WO2015039605A1 - Pompe à sang à écoulement axial à suspension automatique implantée - Google Patents

Pompe à sang à écoulement axial à suspension automatique implantée Download PDF

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Publication number
WO2015039605A1
WO2015039605A1 PCT/CN2014/086750 CN2014086750W WO2015039605A1 WO 2015039605 A1 WO2015039605 A1 WO 2015039605A1 CN 2014086750 W CN2014086750 W CN 2014086750W WO 2015039605 A1 WO2015039605 A1 WO 2015039605A1
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WIPO (PCT)
Prior art keywords
stator
blood pump
magnetic steel
suspended
pump according
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PCT/CN2014/086750
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English (en)
Chinese (zh)
Inventor
刘中民
范慧敏
周连第
陈应生
金如麟
叶亮
Original Assignee
上海微创医疗器械（集团）有限公司
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Publication of WO2015039605A1 publication Critical patent/WO2015039605A1/fr

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    • 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
    • A61M60/10—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
    • 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
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • A61M60/806—Vanes or blades
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices

Definitions

  • the present invention relates to the field of medical device technology, and in particular to an implantable ventricular assist device.
  • Heart failure (heart failure) is the most common diagnosis of cardiovascular patients, and it is also the disease with the highest medical cost. Internationally, heart failure has been an important issue to be solved in this century. Due to the lack of donors, approximately 30% of patients preparing for heart transplantation die of cardiac function deterioration while waiting for heart delivery.
  • Ventricular Assist Devices VAD
  • NASH National Institutes of Health
  • RFPs Request For Proposals
  • ventricular assist devices As one of the methods of heart failure treatment.
  • the pump system of the general ventricular assist device uses the domestic VZ-IIA blood pump and the Berlin Heart Incor 1 as an example, and the motor magnetic steel rotor, the blood pump rotor and the bearing or the magnetic levitation control body are placed in the blood flow channel, so that not only The volume and weight of the entire pump system is increased, and the placement of the rotor magnet and the magnetic levitation control body in the blood flow path also greatly reduces the blood flow, and the air gap between the stator and the rotor of the motor increases, and the required power also increases.
  • the existing implantable bearing blood pump on the market the bearing is easy to wear, easy to vibrate, short service life, low reliability, and easy to form a thrombus.
  • the magnetic levitation control system of the magnetic levitation blood pump has a complicated structure, a large volume, a heavy weight, and high requirements on parameters such as control operation balance and vibration amplitude. Therefore, the clinical application of the ventricular assist device not only requires small size, light weight, and is not easy to thrombosis, but also requires the device to operate in balance, low vibration, and low noise, so as to improve the comfort of the patient during use.
  • the object of the present invention is to provide an implantable self-suspended axial blood pump, which is smaller in volume, lighter in weight, does not stop rotating due to mechanical failure of the bearing, has higher reliability, and avoids the position at the bearing. Form a thrombus.
  • an embodiment of the present invention discloses an implantable self-suspended shaft blood flow pump comprising: a stator and a rotor, wherein the stator includes: a stator core (2), a stator coil (3), and a motor bracket ( 4); the rotor includes: a magnetic steel (5) containing a magnetic material and a built-in paddle (8);
  • the radial direction from the inside to the outside is: built-in paddle (8), magnetic steel (5), motor bracket (4), stator coil (3) and stator core (2) ;
  • the rotor comprises a hollow annular magnetic steel and a built-in paddle fixed therein, the rotor is directly placed in the middle of the stator, and the stator and the rotor are not directly or indirectly connected by bearings, and the rotor is self-detached from the contact with the inner wall of the stator when rotating. Self-suspending state. Because there is no bearing or magnetic suspension control system, the blood pump is smaller and lighter.
  • the present invention does not stop the rotation due to mechanical failure of the bearing, is more reliable, and avoids the formation of a thrombus at the bearing position. At the same time, no complicated magnetic levitation control system is needed. The cost of the blood pump is lower and the reliability is better.
  • stator coil (3) adopts a hollow cup winding, which not only solves the problem that the small-sized stator is difficult to go offline, but also has no cogging in the stator core, completely eliminating the essential rotation caused by the tooth harmonic magnetic field. fluctuation.
