A1/fr

Links

Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D29/00—Details, component parts, or accessories
    • F04D29/04—Shafts or bearings, or assemblies thereof
    • F04D29/046—Bearings
    • F04D29/048—Bearings magnetic; electromagnetic
    • 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
    • A61M60/10—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
    • A61M60/183—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 drawing blood from both ventricles, e.g. bi-ventricular assist devices [BiVAD]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—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
    • A61M60/40—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
    • 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
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04D—NON-POSITIVE-DISPLACEMENT PUMPS
    • F04D13/00—Pumping installations or systems
    • F04D13/02—Units comprising pumps and their driving means
    • F04D13/06—Units comprising pumps and their driving means the pump being electrically driven
    • F04D13/0606—Canned motor pumps
    • F04D13/0633—Details of the 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
    • 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

Definitions

  • the present invention relates to a motor, and in particular a fluid pump using an impeller which is suitable for use as a heart assist or heart replacement device, such as an LVAD (left-ventricular device) or BiVAD (Bi-ventricular device).
  • LVAD left-ventricular device
  • BiVAD Bi-ventricular device
  • Hydrodynamics bearings require relatively small clearances to provide sufficient bearing force. High shear stress is found in such clearances and is a possible site of haemolysis should blood cells enter this region. Hydrodynamic bearings rely on a passive response to forces imposed on the impeller, that is bearing stiffness cannot be altered for a given condition. Should forces exceed the predetermined bearing stiffness, touchdown is imminent. Additionally, rotors suspended hydrodynamically generate bearing force stiffness in direct proportion to rotor rotational speed. Ventricular assist devices have the potential to collapse the ventricle wall and thus block the inlet canula to the pump when excessive flow is demanded by the circulation system.
  • the rotational speed of the pump must be reduced for a period of time to allow the ventricular wall to detach, a situation not afforded to pumps suspended via hydrodynamic bearings, since a reduction in rotational speed results in reduced bearing stiffness and potential impeller touchdown.
  • US Patent No. 5,326,344 entitled “Magnetically Suspended and Rotated Rotor” describes an impeller for a blood pump which is supported by permanent magnets located in the impeller and pump housing respectively and stabilised by an electromagnet on the housing.
  • the configuration of the magnetic suspension system lends itself to low efficiency due to relatively large magnetic "Air Gaps". That is, the distance from rotor magnets to housing magnets is relatively large resulting in excess magnetic flux leakage and thus poor efficiency. Additionally, the magnetic suspension system is separated from the drive mechanism leading to increased size and electronics to provide both functions independently.
  • International Publication No. WO 99/01663 describes an improved rotor for a blood pump which relies on positioning of an impeller to give dynamic balance which is achieved through a combination of hydrodynamic and buoyant forces.
  • the rotor is driven electromagnetically by means of an electromagnetic drive system operating in conjunction with one or more arrays of permanent magnets.
  • the permanent magnets may be enclosed within radial vanes on the surface of the rotor with the drive components being arranged in a brushless motor configuration. In this device rotational movement of the rotor may occur around an axis which varies relative to the pump housing.
  • the arrangement was provided to attempt to eliminate the need for highly precise axis control and design fabrication. Part of the problem addressed is the need to avoid the introduction of large forces which otherwise are created when the axis of the rotor shifts away from its normally centrally disposed position in a magnetic levitation system.
  • the rotor is fashioned around an internal bore for accommodating inlet fluid and it is provided with a series of external shrouds providing multiple annular flow channels. This arrangement provides a larger surface area to contact blood during normal pumping operation. Erythrocyte fragility becomes a very relevant concern in such a device as shear force and frictional force interaction between the moving components and the blood volume may tend to lysis of red blood cells.
  • centrifugal heart pumps used for left ventricular assistance to date feature a conventional single sided impeller. That is, a rotating impeller with one set of vanes used to urge blood from one inlet to one outlet.
  • this technique can result in stagnation zones beneath the impeller, as well as unbalanced hydraulic forces experienced by the impeller which must be countered by forces generated from the suspension technique, thus leading to increased bearing power requirements and an overall loss of efficiency.
  • Placement of magnetic material within the rotor required for suspension and/or drive is limited due to the miniature rotor size.
  • the present invention provides a fluid pump including: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) a set of coils for generating a magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the magnetic field in use; c) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity; d) a radial bearing for controlling the position of the impeller in a direction orthogonal to the cavity axis; e) an axial coupling for controlling the position of the impeller in
  • the axial coupling may include: a) a second set of coils for generating a second magnetic field; and, b) a number of axial support magnets provided in the body and positioned in the second magnetic field in use, wherein the controller controls the second magnetic field to thereby control movement of the impeller in a direction parallel to the cavity axis.
  • the axial coupling may include the first set of coils and a number of axial support magnets provided in the body and positioned in the magnetic field in use, wherein the controller controls the magnetic field to thereby control movement of the impeller in a direction parallel to the cavity axis.
  • the axial coupling may include at least one of: a) a set of magnets coupled to the housing to generate an axial control field; and b) a number of axial support magnets provided in the body and positioned in the axial control magnetic field in use to thereby restrict movement of the impeller in a direction parallel to the cavity axis.
  • the axial support magnets can be the driver magnets.
  • the axial coupling may include: a) a first bearing member coupled to the housing; and, b) a second bearing member coupled to the impeller, the first and second bearing members cooperating to thereby restrict movement of the impeller in a direction parallel to the cavity axis.
  • the radial bearing may include : a) an inner surface of the housing; and, b) at least a portion of an outer surface of the impeller, the outer surface portion being shaped so as to cooperate with the inner surface such that when fluid is pumped in use, a boundary layer is formed between the inner and outer surface portions, to thereby restrict movement of the impeller in a direction orthogonal to the cavity axis.
  • the radial bearing may include a second set of coils for generating a second magnetic field, wherein the controller controls the third magnetic field using signals from the sensors to thereby control movement of the impeller orthogonal to the cavity axis.
  • the fluid pump typically includes at least one sensor positioned at a first end of the cavity and at least two sensors positioned at a second opposing end of the cavity.
  • the dimensions of the vanes are typically selected to control at least one of the fluid pressure and the flow rate at the outlet.
  • the dimensions may include at least one of: a) The height of the vanes; b) The diameters of the impellers; c) The length of the vanes; d) The width of the vanes; e) The inlet and outlet vane angles; f) The shape of the vanes; and, g) The number of vanes .
  • the housing includes: i) at least two fluid inlets; and, ii) at least two fluid outlets; and, b) the impeller includes: i) at least two body portions; and, ii) first and second sets of vanes positioned on the first and second body portions respectively, each set of vanes being for urging fluid from a respective inlet to a respective outlet, in use.
  • the impeller preferably cooperates with the cavity to define first and second cavity portions, each cavity portion including a respective inlet, outlet, and the impeller and cavity being configured to substantially prevent fluid transfer between the cavity portions.
  • the first and second sets of vanes may each have substantially identical dimensions to thereby provide fluid at substantially equal pressures and flow rates at the outlets.
  • the first and second sets of vanes may each have respective different dimensions to thereby provide fluid at respective first and second pressures at the respective outlet.
  • the first outlet may be coupled to the second inlet.
  • the cavity can be substantially rotational symmetric around the cavity axis will, with the coils being arranged circumferentially spaced around the cavity.
  • the body may be substantially rotational symmetric around the impeller axis, the driver magnets being positioned radially outwardly from and circumferentially spaced around the impeller axis.
  • the driver magnets are preferably positioned radially inwardly of the coils.
  • the first set of coils may be positioned radially inwardly of the second set of coils.
  • the coils are typically mounted on a yoke.
  • the yoke may include slots for receiving the coils.
  • the set of coils can include three pairs of first coils, the first coils in each pair being positioned in circumferential opposition, the controller being adapted to cause current to flow through the coils in corresponding directions, to thereby cause rotation of the impeller.
  • the controller can be adapted to: a) determine a required impeller rotation rate; b) determine a control signal sequence for each pair of first coils; and, c) apply the respective control signal sequence to the respective pair of first coils to urge the driver in a direction predetermined direction thereby causing rotation of the impeller.
  • the second set of coils can include three pairs of second coils, the second coils in each pair being positioned in circumferential opposition, the controller being adapted to cause current to flow through the coils in counter-corresponding directions, to thereby cause radial movement of the driver member with respect to the cavity axis.
  • the controller is typically adapted to: a) monitor the sensors; b) determine any movement of the driver axis in a direction radial to the cavity axis; c) select one or more pairs of second magnets; d) generate a control signal for each selected pair; and, e) apply the control signal to the respective selected pair to urge the driver in a direction predetermined direction thereby moving the driver axis toward the cavity axis.
