WO2015039605A1 - Implanted self-suspended axial flow blood pump - Google Patents

Abstract

An implanted self-suspended axial flow blood pump, comprising a stator and a rotor; the stator comprises a stator iron core (2), a stator coil (3) and a motor bracket (4); the rotor comprises a magnetic steel (5) comprising magnetic material and built-in blades (8); the built-in blades (8), the magnetic steel (5), the motor bracket (4), the stator coil (3) and the stator iron core (2) are sequentially disposed in a radial direction from inward to outward in the cross section of the blood pump; the stator and the rotor are connected without bearings; the rotor is in a self-suspended state when rotating; in the structure of the blood pump, the built-in blades (8) are disposed in the front, and the blades (9) to be externally disposed are arranged in the rear, and the tangent plane of the blades take the form of the tangent plane of awing-shaped blade of a marine duct propeller, such that blood is ensured to smoothly bifurcate and flow in main and branch vessels.

Description

Implantable self-suspended shaft blood pump Technical field

The present invention relates to the field of medical device technology, and in particular to an implantable ventricular assist device.

Background technique

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.

The emergence and development of Ventricular Assist Devices (VAD) has made new treatments for heart failure. Since 1981, the National Institutes of Health (NIH) Initiate RFPs (a Request For Proposals) program for the development of "implantable ventricular assist devices that enable patients to move freely and use electric energy for long-term cardiac support." To date, more than $40 billion has been invested to support the development of ventricular assist devices. The 2006 European Heart Failure Guidelines have used ventricular assist devices as one of the methods of heart failure treatment. After years of research, there are currently several products in the world for clinical use, mainly for the transition of heart transplantation, recovery of cardiac function and even permanent replacement therapy. However, imported products are expensive, and the localization of ventricular assist devices is extremely urgent.

At present, 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.

At the same time, 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. On the other hand, 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.

Summary of the invention

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.

In order to solve the above technical problem, 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);

In the cross section of the blood pump, 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) ;

There is no bearing connection between the stator and the rotor.

Compared with the prior art, the main differences and effects of the embodiments of the present invention are as follows:

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.

Further, 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.

Further, the 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.

Further, 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.

Further, 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.

Further, 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.

Further, the outlet right-handed stator (7) is fixed to the motor bracket (4) to adjust the direction of blood flow outflow.

Further, 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.

Further, 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. Compared with the blood pump structure (removing bearing) involved in CN 201208423Y, 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, and the effective value of vibration displacement is reduced by 13~33μm. 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.

Further, in the magnetic steel (5) containing a magnetic material, other materials may be contained as long as the permanent magnets are contained therein. 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.

Further, 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.

DRAWINGS

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;

2 is a schematic structural view of a slurry shaft integrated tandem blade according to a first embodiment of the present invention;

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;

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;

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;

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;

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).

detailed description

In the following description, numerous technical details are set forth in order to provide the reader with a better understanding of the present application. However, those skilled in the art can understand that the technical solutions claimed in the claims of the present application can be implemented without these technical details and various changes and modifications based on the following embodiments.

The embodiments of the present invention will be further described in detail below with reference to the accompanying drawings.

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);

In the cross section of the blood pump, 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) .

There is no bearing connection between the stator and the rotor.

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 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).

Further, preferably, 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). Preferably, 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).

1 is a schematic structural view (cross-sectional view) of a preferred implantable self-suspended axial blood pump.

Specifically, as shown in FIG. 1, 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).

Further, specifically, the magnetic steel (5) containing a magnetic material may further contain other materials as long as the permanent magnets are contained therein.

In the present embodiment, preferably, the stator and the rotor are not directly or indirectly connected by bearings. Among them, 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.

Specifically, 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.

Similarly, 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).

Further, preferably, 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). Compared with the blood pump structure (removing the bearing) involved in CN 201208423Y, the effective value of the vibration acceleration is reduced by 1~2m/s ² , the effective value of the vibration speed is reduced by 3~5mm/s, and the effective value of the vibration displacement is reduced by 13~33μm. Stability is greatly improved.

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.

Moreover, it will be appreciated that in other certain embodiments of the invention, the 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.

Moreover, it will be appreciated that in other embodiments of the invention, the 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.

In addition, 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).

Preferably, 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.

Further, 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.

In addition, 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). And the built-in paddle (8) constitutes a pulp shaft-integrated tandem blade (6). Preferably, the outer paddle (9) and the built-in paddle (8) are integrally connected in series to the paddle shaft (10). In addition, the two can also be directly connected without using a paddle shaft, as shown in FIG.

In the present embodiment, preferably, 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.

In view of the narrow flow path in the blood pump, 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. In this embodiment, 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.

Of course, this is only a preferred embodiment of the present invention. In some other embodiments of the present invention, 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. When the blood flows through the airfoil-shaped cut surface, 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.

In addition, it will be appreciated that in other certain embodiments of the invention, 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. Alternatively, other forms may be used, for example, in the form of a flat leaf cut of a general pump.

In the present embodiment, 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.

There are no other obstructions in the main channel, so the flow path is smooth, allowing large amounts of blood to pass smoothly.