  • the structure with the built-in paddle (8) in front and the outer paddle (9) in the back can ensure that the blood enters the flow channel first, and is firstly subjected to the rotation of the blade by the built-in paddle (8) to ensure maximum Part of the blood passes through the main channel, and the trace blood passes through the tip of the outer blade (9) disposed at the back, which ensures that the blood smoothly branches in the main and branch channels, smoothly passes, and does not cause congestion. Thrombosis.
  • the leaf cut surface of the built-in blade (8) and the outer blade (9) adopts a blade-shaped blade shape of a marine ducted propeller, and when blood flows through the airfoil-shaped cut surface, a positive surface appears on the leaf cut surface.
  • Pressure, negative pressure on the leaf back of the leaf cut surface, the pressure difference between the leaf surface and the leaf back can improve the efficiency of the blood pump and increase the pressure head.
  • the two-phase conduction, three-phase six-state conduction mode not only improves the utilization of the winding, reduces the volume and weight, but also reduces the magnetic state angle and reduces the rotational fluctuation.
  • outlet right-handed stator (7) is fixed to the motor bracket (4) to adjust the direction of blood flow outflow.
  • the circuit realizes the function of identifying the position of the rotor and the self-starting function, and functions as a position sensor, which can cancel the conventional position sensor, thereby reducing the difficulty of sealing, improving the reliability, simplifying the structure, and reducing the structure. volume.
  • the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.003D to 0.019D, preferably between 0.0042D and 0.0048D, and D is the inner diameter of the cross section of the magnetic steel (5).
  • the range of D is preferably between 5 and 32 mm, more preferably between 6.7 and 25 mm, which has the best effect of reducing vibration.
  • the effective value of vibration acceleration is reduced by 1 ⁇ 2m/s 2
  • the effective value of vibration speed is reduced by 3 ⁇ 5mm/s
  • the effective value of vibration displacement is reduced by 13 ⁇ 33 ⁇ m.
  • the gap between the motor bracket (4) and the magnetic steel (5) refers to one-half of the difference between the inner diameter of the motor bracket and the outer diameter of the magnetic steel.
  • the magnetic steel (5) may also contain a biocompatible material such as a titanium alloy, a polymer material, or the like.
  • the motor bracket is a layer structure which is coated on the inner diameter surface of the stator coil (3), and may be any insulating material or combination of insulating materials, or may be a film structure, a plating layer, a spray paint or the like.
  • the thickness of the magnetic steel (5) ranges from 1.5 mm to 3.5 mm, preferably between 2.0 mm and 3.0 mm, more preferably between 2.3 mm and 2.8 mm, and the blood pump involved in CN 201208423Y Compared with the structure (removing the bearing), the rotation speed can be increased by about 2000 rpm, and the current can be reduced and the power consumption can be reduced.
  • FIG. 1 is a schematic structural view (cross-sectional view) of an implantable self-suspended shaft blood flow pump according to a first embodiment of the present invention
  • FIG. 2 is a schematic structural view of a slurry shaft integrated tandem blade according to a first embodiment of the present invention
  • FIG. 3 is a schematic view showing a blade cut surface of a slurry shaft integrated tandem blade according to a first embodiment of the present invention
  • FIG. 4 is a schematic radial cross-sectional view showing a structure of a stator and a rotor in a first embodiment of the present invention
  • FIG. 5 is a schematic structural view (cross-sectional view) of an initial state of an implantable self-suspended shaft blood flow pump according to a first embodiment of the present invention
  • FIG. 6 is a schematic structural view (cross-sectional view) of a suspension state of an implantable self-suspended shaft blood flow pump according to a first embodiment of the present invention
  • FIG. 7 is a schematic structural view of an implantable self-suspended shaft blood flow pump in a first embodiment of the present invention. (profile view).
  • a first embodiment of the invention relates to an implantable self-suspended shaft blood flow pump.
  • the implantable self-suspended shaft blood pump comprises: a stator and a rotor, wherein the stator comprises: a stator core (2), a stator coil (3) and a motor bracket (4); and the rotor comprises: a magnetic steel containing a magnetic material (5) ) and built-in paddles (8);
  • the radial direction from the inside to the outside is: built-in paddle (8), magnetic steel (5), motor bracket (4), stator coil (3) and stator core (2) .
  • the inner envelope of the cross section of the motor bracket (4) is circular;
  • the magnetic steel (5) has an axial central hole, and the outer envelope of the cross section of the magnetic steel (5) is circular;