  • the controller may be formed from a processing system having a memory and a processor, the processing system being adapted to generate control signals to control the magnetic field generated by the coils in accordance with a predetermined algorithm stored in the memory.
  • the processing system can be coupled to a signal generator, the control signal being formed by having the processing system cause the signal generator to apply a predetermined current to the coils.
  • the driver magnets may include eight circumferentially spaced permanent magnets, the poles of the magnets being aligned perpendicularly to the driver axis, and arranged such that the direction of pole alignment is reversed in adjacent magnets.
  • the body can include: a) two body end portions; and, b) a number of vanes positioned on the end body portions, the vanes extending from a surface of the body end portions in a direction substantially parallel to the driver axis, and being positioned radially outwardly from and circumferentially spaced around the driver axis.
  • Each body end portion may have a substantially conical shape.
  • the body can include a substantially cylindrical central body portion positioned between the two body end portions, the driver magnets being positioned in the cylindrical central body portion.
  • the cavity may include first and second cavity end portions each cavity end portion having: a) an inlet positioned along the cavity axis; and, b) an outlet directed orthogonally with respect to the cavity axis, and arranged radially offset from the cavity axis; and, c) a substantially conical shape for cooperating with the impeller to allow the vanes to urge fluid from the inlet to the outlet in response to rotation of the impeller.
  • the impeller and the cavity typically cooperate to substantially prevent fluid flow from one cavity end portion to the other, the vanes on each body end portion having a respective height or length to thereby control the pressure or rate of fluid flow at the outlet in the respective end portion.
  • the pump preferably includes at least two sensors positioned in at least one of the cavity end portions to thereby determine the distance between the sensor and the surface of the respective body end portion.
  • the impeller may include a shroud coupled to the vanes, the sensors being adapted to determine the position of the shroud.
  • the pump can include at least three sensors positioned radially outwardly from and circumferentially spaced about the cavity axis.
  • the sensors may include a radiation source adapted to emit radiation towards the surface of the respective body end portion and a detector for detecting reflected radiation.
  • the impeller may include position magnets, the sensors being formed from Hall effect sensors adapted to determine the magnetic field generated by the position magnets.
  • the position magnets can be the driver magnets.
  • the support magnets can be substantially cone or frustro-conically shaped.
  • the impeller and the cavity may have a substantially cylindrical shape.
  • the impeller can include one or more wedges positioned on an outer circumference of the body to thereby cooperate with the inner surface to hydrodynamically control the position of the impeller in a direction orthogonal to the cavity axis.
  • the wedges may be provided in a central body portion.
  • the axial support magnets can be formed from a magnetic material positioned in a magnetic field.
  • the axial support magnets can be formed from soft iron.
  • the impeller may include a shroud on each body end portion.
  • Each shroud may include driver magnets.
  • Each shroud can include axial support magnets.
  • the pump can include a set of second magnets provided in each of two cavity end portions.
  • a fluid pump including: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) first and second sets of coils for generating respective first and second magnetic fields; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the first and second magnetic fields in use; c) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity; and
  • the controller can control the second magnetic field to thereby control movement of the impeller parallel to the cavity axis.
  • the fluid pump can include an axial coupling for restricting movement of the impeller in a direction parallel to the cavity axis.
  • a fluid pump including: a) a housing having an inner surface defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) a set of coils coupled the housing for generating a magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the magnetic field in use; and, iv) an outer surface, at least a portion of the outer surface being shaped so as to cooperate with a correspondingly shaped portion of the inner surface such that when fluid is pumped in use, a boundary layer is formed
  • the axial coupling includes: a) a second set of coils for generating a second magnetic field; and, b) at least two sensors for sensing the position of the impeller within the cavity, the controller being coupled to the sensors and the second set of coils, and wherein in use the controller controls the second magnetic field to thereby confrol movement of the impeller in a direction parallel to the cavity axis.
  • the axial coupling can include at least one of: a) a set of magnets coupled to the housing to generate an axial control field; and b) a number of axial support magnets provided in the body and positioned in the axial control field in use to thereby restrict movement of the impeller in a direction parallel to the cavity axis.
  • the axial coupling may include: a) a first bearing member coupled to the housing; and, b) a second bearing member coupled to the impeller, the first and second bearing members cooperating to thereby restrict movement of the impeller in a direction parallel to the cavity axis.
  • the present invention provides a fluid pump including: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) a set of coils for generating a magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the first magnetic field in use; c) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity; and, d) a controller coupled to the sensors and the set of coils, wherein in use the controller confrols the magnetic field to thereby control: i) rotation of the impeller about the imp
  • the present invention provides a fluid pump including: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) a set of coils to generate a first magnetic field; iv) a set of magnets to generate an axial control magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the first magnetic field in use; and, iv) a number of support magnets positioned in the axial confrol magnetic field to thereby restrict movement of the impeller in a direction parallel to the cavity axis; c) a controller coupled to the set of coil
  • the present invention provides a fluid pump including: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; ii) at least one fluid outlet; and, iii) a first bearing member; iv) a set of coils for generating a respective magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets; and, iv) a second bearing member, the first and second bearing members cooperating to thereby restrict movement of the impeller in a direction parallel to the cavity axis; c) a controller coupled to the set of coils, the controller being adapted to confrol the magnetic field generated by the first set of coil
  • the fluid pump typically further includes a radial bearing for confrolling movement of the impeller orthogonal to the cavity axis.
  • the radial bearing may include: a) an inner surface of the housing; and, b) the impeller has an outer surface, at least a portion of the outer surface being shaped so as to cooperate with a correspondingly shaped portion of the inner surface such that when fluid is pumped in use, a boundary layer is formed between the inner and outer surface portions, to thereby restrict movement of the impeller in a direction orthogonal to the cavity axis.
  • the radial bearing may include: a) a second set of coils for generating a second magnetic field; b) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity, wherein the controller controls the third magnetic field using signals from the sensors to thereby control movement of the impeller orthogonal to the cavity axis.
  • the fluid pump can include at least one sensor positioned at a first end of the cavity and at least two sensors positioned at a second opposing end of the cavity.
  • the present invention provides a fluid pump including: a) a housing having an inner surface defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; ii) at least one fluid outlet; iii) a set of coils coupled the housing for generating a first magnetic field; and, iv) a set of magnets coupled to the housing to generate an axial control magnetic field; b) an impeller positioned in the cavity for urging fluid from the inlet to the outlet, wherein the impeller has: i) a body defining an impeller axis, ii) a number of driver magnets positioned in the first magnetic field in use; iii) an outer surface, at least a portion of the outer surface being shaped so as to cooperate with a correspondingly shaped portion of the inner surface such that when fluid is pumped in use, a boundary layer is formed between the inner and outer surface portions, to thereby restrict movement of the impeller in a direction orthogonal
  • the present invention provides a method of pumping fluid, using a fluid pump having: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) first and second sets of coils for generating respective first and second magnetic fields; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the first and second magnetic fields in use; and, c) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity, wherein the method includes: i) controlling the first magnetic field to thereby control rotation of the impeller about the impeller axis;
  • the present invention provides a method of pumping fluid using a fluid pump having: a) a housing defining a cavity having a cavity axis, the housing having: i) at least one fluid inlet; and, ii) at least one fluid outlet; iii) a set of coils for generating a magnetic field; b) an impeller positioned in the cavity, the impeller having: i) a body defining an impeller axis, the impeller axis being substantially parallel to the cavity axis in use; ii) a number of vanes positioned on the body for urging fluid from the inlet to the outlet, in use; iii) a number of driver magnets positioned in the first magnetic field in use; c) at least two sensors, the sensors being adapted to detect the position of the impeller within the cavity, wherein the method includes controlling the magnetic field to thereby control: i) rotation of the impeller about the impeller axis; and, ii) movement of the imp
  • the present invention provides an impeller for use in a fluid pump, the impeller being mounted in a pump cavity and being adapted to urge fluid from first and second inlets to corresponding first and second outlets, wherein the impeller includes: a) a body defining an impeller axis, the body including first and second body end portions; b) a set of vanes positioned on each body end portion for urging fluid from a respective inlet to a corresponding outlet, in use; c) a number of driver magnets positioned in the first and second magnetic fields in use; and, d) an outer surface portion shaped so as to cooperate with a correspondingly shaped portion of the inner surface such that when fluid is pumped in use, a boundary layer is formed between the inner and outer surface portions, to thereby restrict movement of the impeller in a direction orthogonal to the cavity axis.