There are no obstructions in the branch channels (13) and (14) that impede the flow of blood, and because the gap between the branch channels is small, the air gap between the stator coil (3) and the magnetic steel (5) is also small, thereby significantly reducing The volume and weight of the blood pump.

With 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.

Considering that the implantable self-suspended shaft blood pump is used for the implantable ventricular assist device, there is a high requirement for the structural sealing. If a conventional brushless DC motor position sensor is used, the sensor stator Hall element is used. Excessive out-of-line (at least 5), leading to lead seal and lead material and human body rejection, 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.

4 is a schematic radial cross-sectional view of the stator and rotor structure.

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.

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. For example, 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.

Taking one of them as an example, it has been successfully rotated for four months and is still operating normally. 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.). At the same time, 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 following table shows the experimental test data sheets of the prototype from November 17, 2011.

date	Speed RPM	Pressure MMHG	Current A	Flow rate L/MIN
					2011.12.07	7610	99.10	0.55	4.85
2011.12.12	7599	98.70	0.55	4.90
					2011.12.17	7623	99.80	0.55	4.81
2011.12.22	7630	99.81	0.55	4.50
					2012.01.09	7684	99.15	0.55	4.80
2012.01.14	7600	98.70	0.55	4.80
					2012.01.19	7557	94.29	0.51	4.40
2012.01.24	7704	97.62	0.55	4.85
					2012.01.29	7550	94.02	0.51	4.40
2012.02.05	7488	94.01	0.51	4.80
					2012.02.10	7408	93.80	0.51	4.80
2012.02.15	7501	95.00	0.52	4.81

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.

Moreover, the inventors tested the implantable self-suspended axial blood pump prototype under different pressures and obtained the following data:

It can be seen from the above test data that the power consumption of the blood pump varies from 14 to 20w under normal working conditions, and the corresponding pump temperature is kept below 38 degrees Celsius.

It has been observed experimentally that 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). When 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.

In the fatigue test, the axial flow self-suspending pump of the present invention can continuously rotate for one year and four months or more.

Although the invention has been illustrated and described with reference to the preferred embodiments of the present invention, it will be understood The spirit and scope of the invention.

Claims (15)

1. An implantable self-suspended axial blood flow pump, comprising: a stator and a rotor, wherein the stator comprises: a stator core (2), a stator coil (3) and a motor bracket (4); the rotor comprises: a magnetic material Magnetic steel (5) and built-in paddles (8);

   In the cross section of the blood pump, 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) ;

   There is no bearing connection between the stator and the rotor.
2. The implantable self-suspended axial blood pump according to claim 1, wherein the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.003D to 0.019D, and D is a magnetic steel. (5) The inner diameter of the cross section.
3. The implantable self-suspended axial blood pump according to claim 1, wherein the gap between the motor bracket (4) and the magnetic steel (5) ranges from 0.0042D to 0.0048D, and D is a magnetic steel. (5) The inner diameter of the cross section.
4. The implantable self-suspended axial blood pump according to claim 1, characterized in that the thickness of the magnetic steel (5) ranges from 1.5 mm to 3.5 mm.
5. The implantable self-suspended axial blood pump according to claim 1, wherein the thickness of the magnetic steel (5) ranges from 2.0 mm to 3.0 mm.
6. The implantable self-suspended axial blood pump according to claim 1, wherein the thickness of the magnetic steel (5) ranges from 2.3 mm to 2.8 mm.
7. The implantable self-suspended axial blood pump according to claim 1, further comprising: 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). .
8. The implantable self-suspended axial blood pump according to claim 1, characterized in that the leaf-cut surface of the inner blade (8) and the outer blade (9) adopts a wing-shaped blade section of a marine conduit propeller. form.
9. The implantable self-suspended axial blood pump according to claim 1, further comprising: an outlet right-handed stator (7), the outlet right-handed stator (7) being placed on the implantable self-suspended shaft for bleeding The blood outlet end of the pump is fixed to the motor bracket (4).
10. The implantable self-suspended axial blood pump according to any one of claims 1 to 8, characterized in that the mainstream of the blood flow is formed between the outer paddle (9) and the inner wall of the motor bracket (4). (11) a main flow path (12) between the built-in paddle (8) and the inner wall of the magnetic steel (5) to form a blood flow; the outer wall of the magnetic steel (5) and the inner wall of the motor support (4) constitute a blood flow Branch runners (13) and (14).
11. The implantable self-suspended axial blood pump according to claim 9, wherein a position sensor that determines a relative position between the stator and the rotor is not included in the blood pump.
12. The implantable self-suspended axial blood pump according to claim 10, characterized in that the stator coil (3) is a hollow cup winding.
13. The implantable self-suspended axial blood pump according to claim 11, wherein the magnetic steel (5) is made of a neodymium-iron-boron permanent magnet material, radially magnetized and a pair of poles. Cylindrical magnetic ring.
14. The implantable self-suspended axial blood flow pump according to claim 12, wherein the stator adopts a two-phase conduction, three-phase six-state conduction mode.
15. The implantable self-suspended axial blood pump according to claim 13, wherein a motor housing (1) is fixed to an exterior of the stator.

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