  • stator and the rotor are not directly or indirectly connected by bearings; wherein the indirect connections include magnetic levitation and the like.
  • the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.003D to 0.019D, and D is the inner diameter of the cross section of the magnetic steel (5).
  • the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.0042D to 0.0048D, and D is the inner diameter of the cross section of the magnetic steel (5).
  • the outer diameter, inner diameter and length range (mm) of the stator core according to the present invention can be appropriately adjusted according to the design of the present invention. Among them, the outer diameter, inner diameter and length range of the stator core (mm) ( ⁇ 10.5-48.6) ⁇ ( ⁇ 8.4-40.6) ⁇ (11.5-100.0); outer diameter, inner diameter and length range (mm) of the stator coil: ( ⁇ 8.4-40.6) ⁇ ( ⁇ 7.5-35.5) ⁇ (12.5 -102.5).
  • the outer diameter, inner diameter and length range (mm) of the stator core ( ⁇ 14.5-37.7) ⁇ ( ⁇ 11.4-29.6) ⁇ (11.5-30.0); outer diameter, inner diameter and length range (mm) of the stator coil :( ⁇ 11.4-29.6) ⁇ ( ⁇ 10.3-26.6) ⁇ (12.5-32.5). More preferably, the outer diameter, the inner diameter and the length range (mm) of the stator core are: ( ⁇ 20.3-37.7) ⁇ ( ⁇ 15.9-29.6) ⁇ (16.1-30.0), the outer diameter, the inner diameter and the length range of the stator coil ( Mm) can be ( ⁇ 15.9-29.6) ⁇ ( ⁇ 14.3-26.6) ⁇ (17.5-32.5).
  • FIG. 1 is a schematic structural view (cross-sectional view) of a preferred implantable self-suspended axial blood pump.
  • the implantable self-suspended shaft blood pump includes a stator and a rotor, wherein the stator includes a stator core (2), a stator coil (3), and a motor bracket (4).
  • the rotor includes: a magnetic ring magnet (5) having a cylindrical inner wall and a built-in paddle (8).
  • the magnetic steel (5) containing a magnetic material may further contain other materials as long as the permanent magnets are contained therein.
  • stator and the rotor are not directly or indirectly connected by bearings.
  • the indirect connection includes magnetic levitation and the like.
  • Bearings in various embodiments of the present invention include directly coupled bearings, as well as bearings that are not directly connected, such as magnetic bearings.
  • the stator coil (3) is inside the stator core (2).
  • the stator coil (3) is used to generate an alternating magnetic field that drives the rotation of the magnetic steel (5) after energization.
  • the stator is a hollow cylindrical structure. Because of the existence of the stator, the magnetic steel (5) made of permanent magnet material can be firmly attracted to the middle portion of the stator by the action of the magnetic force, and is not generated by the rotation. The reaction forces the rotor out of the middle of the stator.
  • the stator coil (3) uses a hollow cup winding.
  • a motor bracket (4) is fixed on the inner wall of the stator, and the motor bracket (4) has a hollow inner wall in which the rotor is placed.
  • the inner envelope of the cross section of the motor bracket (4) is circular; the magnetic steel (5) has an axial central hole, and the outer envelope of the cross section of the magnetic steel (5) is circular.
  • the hollow inner wall of the motor bracket (4) may be a regular cylindrical shape, an irregular cylindrical shape or a conical shape, or the like, as long as the inner envelope of the cross section of the motor bracket (4) is circular. can.
  • the outer wall of the magnetic steel (5) may be a regular cylindrical shape, an irregular cylindrical shape or a conical shape, or the like, as long as the outer envelope of the cross section of the magnetic steel (5) is circular.
  • the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.003D to 0.019D, and D is the inner diameter of the cross section of the magnetic steel (5).
  • the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.0042D to 0.0048D, and D is the inner diameter of the cross section of the magnetic steel (5).
  • the thickness of the magnetic steel (5) ranges from 1.5 mm to 3.5 mm, preferably between 2.0 mm and 3.0 mm, more preferably between 2.3 mm and 2.8 mm. More preferably, the thickness is 2.8 mm, the rotation speed can be increased by about 2000 rpm, and the current can be reduced by 0.1 A, compared with the blood pump structure (removing the bearing) of CN 201208423Y.
  • the stator coil (3) adopts a hollow cup winding, which not only solves the problem of difficulty in lowering the stator of the small size, but also has no cogging in the stator core, completely eliminating the inherent rotational fluctuation caused by the tooth harmonic magnetic field.
  • stator coil (3) is also Instead of a hollow cup winding, other coil forms can be used.
  • the stator adopts a two-phase conduction, three-phase six-state conduction mode.
  • the two-phase conduction and three-phase six-state conduction mode not only improves the utilization of the winding, reduces the volume and weight, but also reduces the magnetic state angle and reduces the rotational fluctuation.
  • stator may also employ other conductive modes, and is not limited to only two-phase conduction, three-phase six-state conductive modes.