  • the impeller forms part of a fluid pump according to claim 4.
  • the present invention provides an impeller for use in a fluid pump, the impeller being mounted in a pump cavity and being adapted to urge fluid from first and second inlets to corresponding first and second outlets, wherein the impeller includes: a) a body defining an impeller axis, the body including first and second body end portions; b) a set of vanes positioned on each body end portion for urging fluid from a respective inlet to a corresponding outlet, in use; c) a number of driver magnets positioned in the first and second magnetic fields in use; and, d) at least a first part of an axial coupling for restricting movement of the impeller in a direction parallel to the impeller axis.
  • the axial coupling may include at least one of: a) a second bearing member adapted to cooperate with a first bearing member provided on the housing; and, b) a number of support magnets for positioning in an axial control magnetic field in use.
  • the dimensions of the vanes typically are typically selected to control at least one of the fluid pressure and the flow rate at the outlet.
  • the dimensions usually include at least one of: a) The height of the vanes; b) The diameters of the impellers; c) The length of the vanes; d) The width of the vanes; e) The inlet and outlet vane angles; f) The shape of the vanes; and, g) The number of vanes.
  • the impeller can be positioned in a pump cavity in use such that the inlets are aligned parallel to the body axis, with each inlet being positioned to direct fluid along the body axis towards a respective body end portion, the impeller being rotated in use to thereby urge the fluid radially outwardly towards the outlets.
  • the body may include a substantially cylindrical central body portion positioned between the two end portions, the driver magnets being positioned in the cylindrical central body portion.
  • the impeller can be adapted to cooperate with the pump cavity to define first and second cavity portions, each cavity portion including a respective inlet, outlet, and end body portion, the impeller being adapted to substantially prevent fluid transfer between the cavity portions.
  • the impeller can be adapted for use a in heart pump, the first and second sets of vanes being adapted to pump blood for assisting the left and right ventricles respectively.
  • Figures 1A to IE are schematic cross sectional, end, plan, perspective and explored perspective views of an example of a fluid pump incorporating an impeller;
  • Figures 2A to 2F are schematic plan views of examples of inlet and outlet volutes for use in the pump of Figures lA to IE;
  • Figures 3A to 3D are schematic perspective and plan views of examples of impellers for use in the pump of Figures lAto IE;
  • Figures 4A to 4J are schematic views of examples of magnets for use in the pump of Figures 1A to IE;
  • Figures 5 A and 5B are schematic plan views of the fields generated by the coils and the corresponding movement of the impeller in the pump of Figures 1 A to IE;
  • Figure 6 is a schematic representation of an example of a controller for confrolling the pump of Figures
  • Figures 7 A to 7C are schematic perspective, plan and side views of examples of sensors for use in the pump of Figures lAto IE;
  • Figure 8 is a schematic view of an example of the sensing of the position of the impeller of Figure 3 A;
  • Figure 9 is a schematic view of an example of the sensing of the position of the impeller of Figure 3B;
  • Figure 10 is a schematic view of an example of a fluid pump having additional axial suspension
  • Figures 11A and 1 IB are schematic perspective views of an example impeller and a housing for use in a pump having active axial suspension
  • Figures 12A to 12L are schematic views of a further example of a fluid pump incorporating an impeller
  • Figures 13 A to 13J are schematic views of a further example of a fluid pump incorporating an impeller
  • Figure 14 is a schematic cross sectional view of a fluid pump having an axial bearing.
  • FIG. 1 A to IE An example of a fluid pump incorporating a double impeller is shown in Figures 1 A to IE.
  • the pump includes a housing 1 having two conically shaped end portions 1A, IB, defining a cavity 2, containing an impeller 3.
  • the impeller is formed from two substantially conically body end portions, 3 A, 3B, each having a number of vanes 4 mounted thereon.
  • Each housing portion 1A, IB is provided with a respective inlet 5A, 5B, and a respective outlet 6A, 6B.
  • the housing includes a clearance gap 8 A between a rim 8 and the impeller 3, which cooperate to effectively split the cavity 2, into two cavities cavity end portions forming respective 2A, 2B, and to reduce fluid flow between the two cavities.
  • the pump effectively includes two pumps defined by the cavities 2 A, 2B.
  • the impeller 3 is rotated about an axis shown generally at 7. This causes fluid at the respective inlets 5A, 5B to be urged towards the respective outlet 6A, 6B, as will be appreciated by persons skilled in the art.
  • the inlets 5A, 5B are preferably aligned with the cavity axis 7, to thereby direct blood flow directly onto the impeller 3 and hence into contact with the vanes 4.
  • the fluid should enter the cavity from a direction substantially perpendicular to the cavity axis.
  • the inlet includes a 90° a turn to align entry of the fluid into the cavity 2 along the cavity axis 7.
  • inlet volutes 5 A, 5B may be replaced with straight canula parallel to the axis of impeller rotation 7.
  • inlet volutes 5C, 5D examples of which are shown in Figures 2A and 2B.
  • Flow enters the inlets rolutes 5C, 5D via respective ports 5E,5F and is provided with a rotational component by the shape of the volute shown at 5G, and the lip 5H at the impeller eye.
  • This lip 5H also reduces recirculation and potential stagnation in the region.
  • the inlet volutes 5C, 5D provide additional anatomical compatibility when implanting the fluid pump beneath a subject's heart.
  • the pump the inlet and outlet flow should preferably be in the same plane.
  • the axial size of the fluid may be reduced by employing a flattened 'pancake' style inlet volute.
  • the inlet volutes 5C, 5D direct blood onto the revolving impeller 3.
  • the vanes 4 have the effect of urging blood via respective outlet volutes 37A, 37B, which describe a spiral channel, which leads to a respective one of the outlets 6 A and 6B.
  • FIG. 2C Examples of a number of outlet volutes are shown in Figures 2C to 2F.
  • the volutes 37 A, 37B commence with a narrow space between the vanes 4 and an inner surface of the cavity 2, known as the 'cutwater' 38 A.
  • the volute increases in volume and flares out to be continuous with the respective outlet 6A, 6B, or alternatively can further flare out into a vaneless diffuser 38C, as shown in Figure 2E.
  • This volute structure can help decrease turbulent flow and wall friction during flow as the volume of blood is urged towards the outlet, since fluid velocity is kept uniform, thereby reducing shear stress development and preserving the components of the fluid being pumped.
  • the embodiment shown in Figure 2D implements a split volute.
  • the radial clearance gap or first volute area 37A between the rotor and the housing increases from the initial point (cutwater) 38A, until it encompasses half or approximately 180° of the impeller.
  • a second cutwater 38B is implemented at 180° as the beginning to the second volute 37B.
  • the split, or 'double' volute encounters a reduced radial thrust and improved efficiency over a larger operating range, which is encountered by a patient with varying levels of heart failure and thus assistance required during the course of their support.
  • Figure 2F shows a concentric volute. Radial hydraulic thrust is reduced only at the best efficiency point of the single volute, whereas concentric volute encounters the most radial thrust over all operating conditions.
  • Levitation and rotation of the impeller 3 within the cavity 2 and about the cavity axis may be achieved in a number of manners, h one example this is achieved using two sets of magnets, formed from electrically activated coils 11, 12, provided in the housing, and a set of permanent driver magnets 9 provided in the impeller as shown in Figure 4B, and as will be described in more detail below.
  • the first set of magnets cooperate with the driver magnets 9 embedded in the impeller to provide a rotational torque, with the second set of magnets (coils 12) being used to form a magnetic bearing which can be used to maintain the position of the impeller 3 within the cavity.
  • the 1 st and 2 nd set of magnets (coils) can be combined into a single set of magnets (coils) and energised with superimposed currents to produce bearing and motor flux independently.
  • the active magnetic bearing provides additional magnetic flux to counteract any disturbance forces. This practice is common to magnetic motor-bearing systems derived from so called Lorentz and Reluctance theory, as described in "Active Magnetic Bearings : Basics, Properties and Applications of Active Magnetic Bearings", Schweitzer, G. Bleuler, H.,Traxler, A, (1994).
  • This form of pump assembly can provide assistance or replacement of one or more ventricles of a mammalian heart. This is achieved by connecting the inlets 5A, 5B of the pump to either the left ventricle or atrium, imparting energy to the fluid via the double sided centrifugal impeller 3, and connecting the outlets 6A, 6B to the aorta, thus assisting the natural function of the left heart. Additionally or alternatively, the inlets 5A, 5B may be connected to the right ventricle/atrium, with the outlets 6A, 6B connected to the pulmonary artery, thus providing left and right, or right heart assistance respectively.