  • a motor housing (1) is also attached to the outside of the stator.
  • the utility model further comprises: an outlet right-handed stator (7), the outlet right-handed stator (7) is placed at the blood outlet end of the implantable self-suspended shaft blood pump, and is fixed with the motor bracket (4), Adjust the direction of blood outflow to further reduce rotational fluctuations.
  • the central axis of the magnetic steel (5) is parallel to the central axis of the stator coil (3).
  • the magnetic steel (5) is a cylindrical magnetic ring made of a neodymium iron boron permanent magnet material and radially magnetized and a pair of poles.
  • Magnetic steel (5) adopts NdFeB permanent magnet material with high residual magnetic induction intensity, and adopts radial magnetization and a pair of pole cylindrical magnetic ring column steel, which can be under the large electromagnetic air gap of hollow cup winding. It can still produce a strong air gap magnetic field, which reduces the volume and weight of the motor.
  • the one-pole integral cylindrical magnetic steel is more likely to ensure uniform mass, reduce the dynamic imbalance under high-speed motion, and because it does not exist.
  • the single-sided magnetic pulling force makes the operation smooth and improves the comfort of use.
  • a position sensor that determines the relative position between the stator and the rotor is not included in the blood pump.
  • the magnetic steel (5) has an axial central hole in which the built-in paddle (8) is placed, and the blade tip of the built-in paddle (8) is in close contact with or fixed to the inner wall of the central hole.
  • the inner bore of the magnetic steel (5) constitutes the main flow of blood flow.
  • the main channel in the inner hole of the magnetic steel (5) has no other obstructions, so the flow path is unobstructed. Xu Da blood flow smoothly passed.
  • it also includes a paddle shaft (10), and/or an external paddle (9).
  • the outer paddle (9) is larger than the inner paddle (8), and the outer paddle (9) is adjacent to the blood outlet end of the implantable self-suspended shaft blood pump, and is placed outside the central hole of the magnetic steel (5).
  • the built-in paddle (8) constitutes a pulp shaft-integrated tandem blade (6).
  • the outer paddle (9) and the built-in paddle (8) are integrally connected in series to the paddle shaft (10).
  • the two can also be directly connected without using a paddle shaft, as shown in FIG.
  • the rotor is designed in the form of a tandem blade, and a tandem structure in which the built-in paddle (8) is in front and the outer paddle (9) is behind is used.
  • the diameter of the rotor blade is limited, and the flow path is further divided into a main flow path and a branch flow path.
  • the concept of a tandem propeller in a marine propeller special propeller is adopted, and the blood pump is used.
  • the rotor is designed in the form of a tandem blade.
  • the so-called tandem blade refers to the installation of different sizes of blades on the same shaft and rotates at the same speed. This type of tandem blade is especially suitable for the narrow flow path of the implanted blood pump and the diameter of the rotor is limited. happening.
  • the rotor may not be a tandem blade, but other forms of blades, such as continuous blades, built-in.
  • the paddles and the outer blades can be connected to each other without a paddle shaft or the like.
  • the blade section of the built-in blade (8) and the external blade (9) is in the form of a wing-shaped blade of a marine ducted propeller.
  • the blade cut surface of the built-in blade (8) and the external blade (9) adopts the airfoil-shaped blade cut surface of the marine duct propeller.
  • a positive pressure appears on the leaf cut surface leaf.
  • Negative pressure occurs on the back of the cut leaf, and the pressure difference between the leaf surface and the leaf back can increase the efficiency of the blood pump and increase the pressure head.
  • the blade sections of the inner blade (8) and the outer blade (9) may also be shaped without the airfoil blade of the marine conduit propeller.
  • other forms may be used, for example, in the form of a flat leaf cut of a general pump.
  • the pump body rotor employs a wing-shaped blade section and large and small tandem rotors, particularly large and small tandem rotor blades.
  • the data shows that at a speed of 7500 rpm to 8000 rpm and a pressure of 90 mmHg to 100 mmHg, the flow rate of the large and small rotor blades is 2 liters/minute larger than that of the single small rotor blade.
  • 2 is a schematic view showing the structure of the slurry shaft integrated tandem blade.
  • Fig. 3 is a schematic view showing the blade cut surface of the slurry shaft integrated tandem blade and its force.
  • the slurry shaft integrated tandem blade (6) forms a mainstream flow (11) and (12) of blood flow between the inner wall of the motor bracket (4) and the inner hole of the magnetic steel (5); the magnetic steel (5)
  • the outer wall and the inner wall of the motor bracket (4) constitute branch passages (13) and (14) for blood flow.