  • LVAD left chambers of the heart
  • FIG. 1A shows a detailed cross section of one example of a pump used as a left ventricular assist device embodiment.
  • this configuration includes two volute type inlets, 5C,5D which supply fluid to a double sided centrifugal pump formed by two substantially conical shaped body portions 3A,3B, each having a number of vanes 4A,4B mounted thereon.
  • the vanes are configured to produce the same pressure at the outlet 6 A, 6B of each cavity 2 A, 2B.
  • This in effect represents two centrifugal pumps operating in parallel, thus output flow rate at a canula 40 is double the flow rate produced at each outlet 6A, 6B, for the specific pressure increase.
  • the cavity 2 is separated into two cavities 2A, 2B by a small clearance gap 8A, which is the site for the radial type magnetic motor bearing.
  • the coils 11, 12 reside on the outside of the pump housing 1, as shown and couple to the permanent driver magnets 9 embedded in the cylindrical circumference of the impeller. This magnetic bearing provides contact free impeller suspension in the radial (x,y) directions as well as rotational torque.
  • Figure IE is a detailed exploded view of the pump.
  • hilet flow is provided by a single canula 39 from the left ventricle or atrium, and is split into two conduits 39A, 39B, which connect to the inlets 5A, 5B to provide even flows in both of the cavities 2A, 2B.
  • the variations of left ventricular pressure developed during systole and diastole are transmitted directly to both of the inlets 5A, 5B of the pump via the inlet volutes 5C,5D, acting to balance and therefore minimise axial thrust forces encountered by the impeller 3 which is a feature not significantly afforded in conventional single sided pumps.
  • Figure 3A is an example of one configuration of the impeller 3 used in this example.
  • the impeller is formed from three portions, namely end portions 3A, 3B and a central portion 3C, which in one example includes the permanent driver magnets 9.
  • the end portions 3 A, 3B include respective sets of vanes 4A, 5B, as shown.
  • vanes 4A, 4B allow the characteristics of flow provided at the outlets 6A, 6B to be controlled. This will be effected by a number of factors as discussed in more detail below. It will be appreciated from this however, that a number of different vane arrangements can be used.
  • FIG. 3B another impeller configuration is described by Figure 3B.
  • a shroud 3D is employed on the vanes 4A, 4B to improve hydraulic efficiency as well as providing a closer proximity sensor target. This situation does however lend itself to potentially higher shear values between the shroud the shroud 3D and the cavity 2, but increase sensor resolution as will be described in more detail below.
  • Figure 3C shows a 'backward inclined' vane embodiment, with outer and inner blade diameter 4D, 4C, outer vane angle 4E, inlet vane angle 4F and vane height 4G, which can be used to produce the desired flow characteristics.
  • the vanes 4 can be straight radial in nature as shown in Figure 3D, or forward inclined (not shown). '
  • fluid leaving the impeller 3 is collected by 9 split volute type casing 37 A, 37B and transmitted to outlets 6A,6B, with the angle of spiral corresponding to the relative angle of flow off the vanes 4 at design conditions.
  • Outlet flow is combined by the conduits 40A, 40B to provide the single canula 40 to the aorta.
  • each output flow 6A, 6B can be directed to different sites of the aorta, eg, the ascending and descending aorta. This may provide additional flow to specific organs otherwise depleted from a single ascending aortic interface, but does not require an additional interface site to the circulatory system.
  • the impeller 3 is suspended and driven by first and second sets of coils 11, 12 which generate respective magnetic fields which couple to the driver magnets 9 provided in the central portion 3C, of the impeller 3, as shown in Figure 4A.
  • the first and second sets of coils 11, 12 are positioned in an outer section of the housing 1 circumferentially surrounding the driver magnets 9, to thereby provide the required magnetic bearing and rotational torque.
  • the sets of coils 11, 12 are arranged on a common yoke 15, which acts as a stator.
  • the yoke is preferably constructed from a laser or water jet cut laminated or sintered iron core, for the purpose of eddy current loss reduction.
  • the magnetic material can be rare-earth, neodynimum, or any material available to provide sufficient flux, hi one example, six coils are provided in each set, but other numbers amounts could be used.
  • the coils 11, 12 may be provided flush on the surface of the yoke 15 (known as a "slotless" arrangement), as shown in Figures 4C to 4E.
  • This configuration requires permanent magnet shape 9A, as shown in Figure 4F. Compared to other arrangements this results in a lower production of radial force, though significantly reduces the degree of negative stiffness instability as well as reducing the inductance and therefore allows for greater rotational speed generation as the back EMF generation is lower. Greater impeller mass and larger coil sizes result in a larger volume occupied by this magnetic bearing type.
  • the coils can be located in slots 15A in the yoke (known as a "slot-type"), so that the yoke extends radially inwardly as shown at 15C, 15D in Figure 4G.
  • This configuration prefers the magnet shape 9B shown in Figures 4H and 41 to reduce the degree of cogging torque produced. Greater bearing and torque generation is possible for this stator type, however speed is limited due to the relatively larger inductance, however sufficient rotational speed is possible for this application.
  • magnets can be configured in a Halbach array as shown in Figure 4J to improve the flux density. This involves constructing each separate magnet from a plurality of smaller magnets each with slightly changing radial polarity direction.
  • the driver magnets 9 are arranged with their poles aligned perpendicular to the axis of the impeller 3, with adjacent magnets having poles aligned in opposing directions. This provides alternating magnetic fields around the outside of the impeller 3, as shown by the arrows 10.
  • the magnetic fields extend radially outwardly from the permanent magnets 9, with the direction of the field alternating between being directed radially outwardly or radially inwardly, as shown.
  • FIGS 5A and 5B are cross sectional views of the circumference of the coils 11, 12 and yoke 15 to show the directions of the coils 11, 12.
  • the first set of coils 11 provide the rotational torque (known as the "motor coils") and the second set of coils 12 provide the bearing action (known as the "bearing coils").
  • a pair of opposingly positioned motor coils 11 A, 1 IB in the motor winding are energised with a current flow as shown.
  • This causes the generation of a magnetic field shown by arrows 16A which in turn generates a Lorenz force in the coils as shown by the arrows 16B.
  • the impeller can be rotated.
  • a pair of opposing coils 12A, 12B in the bearing winding are energised with a current flow as shown.
  • the controller includes a processing system 20 having a processor 21, a memory 22, and an external interface 23 coupled together via a bus 24.
  • An optional input/output device 25 may also be provided.
  • the processing system 20 is coupled to three sensors, 26A, 26B, 26C, and a signal generator 27 via the external interface 23.
  • the signal generator 27 is coupled to the motor and bearing coils, to allow pairs of opposing coils to be selectively activated as shown generally for the motor coils 11 A, 11B, 11C, 11D, HE, 11F and the bearing coils 12A, 12B, 12C, 12D, 12E, 12F respectively.
  • the coils are arranged as pairs of opposingly position coils 11 A, 11B; 11C, 11D; HE, 11F and 12A, 12B; 12C, 12D; 12E, 12F.
  • the processor 21 determines from data stored in the memory 22 the current that must be applied to the motor coils in order to provide a required rotation speed.
  • a single speed may be pre-set before the device is implanted. It will be appreciated that this may be achieved by storing information defining the pre-set speed in the memory 22, using either the I/O device 25, or a remote processing system coupled to the external interface 23.
  • different speeds may be set whilst the pump is in use. This may be achieved for example using the I/O device 25, or via a wired or wireless connection to the external interface 23, or in response to external impetus, such as an increase in latent heart rate, or the like, through the use of appropriate detection systems. i any event, signals representing the currents to be supplied are provided to the signal generator 27, which operates to generate appropriate currents, which are then supplied to the motor coils HA, 11B, 1 lC. This will typically involve activating the motor coil pairs in a predetermined sequence in order to create the desired movement of the impeller.
  • a set of apertures are provided in each body potion 1A, IB, evenly circumferentially spaced around the respective cavities 2A, 2B.
  • each set of apertures are spaced such that sensors 26A, 26B are arranged along x and y axes having an origin coincident with the cavity axis.
  • the third sensor 26C is positioned mid way between the -x and -y axes.
  • the sensors 26A, 26B, 26C operate by determining the distance "d" between the respective sensor and the surface 33 of the impeller 3, as shown in Figure 8.
  • the determined distance for the three sensors 26A, 26B, 26C is used to determine the position of the impeller body by resolving these distances into the x,y and z planes, as appreciated by anyone skilled in the art.
  • each sensor 26A, 26B, 26C can be formed from a radiation source such as an LED laser, or the like and corresponding optical detector, as will be appreciated by persons skilled in the art. Other techniques may also be used.
  • a shroud 3D can be mounted on the vanes 34, as shown in Figure 9.
  • the position of the impeller 3 can be measured by measuring the distance dl between magnetic sensor targets embedded in the shroud 3D and the sensors 26A, 26B, 26C.
  • the distance dl between the permanent magnetic sensor targets and the sensors 26A, 26B, 26C is less than distance d between the surface 33 and the sensors 26A, 26B, 26C.
  • the vanes 4 will periodically pass between the sensors 26A, 26B, 26C and the surface 33, which can affect the measurements.
  • the use of the shroud 3D tends to allow the processor to determine the position of the impeller faster and more accurately, with a higher degree of resolution.
  • the presence of the shroud 3D can reduce the effectiveness of the impeller 3, and generate turbulence within the respective cavity 2 A, 2B. This is undesirable for some applications, such as use of the system as a heart pump.
  • An alternative method of sensing the position of the impeller within the cavity 2 relates to the so called 'self sensing' technique, whereby the voltage and current waveforms of each motor and/or bearing coil can be monitored by the processing system 20 to sense the position of the impeller.
  • a component of the current waveform is related to the circuit inductance, which in turn varies inversely with movement of the permanent driver magnets 9 in the air gap 8A. Recording and analysing the back EMF voltage generated by the motor achieves rotational position sensing, with signals from the bearing coils determining the position. It will be appreciated that in this example, the bearing coils 12 and the motor coils 11 form the sensors 26.
  • the processing system 20 detects movement of the impeller laterally such that the axis of the impeller 3 and the cavity axis 7 are no longer aligned, the processor will use a predetermined algorithm to determine the current that needs to be applied to selected pairs of bearing coils 12. An indication of this is transferred to the signal generator 27, which in turn responds by generating appropriate currents and applying these to the selected ones of the bearing coils 12. The current in the coils 12 causes the impeller body to move, as described above, thereby realigning the impeller body axis with the cavity axis.
  • the sensors 26 can also be adapted to determine the rotational position of the impeller 3, thereby allowing the rate of rotation to be monitored and adjusted by the processing system 3.
  • other magnetic bearing techniques may be implemented, such as those based on reluctance type magnetic theory.
  • This configuration requires a slightly different control strategy and slotted stator configuration, with six coils around six iron only cores, as will be appreciated by those skilled in the art.
  • the impeller is positioned so that the magnets 9 are situated radially inwardly of the motor and bearing coils 11, 12, as this provides optimum coupling between the coils 11, 12 and the permanent magnets 9, thereby providing optimum efficiency and thus stiffness in the radial direction. This can be achieved in a number of ways depending on the specific implementation. hi addition to controlling the position of the impeller 3 laterally, it is also necessary to ensure that the position of the impeller along the cavity axis (the "axial position”) is maintained.
  • the permanent driver magnets 9 are attracted to the magnetic fields generated in the motor and bearing coils 11, 12. This provides a degree of restoring action to the axial null position, hi particular, if the impeller is displaced along the cavity axis, the attraction of the coils 11, 12, will urge the impeller back into the optimum position due the effect know as passive stability. This is generally sufficient to maintain alignment in the axial direction in most cases, especially if the fluid pressure is substantially equal in both cavities 2A, 2B.
  • additional or alternative axial alignment can be provided through the provision of additional support magnets.
  • the support magnets can be provided in the housing, with corresponding magnets being provided in the body of the impeller 3. This can be achieved using a variety of magnet configurations.
  • flat (parallel to the radial axes) or frustro-conically shaped permanent magnets 35 can be provided around the circumference of the housing portions 1A, IB as shown in Figure 10. This can be achieved with a single appropriately shaped magnet, or a series of circumferentially spaced magnets 35.
  • the support magnets 35 A, 35B cooperate with corresponding permanent support magnets 36A, 36B provided in the impeller body 3. If the magnets are configured with like poles facing each other, the support magnets 35 will repel the support magnets 36, thereby urging the impeller body into the centre of the cavity.
  • the magnets 35 can be replaced by coils.
  • the support magnets 36 in a manner similar to the driver magnets 9, this allows the axial bearing to be additionally used to drive the impeller in a manner similar to that described above.
  • the axes of polarity of the housing magnets and rotor magnets being at an angle to the impeller axis, although the rotor and/or housing magnets may be physically perpendicular to the impeller axis in which case the angle may be suitably 0°, and the magnetic polarity parallel to the impeller axis.
  • the angle corresponds to the angle of the cones forming the impeller 3, to provide the smallest gap between rotor and housing permanent magnets, but it may suitably be in the range of 0° - 65°.
  • the angle should be arranged to provide the most counteraction against the varying axial loads imposed by the pumped fluid. This angle may in fact be different from rotor magnets to housing magnets and may be suited to provide one of either radial or axial support.
  • the pump is adapted to operate to assist or replace the natural function of the left ventricle, at a reduced rotational speed or impeller diameter as compared to the first example.
  • fluid enters directly from the left ventricle/atrium into the first inlet volute 5C.
  • the fluid travels through inlet 5A, with the vanes 4A on the impeller 3A within the cavity 2A acting to urge the fluid to outlet 6A.
  • Fluid then travels from outlet 6A through a cross over volute to the inlet 5B, thus entering the pump cavity 2B.
  • the vanes 4B urge the fluid to the outlet 6B and into the circulatory system via a canula to the aorta. Fluid is separated from the cavities 2A, 2B by the clearance gap 8A.
  • the fluid undergoes two stages in pressure increase.
  • the fluid entering cavity 2A must undergo a rise in pressure in the order of half of the overall required output pressure rise as fluid is transferred from the inlet 5 A to the outlet 6B.
  • the fluid entering the cavity 2B, via the inlet 5B is already at half the desired overall pressure value, and therefore can undergo the other half of the required overall pressure rise in the cavity 2B.
  • the impeller rotational speed can be reduced as compared to the LVAD example described above.
  • the reduction in speed is in the order of LVAD RPM /2. This reduction in rotational speed significantly reduces the level of shear stress within the pump, leading to a potential reduction in hemolysis levels.
  • the impeller rotational speed may be kept constant, with the impeller outer diameter reducing to achieve the desired pressure rise, as described by Fluid Mechanics Theory. It will be appreciated that this configuration may result in an imbalance in the pressure distribution between the two in cavities 2A, 2B, causing an axial force in the direction of the cavity axis 7 toward the lower pressure cavity 2A. Similarly, a leakage of flow may occur from the cavity 2B to the cavity 2 A, through the clearance gap 8 A, due to the pressure difference between the cavities 2A, 2B.
  • Figures 12A to 12F show a first example configuration for X-LVAD operation.
  • similar reference numerals to those described above, increased in value by 50, will be used, and each element of the pump will not therefore be described in detail.
  • the impeller 53 is completely suspended in the axial direction, and rotated about the cavity axis 57 with the use of an axial magnetic motor bearing.
  • the radial degrees of freedom are restricted by a combination of passive magnetic forces caused by the active axial bearing coupled with a hydrodynamic bearing located at 58.
  • the hydrodynamic bearing requires a minimal clearance gap 58A, which acts to significantly reduce the fluid flow from cavity 52B to 52A.
  • the cavity 52 is correspondingly shaped, to accommodate the alternative impeller shape.
  • the impeller 53 is cylindrical and employs a shroud 53D to improve hydraulic efficiency as well as providing a region for magnet material placement.
  • the vanes 44A are configured, via correct selection of vanes angles, and heights, to produce a pressure rise of half the desired overall pressure rise required by the pump.
  • the rise in pressure from the inlet 55A to the outlet 56A is in the region of 50mmHg.
  • This volute transfers the fluid in an efficient manner to the inlet 55B of the second stage.
  • Fluid entering the second stage is at half the overall pressure, and the vanes 54B are required to cause the second half of the overall pressure rise.
  • the vanes 54B may have slightly different profiles to accommodate for the different inlet conditions.
  • a magnet system is used to provide both axial suspension and rotation of the impeller 53, with the cavity 52.
  • An example of this will now be described with respect to Figures 12G to 12L.
  • two slotted type stators 65 A, 65B are positioned axially above and below the impeller 53.
  • four driver magnets 59A are provided on the first end 53 A of the impeller, with a corresponding set of driver magnets 59B provided on the second end 53B.
  • alternative numbers of magnets may be used.
  • coils 61 A, 6 IB located in the top and bottom stators 65A, 65B. h this example, six coils 61A, 61B are shown, but other numbers may be used.