  • the built-in paddle (8) in front and the outer paddle (9) in the rear structure it can ensure that blood enters the flow channel from the blood flow inlet (15), and then the built-in tandem blade (8) rotates the blade first.
  • the role is to ensure that most of the blood passes through the main channel, and the trace blood is passed through the tip of the outer blade (9) disposed behind, so that the blood can be smoothly split in the main and branch channels, and the flow is smooth. Pass, no congestion thrombosis.
  • the implantable self-suspended shaft blood pump is used for the implantable ventricular assist device, there is a high requirement for the structural sealing.
  • a conventional brushless DC motor position sensor is used, the sensor stator Hall element is used.
  • the present invention uses a circuit to realize the function of identifying the rotor position and self-starting, and functions as a position sensor, which can cancel the conventional brushless The necessary position sensor for the DC motor, so that Reducing the difficulty of sealing, improving reliability, simplifying the structure and reducing the volume.
  • the rotor comprises a hollow cylindrical magnetic steel and a built-in paddle fixed therein, the rotor is directly placed in the middle of the stator, and the stator and the rotor are not directly or indirectly connected by bearings, and the rotor is free from contact with the inner wall of the stator when rotating, Self-suspended. Because no bearing or magnetic levitation control is used, the blood pump is smaller in size, lighter in weight, does not stop rotating due to mechanical failure of the bearing, is more reliable, and avoids the formation of a thrombus at the bearing position.
  • FIG. 4 is a schematic radial cross-sectional view of the stator and rotor structure.
  • stator coil (3) When the stator coil (3) is energized, an air gap between the inner wall of the stator coil (3) and the outer wall of the magnetic steel (5) generates a rotating magnetic field to drive the magnetic steel (5) to rotate, due to the centrifugal force of the magnetic steel, magnetic
  • the steel instantaneously disengages from the initial state of contact with the stator coil, and lies on the inner wall of the motor bracket (4), and the medium is an incompressible fluid, and the magnetic steel quickly reaches a state of suspension rotation coaxial with the stator coil, and drives the magnetic steel.
  • the integrated paddle shaft integrated serial blade (6) rotates together, and blood is sucked from the blood flow inlet (15) of the pump body and flows out from the outlet.
  • FIG. 5 is a schematic structural view (cross-sectional view) of the initial state of the implantable self-suspended axial blood pump
  • FIG. 6 is a schematic structural view (cross-sectional view) of the floating state of the implantable self-suspended axial blood pump, wherein the number is 20 Indicates the outer diameter of the magnetic steel, and 21 indicates the inner diameter of the motor bracket.
  • the implantable self-suspended axial blood pump has the advantages of simple structure, small volume, light weight, blood bifurcation by the main channel and the branch channel, smooth flow, no congestion and thrombus, no bearing friction, balanced operation, comfortable use, and blood pump efficiency. High, hemolysis and anti-thrombosis properties, fully suitable for use as an implantable ventricular assist device. Based on the above principles, the inventors have developed prototypes of various sizes, all of which can operate normally.
  • the outer diameter, inner diameter and length of the stator core may be (mm): 10.5 ⁇ 8.7 ⁇ 11.5; 14.5 ⁇ 12.4 ⁇ 15.5; 20.5 ⁇ 17.7 ⁇ 30; 29 ⁇ 22.8 ⁇ 33; 35.5 ⁇ 29.6 ⁇ 60;
  • the outer diameter, inner diameter and length of the motor coil may be (mm): 8.7 x 7.5 x 12.5; 12.4 x 10.3 x 17.5; 17.7 x 12.6 x 32.5; 22.8 x 20.5 x 38; 29.6 x 26.6 x 65.5.
  • the prototype can be started and stopped in all directions, and can operate normally under the impact of a certain external force (impact or sway, etc.).
  • the inventor performed a fatigue test on the implantable self-suspended shaft blood pump and recorded it in real time by a computer, wherein the prototype can also operate normally in the case of intermittent start and stop.
  • the self-suspended shaft blood pump body is optimized, compact in structure, has few main channel nodes, and has good axial sealing performance.
  • the pump body can be significantly shortened.
  • the outer diameter, inner diameter and length range (mm) of the motor core according to the present invention can be appropriately adjusted according to the design of the present invention.
  • the rotational speed of the blood pump ranges from 4000 rpm to 8000 rpm, and the corresponding flow rate varies from 2 to 6 L/min under the same pressure (100 mmHg).
  • the rotation speed is 8000 rpm, the corresponding flow rate is about 6 L/min.
  • the speed can be further increased, and the relevant indicators such as the corresponding flow rate also rise.
  • the axial flow self-suspending pump of the present invention can continuously rotate for one year and four months or more.

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  • 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)
  • Vascular Medicine (AREA)
  • External Artificial Organs (AREA)

Abstract

L'invention concerne une pompe à sang à écoulement axial à suspension automatique implantée, comprenant un stator et un rotor ; le stator comprend un noyau de fer de stator (2), une bobine de stator (3) et un support de moteur (4) ; le rotor comprend un acier magnétique (5) comportant un matériau magnétique et des pales intégrées (8) ; les pales intégrées (8), l'acier magnétique (5), le support de moteur (4), la bobine de stator (3) et le noyau de fer de stator (2) sont disposés de manière séquentielle dans une direction radiale de l'intérieur vers l'extérieur dans la section transversale de la pompe à sang ; le stator et le rotor sont reliés sans paliers ; le rotor est dans un état de suspension automatique lorsqu'il tourne ; dans la structure de la pompe à sang, les pales intégrées (8) sont disposées à l'avant, et les pales (9) à placer à l'extérieur sont disposées à l'arrière, et le plan tangent des pales prend la forme du plan tangent d'une pale en forme d'ailette d'une hélice de conduit marin, de telle sorte que le sang peut se séparer doucement et s'écouler dans des vaisseaux principaux et ramifiés.
PCT/CN2014/086750 2013-09-17 2014-09-17 Pompe à sang à écoulement axial à suspension automatique implantée WO2015039605A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN201310425934.5 2013-09-17
CN201310425934.5A CN104436338B (zh) 2013-09-17 2013-09-17 植入式自悬浮轴流血泵

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3313471A4 (fr) * 2015-06-29 2019-02-20 Tc1 Llc Dispositifs d'assistance ventriculaire munis d'un rotor creux et procédés d'utilisation
US11368081B2 (en) 2018-01-24 2022-06-21 Kardion Gmbh Magnetic coupling element with a magnetic bearing function
US11754075B2 (en) 2018-07-10 2023-09-12 Kardion Gmbh Impeller for an implantable, vascular support system
US11944805B2 (en) 2020-01-31 2024-04-02 Kardion Gmbh Pump for delivering a fluid and method of manufacturing a pump
US12005248B2 (en) 2018-05-16 2024-06-11 Kardion Gmbh Rotor bearing system