  • an increase in the current supplied to the coils 61 A is accompanied by a corresponding decrease in the current applied to the coils 61B, thereby causing an increase in magnetic attraction to the coils 61A, and decreased magnetic attraction to the coils 61B.
  • This confrol will again be performed by determining the position of the impeller 53 using appropriate sensors 76, coupled to a processing system 70. Operation will then be performed in a manner similar to that described with respect to Figures 5A, 5B and 6, and will not therefore be described in any detail.
  • the stator 65A can be adapted to act solely as a magnetic bearing, coupling to iron on the first end 53 A of the impeller.
  • the rotational torque is only provided by the bottom stator 65B, which has more iron cores, coupled to a suitable number of driver magnets 59B embedded in the end 53B.
  • the sensors 76 can be mounted to target onto the flat impeller shroud 53D, to directly sense motion in the axial direction only, as required for the axial type magnetic bearing.
  • the magnetic fields generated by the coils 61 A, 6 IB couple directly to iron embedded within the shroud 55D, at either end 53 A, 53B, of the impeller 53.
  • This provides axial bearing confrol only, and can therefore be used to control the position of the impeller 53 along the cavity axis 57.
  • Rotational torque is provided via similar method described previously, by coupling a three phase motor to magnets 59 embedded in the cylindrical circumference of the impeller 53. This may be achieved using similar arrangements to those described above with respect to Figures 4 to 7.
  • the motor has six coils wound around a six core stator located in the housing radially outward from the outer circumference of the impeller. h all of the above examples, movement in a radial direction can be controlled using a number of different manners. For example, this can be achieved by using an appropriate set of coils provided on the housing 51. This can include the driver coils, or an additional set of control coils, as described above with respect to Figures 1 to 11.
  • the wedges 90 preferably have rounded edges to reduce damage to blood elements, however this also compromises the stiffness of the hydrodynamic bearing.
  • the combination of these wedges and a relative rotational speed cause a thrust force due to the squeezing of fluid through the tapered gap, as described by Reynolds' theory of lubrication. This radial thrust force is used to balance any radial forces encountered within the pump.
  • the third specific example relates to a single pump that can assist or replace the function of both left and right ventricles of a heart, known as a BiVAD.
  • a BiVAD a single pump that can assist or replace the function of both left and right ventricles of a heart
  • fluid is drawn from the left ventricle into the cavity 102 A via a canula connected to the inlet 105 A.
  • Fluid passes onto the cylindrical impeller 103, whose vanes 104A urge fluid via the volute 137A to the outlet 106A, returning to the circulatory system via a canula connected to the aorta.
  • This imparts sufficient a flow rate and pressure required by the systemic circulatory system, which in one example includes a pressure rise of lOOmmHg at a flow rate of 5 L/min.
  • fluid is drawn from the right ventricle into the cavity 102B via the canula connected to the inlet 105B.
  • Fluid passes onto the side 103B of impeller 103, which has vanes 104B that urge the fluid, via the volute 137B, to the outlet 106B.
  • the vanes 104B are designed to provide a flow rate and pressure suitable for the pulmonary circulatory system, which in one example is a pressure of 20 mmHg at a flow rate of 5 L/min. Fluid is transferred via a suitable canula connected to the pulmonary artery.
  • axial suspension and drive of the impeller may be achieved as described above with respect to either the first or second specific example.
  • the impeller 103 is rotated by coupling magnetic fields generated by the coils 111A, 11 IB, wound on respective stators 115A, 115B, to the driver magnets 109A, 109B embedded in the shroud 103D.
  • axial position can be controlled using a pure axial magnetic bearing located at the housing 101B, which couples with an iron only target in the shroud 103D.
  • radial position confrol can be controlled either using appropriate coil configurations which cooperate with driver magnets 109 provided in the central portion 103C of the impeller 103. Alternatively, this can be achieved using hydrodynamic suspension, as described above with respect to the second specific example.
  • the small clearance gap 8A and length of the cylindrical portion in this region acts to reduce the leakage flow from high pressure to low pressure sides by creating a suitable resistance to fluid flow, therefore minor pollution is experienced.
  • differential pressures and flow characteristics is achieved by utilising respective dimensions for the sets of vanes 104A, 104B, as shown in Figures 13H, to 13J.
  • the difference in pressure is achieved by providing different impeller vanes 104A, 104B on the high pressure impeller side 103 A and low pressure side 103B.
  • the vanes 104B on the impeller portion 103B are of a reduced length, as shown in Figure 13J, when compared to the vanes 104A on the impeller portion 103A.
  • the required flow rates and pressures can be achieved using the following dimensions:
  • Impeller end 103B radius R 12.5mm
  • the pressure difference may result in minimal blood flow from the left to the right sides of the pump.
  • this represents a flow of oxygenated blood into the unoxygenated blood, this does not represent a problem from a medical perspective.
  • the fluid pump as a heart assist device
  • the fluid pump it is possible for the fluid pump to be used for other purposes, and indeed any fluid pumping application where the pressure and flow rates fall within the operating parameters of the device.

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

Abstract

L'invention concerne une pompe à fluide qui comprend un boîtier définissant une cavité. La cavité comprend au moins une entrée et une sortie de fluide, et au moins un ensemble de bobines destiné à produire un champ magnétique. En fonctionnement, une turbine (3) est placée dans la cavité, laquelle comprend un corps et un certain nombre d'aubes (4A, 4B) placées sur le corps en vue d'entraîner le fluide de l'entrée vers la sortie, ainsi qu'un certain nombre d'aimants d'entraînement (9). En fonctionnement, la turbine est suspendue dans la cavité par couplage axial et mise en rotation par production d'un champ à l'aide des bobines.
PCT/AU2004/000600 2003-05-09 2004-05-07 Pompe a fluide WO2004098677A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
JP2006504034A JP2006525460A (ja) 2003-05-09 2004-05-07 流体ポンプ
AU2004236369A AU2004236369A1 (en) 2003-05-09 2004-05-07 Fluid pump

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
AU2003902255 2003-05-09
AU2003902255A AU2003902255A0 (en) 2003-05-09 2003-05-09 Motor

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WO2004098677A1 true WO2004098677A1 (fr) 2004-11-18

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AU (1) AU2003902255A0 (fr)
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WO2006053384A1 (fr) * 2004-11-17 2006-05-26 Queensland University Of Technology Pompe à fluide
WO2006133209A1 (fr) * 2005-06-06 2006-12-14 The Cleveland Clinic Foundation Pompe sanguine
WO2008017289A3 (fr) * 2006-08-06 2008-04-03 Mustafa Akdis Pompe à sang
WO2010118476A1 (fr) * 2009-04-16 2010-10-21 Bivacor Pty Ltd Dispositif de commande de pompe cardiaque
WO2010118475A1 (fr) * 2009-04-16 2010-10-21 Bivacor Pty Ltd Dispositif de commande de pompe cardiaque
US8008884B2 (en) 2007-07-17 2011-08-30 Brooks Automation, Inc. Substrate processing apparatus with motors integral to chamber walls
US8210829B2 (en) * 2006-04-26 2012-07-03 The Cleveland Clinic Foundation Two-stage rotodynamic blood pump with axially movable rotor assembly for adjusting hydraulic performance characteristics
US8267636B2 (en) 2007-05-08 2012-09-18 Brooks Automation, Inc. Substrate transport apparatus
US8283813B2 (en) 2007-06-27 2012-10-09 Brooks Automation, Inc. Robot drive with magnetic spindle bearings
WO2013165485A1 (fr) * 2012-05-04 2013-11-07 Ghsp, Inc. Pompe et moteur double équipé d'un dispositif de commande
US8659205B2 (en) 2007-06-27 2014-02-25 Brooks Automation, Inc. Motor stator with lift capability and reduced cogging characteristics
US8803513B2 (en) 2007-06-27 2014-08-12 Brooks Automation, Inc. Multiple dimension position sensor
US8823294B2 (en) 2007-06-27 2014-09-02 Brooks Automation, Inc. Commutation of an electromagnetic propulsion and guidance system
US9556873B2 (en) 2013-02-27 2017-01-31 Tc1 Llc Startup sequence for centrifugal pump with levitated impeller
US9562534B2 (en) 2012-05-04 2017-02-07 Ghsp, Inc. In-line dual pump and motor with control device
US9623161B2 (en) 2014-08-26 2017-04-18 Tc1 Llc Blood pump and method of suction detection
WO2017120449A2 (fr) 2016-01-06 2017-07-13 Bivacor Inc. Pompe cardiaque
US9752615B2 (en) 2007-06-27 2017-09-05 Brooks Automation, Inc. Reduced-complexity self-bearing brushless DC motor
US9850906B2 (en) 2011-03-28 2017-12-26 Tc1 Llc Rotation drive device and centrifugal pump apparatus employing same
US10052420B2 (en) 2013-04-30 2018-08-21 Tc1 Llc Heart beat identification and pump speed synchronization
US10077777B2 (en) 2014-05-09 2018-09-18 The Cleveland Clinic Foundation Artificial heart system implementing suction recognition and avoidance methods
US10087927B2 (en) 2014-05-01 2018-10-02 Ghsp, Inc. Electric motor with flux collector
WO2018187576A2 (fr) 2017-04-05 2018-10-11 Bivacor Inc. Entraînement et roulement de pompe cardiaque
US10117983B2 (en) 2015-11-16 2018-11-06 Tc1 Llc Pressure/flow characteristic modification of a centrifugal pump in a ventricular assist device
EP2461465B1 (fr) * 2009-07-29 2018-12-19 Thoratec Corporation Dispositif de mise en rotation et dispositif de pompe centrifuge
US10166318B2 (en) 2015-02-12 2019-01-01 Tc1 Llc System and method for controlling the position of a levitated rotor
US10245361B2 (en) 2015-02-13 2019-04-02 Tc1 Llc Impeller suspension mechanism for heart pump
WO2019139686A1 (fr) * 2018-01-10 2019-07-18 Tc1 Llc Pompe à sang implantable sans palier
US10371152B2 (en) 2015-02-12 2019-08-06 Tc1 Llc Alternating pump gaps
US10506935B2 (en) 2015-02-11 2019-12-17 Tc1 Llc Heart beat identification and pump speed synchronization
US10722631B2 (en) 2018-02-01 2020-07-28 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US11002566B2 (en) 2007-06-27 2021-05-11 Brooks Automation, Inc. Position feedback for self bearing motor
US11015585B2 (en) 2014-05-01 2021-05-25 Ghsp, Inc. Submersible pump assembly
CN113082507A (zh) * 2021-05-12 2021-07-09 苏州大学 一种运用于人工心脏的磁悬浮装置
US20210254623A1 (en) * 2020-02-13 2021-08-19 Levitronix Gmbh Pumping device, a single-use device and a method for operating a pumping device
US11185677B2 (en) 2017-06-07 2021-11-30 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
WO2022198279A1 (fr) * 2021-03-26 2022-09-29 Cardiobionic Pty Ltd Pompe à sang à suspension électromagnétique active en trois dimensions
US11511103B2 (en) 2017-11-13 2022-11-29 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11654275B2 (en) 2019-07-22 2023-05-23 Shifamed Holdings, Llc Intravascular blood pumps with struts and methods of use and manufacture
US11724089B2 (en) 2019-09-25 2023-08-15 Shifamed Holdings, Llc Intravascular blood pump systems and methods of use and control thereof
EP4226965A1 (fr) * 2022-02-15 2023-08-16 Medizinische Universität Wien Pompe à sang pour soutenir le débit cardiaque
US11964145B2 (en) 2019-07-12 2024-04-23 Shifamed Holdings, Llc Intravascular blood pumps and methods of manufacture and use
US12102815B2 (en) 2019-09-25 2024-10-01 Shifamed Holdings, Llc Catheter blood pumps and collapsible pump housings
US12104600B2 (en) 2007-02-27 2024-10-01 Miracor Medical Sa Device to assist the performance of a heart
US12121713B2 (en) 2019-09-25 2024-10-22 Shifamed Holdings, Llc Catheter blood pumps and collapsible blood conduits
WO2024242960A1 (fr) 2023-05-16 2024-11-28 Bivacor Inc. Calcul de paramètre d'une pompe d'assistance circulatoire
US12161857B2 (en) 2018-07-31 2024-12-10 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US12220570B2 (en) 2018-10-05 2025-02-11 Shifamed Holdings, Llc Intravascular blood pumps and methods of use

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WO2006053384A1 (fr) * 2004-11-17 2006-05-26 Queensland University Of Technology Pompe à fluide
WO2006133209A1 (fr) * 2005-06-06 2006-12-14 The Cleveland Clinic Foundation Pompe sanguine
US8992407B2 (en) 2005-06-06 2015-03-31 The Cleveland Clinic Foundation Blood pump
US9950101B2 (en) 2005-06-06 2018-04-24 The Cleveland Clinic Foundation Blood pump
US8177703B2 (en) 2005-06-06 2012-05-15 The Cleveland Clinic Foundation Blood pump
US11185678B2 (en) 2005-06-06 2021-11-30 The Cleveland Clinic Foundation Blood pump
US10369260B2 (en) 2005-06-06 2019-08-06 The Cleveland Clinic Foundation Blood pump
US8210829B2 (en) * 2006-04-26 2012-07-03 The Cleveland Clinic Foundation Two-stage rotodynamic blood pump with axially movable rotor assembly for adjusting hydraulic performance characteristics
WO2008017289A3 (fr) * 2006-08-06 2008-04-03 Mustafa Akdis Pompe à sang
US9616157B2 (en) 2006-08-06 2017-04-11 Mustafa Akdis Blood pump
US12270401B2 (en) 2007-02-27 2025-04-08 Miracor Medical Sa Device to assist the performance of a heart
US12264677B2 (en) 2007-02-27 2025-04-01 Miracor Medical Sa Device to assist the performance of a heart
US12104600B2 (en) 2007-02-27 2024-10-01 Miracor Medical Sa Device to assist the performance of a heart
US12117007B1 (en) 2007-02-27 2024-10-15 Miracor Medical Sa Device to assist the performance of a heart
US12270400B2 (en) 2007-02-27 2025-04-08 Miracor Medical Sa Device to assist the performance of a heart
US8267636B2 (en) 2007-05-08 2012-09-18 Brooks Automation, Inc. Substrate transport apparatus
US8283813B2 (en) 2007-06-27 2012-10-09 Brooks Automation, Inc. Robot drive with magnetic spindle bearings
US9752615B2 (en) 2007-06-27 2017-09-05 Brooks Automation, Inc. Reduced-complexity self-bearing brushless DC motor
US11002566B2 (en) 2007-06-27 2021-05-11 Brooks Automation, Inc. Position feedback for self bearing motor
US8659205B2 (en) 2007-06-27 2014-02-25 Brooks Automation, Inc. Motor stator with lift capability and reduced cogging characteristics
US8803513B2 (en) 2007-06-27 2014-08-12 Brooks Automation, Inc. Multiple dimension position sensor
US8823294B2 (en) 2007-06-27 2014-09-02 Brooks Automation, Inc. Commutation of an electromagnetic propulsion and guidance system
US9024488B2 (en) 2007-06-27 2015-05-05 Brooks Automation, Inc. Robot drive with magnetic spindle bearings
US8237391B2 (en) 2007-07-17 2012-08-07 Brooks Automation, Inc. Substrate processing apparatus with motors integral to chamber walls
US8680803B2 (en) 2007-07-17 2014-03-25 Brooks Automation, Inc. Substrate processing apparatus with motors integral to chamber walls
US8008884B2 (en) 2007-07-17 2011-08-30 Brooks Automation, Inc. Substrate processing apparatus with motors integral to chamber walls
US8632449B2 (en) 2009-04-16 2014-01-21 Bivacor Pty Ltd Heart pump controller