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4779614A (en) * 1987-04-09 1988-10-25 Nimbus Medical, Inc. Magnetically suspended rotor axial flow blood pump
US5707218A (en) * 1995-04-19 1998-01-13 Nimbus, Inc. Implantable electric axial-flow blood pump with blood cooled bearing
CN1833736A (zh) * 2005-03-17 2006-09-20 张杰民 搏动轴流血泵
CN201020069Y (zh) * 2007-04-29 2008-02-13 李国荣 心尖室壁内微型轴流泵
CN201150675Y (zh) * 2007-12-29 2008-11-19 同济大学附属东方医院 泵机合一可植入式轴流血泵流道结构
CN201208423Y (zh) * 2008-01-17 2009-03-18 同济大学附属东方医院 泵机合一植入式微型轴流血泵
CN201437016U (zh) * 2009-03-26 2010-04-14 同济大学附属东方医院 植入式心室辅助装置
CN102743801A (zh) * 2011-04-19 2012-10-24 薛恒春 无轴端磁液悬浮轴流血泵
CN103316387A (zh) * 2012-03-19 2013-09-25 上海市东方医院 植入式自悬浮轴流血泵

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5211546A (en) * 1990-05-29 1993-05-18 Nu-Tech Industries, Inc. Axial flow blood pump with hydrodynamically suspended rotor
JP2001207988A (ja) * 2000-01-26 2001-08-03 Nipro Corp 磁気駆動型軸流ポンプ
DE10108810A1 (de) * 2001-02-16 2002-08-29 Berlin Heart Ag Vorrichtung zur axialen Förderung von Flüssigkeiten
CN1260477C (zh) * 2003-08-06 2006-06-21 上海第二医科大学附属新华医院 一种可分离式轴流泵
CN1239209C (zh) * 2003-09-09 2006-02-01 张杰民 磁驱动的轴流式心脏辅助泵
EP1738783A1 (fr) * 2005-07-01 2007-01-03 Universitätsspital Basel Pompe axiale avec une aube hélicoïdale
CN101121045A (zh) * 2006-08-07 2008-02-13 李国荣 一种用于心脏辅助的镶套式永磁叶轮轴流式血泵及其辅助方法
CN102019002A (zh) * 2010-12-03 2011-04-20 中山哈特人工心脏实验室有限公司 一种植入式中空微型轴流血泵
CN103191476B (zh) * 2012-08-03 2015-03-11 上海交通大学医学院附属上海儿童医学中心 一种单支点磁动力离心式血泵

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4779614A (en) * 1987-04-09 1988-10-25 Nimbus Medical, Inc. Magnetically suspended rotor axial flow blood pump
US5707218A (en) * 1995-04-19 1998-01-13 Nimbus, Inc. Implantable electric axial-flow blood pump with blood cooled bearing
CN1833736A (zh) * 2005-03-17 2006-09-20 张杰民 搏动轴流血泵
CN201020069Y (zh) * 2007-04-29 2008-02-13 李国荣 心尖室壁内微型轴流泵
CN201150675Y (zh) * 2007-12-29 2008-11-19 同济大学附属东方医院 泵机合一可植入式轴流血泵流道结构
CN201208423Y (zh) * 2008-01-17 2009-03-18 同济大学附属东方医院 泵机合一植入式微型轴流血泵
CN201437016U (zh) * 2009-03-26 2010-04-14 同济大学附属东方医院 植入式心室辅助装置
CN102743801A (zh) * 2011-04-19 2012-10-24 薛恒春 无轴端磁液悬浮轴流血泵
CN103316387A (zh) * 2012-03-19 2013-09-25 上海市东方医院 植入式自悬浮轴流血泵

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3313471A4 (fr) * 2015-06-29 2019-02-20 Tc1 Llc Dispositifs d'assistance ventriculaire munis d'un rotor creux et procédés d'utilisation
US10702641B2 (en) 2015-06-29 2020-07-07 Tc1 Llc Ventricular assist devices having a hollow rotor and methods of use
US11368081B2 (en) 2018-01-24 2022-06-21 Kardion Gmbh Magnetic coupling element with a magnetic bearing function
US11804767B2 (en) 2018-01-24 2023-10-31 Kardion Gmbh Magnetic coupling element with a magnetic bearing function
US12005248B2 (en) 2018-05-16 2024-06-11 Kardion Gmbh Rotor bearing system
US11754075B2 (en) 2018-07-10 2023-09-12 Kardion Gmbh Impeller for an implantable, vascular support system
US11944805B2 (en) 2020-01-31 2024-04-02 Kardion Gmbh Pump for delivering a fluid and method of manufacturing a pump

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