US8636638B2 (en) 2009-04-16 2014-01-28 Bivacor Pty Ltd Heart pump controller
AU2010237614B2 (en) * 2009-04-16 2013-11-07 Bivacor Pty Ltd Heart pump controller
US20120245680A1 (en) * 2009-04-16 2012-09-27 Bivacor Pty Ltd. Heart pump controller
EP2419159A4 (fr) * 2009-04-16 2017-07-19 Bivacor Pty Ltd Dispositif de commande de pompe cardiaque
CN102458498A (zh) * 2009-04-16 2012-05-16 毕瓦克私人有限公司 心脏泵控制器
WO2010118475A1 (fr) * 2009-04-16 2010-10-21 Bivacor Pty Ltd Dispositif de commande de pompe cardiaque
WO2010118476A1 (fr) * 2009-04-16 2010-10-21 Bivacor Pty Ltd Dispositif de commande de pompe cardiaque
EP2461465B1 (fr) * 2009-07-29 2018-12-19 Thoratec Corporation Dispositif de mise en rotation et dispositif de pompe centrifuge
EP3832861A1 (fr) * 2009-07-29 2021-06-09 Thoratec Corporation Dispositif de mise en rotation et dispositif de pompe centrifuge
EP3490122A1 (fr) * 2009-07-29 2019-05-29 Thoratec Corporation Dispositif de mise en rotation et dispositif de pompe centrifuge
US9850906B2 (en) 2011-03-28 2017-12-26 Tc1 Llc Rotation drive device and centrifugal pump apparatus employing same
US9115720B2 (en) 2012-05-04 2015-08-25 Ghsp, Inc. Dual pump and motor with control device
US9587639B2 (en) 2012-05-04 2017-03-07 Ghsp, Inc. Side-by-side dual pump and motor with control device
US9562534B2 (en) 2012-05-04 2017-02-07 Ghsp, Inc. In-line dual pump and motor with control device
WO2013165485A1 (fr) * 2012-05-04 2013-11-07 Ghsp, Inc. Pompe et moteur double équipé d'un dispositif de commande
US9556873B2 (en) 2013-02-27 2017-01-31 Tc1 Llc Startup sequence for centrifugal pump with levitated impeller
US10052420B2 (en) 2013-04-30 2018-08-21 Tc1 Llc Heart beat identification and pump speed synchronization
US10087927B2 (en) 2014-05-01 2018-10-02 Ghsp, Inc. Electric motor with flux collector
US11015585B2 (en) 2014-05-01 2021-05-25 Ghsp, Inc. Submersible pump assembly
US10077777B2 (en) 2014-05-09 2018-09-18 The Cleveland Clinic Foundation Artificial heart system implementing suction recognition and avoidance methods
US9623161B2 (en) 2014-08-26 2017-04-18 Tc1 Llc Blood pump and method of suction detection
US10856748B2 (en) 2015-02-11 2020-12-08 Tc1 Llc Heart beat identification and pump speed synchronization
US10506935B2 (en) 2015-02-11 2019-12-17 Tc1 Llc Heart beat identification and pump speed synchronization
US11712167B2 (en) 2015-02-11 2023-08-01 Tc1 Llc Heart beat identification and pump speed synchronization
US12213766B2 (en) 2015-02-11 2025-02-04 Tc1 Llc Heart beat identification and pump speed synchronization
US10371152B2 (en) 2015-02-12 2019-08-06 Tc1 Llc Alternating pump gaps
US12285598B2 (en) 2015-02-12 2025-04-29 Tc1 Llc System and method for controlling the position of a levitated rotor
US11724097B2 (en) 2015-02-12 2023-08-15 Tc1 Llc System and method for controlling the position of a levitated rotor
US11781551B2 (en) 2015-02-12 2023-10-10 Tc1 Llc Alternating pump gaps
US10166318B2 (en) 2015-02-12 2019-01-01 Tc1 Llc System and method for controlling the position of a levitated rotor
US11015605B2 (en) 2015-02-12 2021-05-25 Tc1 Llc Alternating pump gaps
US10874782B2 (en) 2015-02-12 2020-12-29 Tc1 Llc System and method for controlling the position of a levitated rotor
US10245361B2 (en) 2015-02-13 2019-04-02 Tc1 Llc Impeller suspension mechanism for heart pump
US11639722B2 (en) 2015-11-16 2023-05-02 Tc1 Llc Pressure/flow characteristic modification of a centrifugal pump in a ventricular assist device
US10888645B2 (en) 2015-11-16 2021-01-12 Tc1 Llc Pressure/flow characteristic modification of a centrifugal pump in a ventricular assist device
US10117983B2 (en) 2015-11-16 2018-11-06 Tc1 Llc Pressure/flow characteristic modification of a centrifugal pump in a ventricular assist device
WO2017120451A2 (fr) 2016-01-06 2017-07-13 Bivacor Inc. Pompe cardiaque avec commande de vitesse de rotation de turbine
WO2017120449A2 (fr) 2016-01-06 2017-07-13 Bivacor Inc. Pompe cardiaque
US11154703B2 (en) 2016-01-06 2021-10-26 Bivacor Inc. Heart pump
US11833341B2 (en) 2016-01-06 2023-12-05 Bivacor Inc. Heart pump
US10543301B2 (en) 2016-01-06 2020-01-28 Bivacor Inc. Heart pump
US11826558B2 (en) 2016-01-06 2023-11-28 Bivacor Inc. Heart pump with impeller rotational speed control
US11278712B2 (en) 2016-01-06 2022-03-22 Bivacor Inc. Heart pump with impeller rotational speed control
US10960200B2 (en) 2016-01-06 2021-03-30 Bivacor Inc. Heart pump with impeller axial position control
CN110709114A (zh) * 2017-04-05 2020-01-17 毕瓦克公司 心脏泵驱动器和轴承
CN110709114B (zh) * 2017-04-05 2023-10-31 毕瓦克公司 心脏泵驱动器和轴承
AU2018250273A8 (en) * 2017-04-05 2023-03-23 Bivacor Inc. Heart pump drive and bearing
US11654274B2 (en) 2017-04-05 2023-05-23 Bivacor Inc. Heart pump drive and bearing
WO2018187576A2 (fr) 2017-04-05 2018-10-11 Bivacor Inc. Entraînement et roulement de pompe cardiaque
AU2018250273B2 (en) * 2017-04-05 2023-06-08 Bivacor Inc. Heart pump drive and bearing
WO2018187576A3 (fr) * 2017-04-05 2019-01-10 Bivacor Inc. Entraînement et roulement de pompe cardiaque
US11717670B2 (en) 2017-06-07 2023-08-08 Shifamed Holdings, LLP Intravascular fluid movement devices, systems, and methods of use
US11185677B2 (en) 2017-06-07 2021-11-30 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
US11511103B2 (en) 2017-11-13 2022-11-29 Shifamed Holdings, Llc Intravascular fluid movement devices, systems, and methods of use
WO2019139686A1 (fr) * 2018-01-10 2019-07-18 Tc1 Llc Pompe à sang implantable sans palier
EP4275737A3 (fr) * 2018-01-10 2023-12-20 Tc1 Llc Pompe à sang implantable sans palier
US10973967B2 (en) 2018-01-10 2021-04-13 Tc1 Llc Bearingless implantable blood pump
US11229784B2 (en) 2018-02-01 2022-01-25 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US10722631B2 (en) 2018-02-01 2020-07-28 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US12076545B2 (en) 2018-02-01 2024-09-03 Shifamed Holdings, Llc Intravascular blood pumps and methods of use and manufacture
US12161857B2 (en) 2018-07-31 2024-12-10 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US12220570B2 (en) 2018-10-05 2025-02-11 Shifamed Holdings, Llc Intravascular blood pumps and methods of use
US11964145B2 (en) 2019-07-12 2024-04-23 Shifamed Holdings, Llc Intravascular blood pumps and methods of manufacture and use
US11654275B2 (en) 2019-07-22 2023-05-23 Shifamed Holdings, Llc Intravascular blood pumps with struts and methods of use and manufacture
US11724089B2 (en) 2019-09-25 2023-08-15 Shifamed Holdings, Llc Intravascular blood pump systems and methods of use and control thereof
US12102815B2 (en) 2019-09-25 2024-10-01 Shifamed Holdings, Llc Catheter blood pumps and collapsible pump housings
US12121713B2 (en) 2019-09-25 2024-10-22 Shifamed Holdings, Llc Catheter blood pumps and collapsible blood conduits
US11619236B2 (en) * 2020-02-13 2023-04-04 Levitronix Gmbh Pumping device, a single-use device and a method for operating a pumping device
US20210254623A1 (en) * 2020-02-13 2021-08-19 Levitronix Gmbh Pumping device, a single-use device and a method for operating a pumping device
WO2022198279A1 (fr) * 2021-03-26 2022-09-29 Cardiobionic Pty Ltd Pompe à sang à suspension électromagnétique active en trois dimensions
CN113082507A (zh) * 2021-05-12 2021-07-09 苏州大学 一种运用于人工心脏的磁悬浮装置
CN113082507B (zh) * 2021-05-12 2023-01-13 苏州大学 一种运用于人工心脏的磁悬浮装置
EP4226965A1 (fr) * 2022-02-15 2023-08-16 Medizinische Universität Wien Pompe à sang pour soutenir le débit cardiaque
WO2023156908A1 (fr) 2022-02-15 2023-08-24 Medizinische Universität Wien Pompe à sang destinée à assister l'activité cardiaque
WO2024242960A1 (fr) 2023-05-16 2024-11-28 Bivacor Inc. Calcul de paramètre d'une pompe d'assistance circulatoire

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