Method for driving blood pump and electronic device

Abstract

The invention provides a blood pump driving method and electronic equipment, a blood pump comprises a rotor assembly, a stator assembly and a shell, the rotor assembly and the stator assembly are arranged in the shell at intervals along the rotation axis of the rotor assembly, and the rotor assembly can rotate around the axis of the rotor assembly under the action of a magnetic field generated by the stator assembly. The driving method comprises the steps that the stator assembly is controlled to drive the rotor assembly to rotate around the axis of the rotor assembly; and the stator assembly is controlled to apply an adjusting force in the rotation axis direction of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly, so that the position of the rotor assembly in the shell is adjusted, and a first preset distance is kept between the rotor assembly and the stator assembly in the rotation process. The stator assembly is controlled to apply the axial adjusting force to the rotor assembly, so that the rotor assembly is kept at the working position, the stability of the axial position of the rotor assembly is guaranteed, and then the service life of the blood pump and the safety of medical operation are guaranteed.

Description

Technical Field

[0001] The present invention relates to the field of medical supplies, and in particular to a driving method of a blood pump and an electronic device. Background Art

[0002] A blood pump is a commonly used medical device that provides the power to keep blood flowing. For example, the heart is the body's power organ, its primary function being to power blood flow and transport it to all parts of the body. When a patient's heart fails and cannot provide sufficient power, a blood pump is placed in the heart to replace the heart and provide the power to keep blood flowing, eliminating the risk to the patient's life.

[0003] A blood pump typically includes a flow channel defined by a housing, a rotor disposed in the flow channel, and a stator that provides power to the rotor. The stator drives the rotor to rotate in the flow channel, thereby driving blood to flow along the flow channel through blades on the rotor, thereby ensuring the normal flow of blood in the patient's blood vessels.

[0004] However, existing blood pumps often experience unstable rotor position during medical procedures. The rotor easily contacts and rubs against the internal structure of the housing, causing significant vibration during operation. This affects the pump's lifespan and reduces the safety of medical procedures. Therefore, precisely positioning the rotor has become a pressing technical challenge in this field. Summary of the Invention

[0005] The present invention aims to solve one of the technical problems in the related art to a certain extent. To this end, the present invention provides a blood pump and an electronic device, wherein the rotor assembly in the blood pump has good position stability, which can ensure the service life of the blood pump and the safety of medical operations.

[0006] To achieve the above objectives, as one aspect of the present invention, a method for driving a blood pump is provided, wherein the blood pump comprises a rotor assembly, a stator assembly, and a housing, wherein the rotor assembly and the stator assembly are spaced apart in the housing along the rotation axis of the rotor assembly, and the rotor assembly is capable of rotating about its own axis under the action of the magnetic field generated by the stator assembly to drive fluid into and out of the housing, and the blood pump further comprises a first magnetic bearing assembly, wherein the first magnetic bearing assembly comprises a first inner magnetic bearing and a first outer magnetic bearing that interact with each other, the first outer magnetic bearing being disposed on the inner wall of the housing, and the first inner magnetic bearing being disposed on the rotor assembly. The method for driving the blood pump comprises:

[0007] Controlling the stator assembly to drive the rotor assembly to rotate around its own axis;

[0008] The stator assembly is controlled to apply an adjustment force to the rotor assembly along the rotation axis of the rotor assembly through the electromagnetic field between the stator assembly and the rotor assembly, so as to adjust the position of the rotor assembly in the housing so that the rotor assembly maintains a first preset distance from the stator assembly during rotation.

[0009] Optionally, the blood pump further comprises a second magnetic bearing assembly, the second magnetic bearing assembly comprising a second inner magnetic bearing and a second outer magnetic bearing interacting with each other, the second outer magnetic bearing being disposed on an inner wall of the housing, and the second inner magnetic bearing being disposed on the rotor assembly;

[0010] When the stator assembly is not powered on, the distance between the first internal magnetic bearing and the stator assembly is different from the distance between the first external magnetic bearing and the stator assembly, and the distance between the second internal magnetic bearing and the stator assembly is different from the distance between the second external magnetic bearing and the stator assembly.

[0011] Optionally, controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes:

[0012] The stator assembly is controlled to apply an adjusting force to the rotor assembly along the direction of the rotation axis of the rotor assembly through the electromagnetic field between the stator assembly and the rotor assembly, so that the distance between the first inner magnetic bearing and the stator assembly is smaller than the distance between the first outer magnetic bearing and the stator assembly, and the second magnetic bearing assembly can only generate a radial force.

[0013] Optionally, controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes:

[0014] controlling the stator assembly to provide an adjustment repulsive force to the rotor assembly along the direction of the rotation axis of the rotor assembly, so that the rotor assembly moves away from the stator assembly along the direction of the rotation axis of the rotor assembly to be spaced apart from the stator assembly by the first preset distance;

[0015] The stator assembly is controlled to provide an adjusting balancing force along the rotation axis of the rotor assembly to the rotor assembly through a magnetic field, so that the rotor assembly maintains the first preset distance from the stator assembly.

[0016] Optionally, when the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the second internal magnetic bearing and the stator assembly is smaller than the distance between the second external magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the stator assembly remains relatively stable.

[0017] Optionally, when the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the first internal magnetic bearing and the stator assembly is smaller than the distance between the first external magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the stator assembly remains relatively stable.

[0018] Optionally, the blood pump further comprises a limiting bracket, wherein the limiting bracket is disposed in the housing and is located on a side of the rotor assembly away from the stator assembly along the direction of the rotation axis of the rotor assembly;

[0019] The controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes:

[0020] controlling the stator assembly to provide an adjusted attraction force to the rotor assembly along the rotation axis of the rotor assembly, so that the rotor assembly moves closer to the stator assembly along the rotation axis of the rotor assembly to a distance from the stator assembly by the first preset distance;

[0021] The stator assembly is controlled to provide an adjusting balancing force along the rotation axis of the rotor assembly to the rotor assembly through a magnetic field, so that the rotor assembly maintains the first preset distance from the stator assembly.

[0022] Optionally, the blood pump further comprises a limiting bracket, wherein the limiting bracket is disposed in the housing and is located on a side of the rotor assembly away from the stator assembly along the direction of the rotation axis of the rotor assembly;

[0023] When the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the second inner magnetic bearing and the stator assembly is greater than the distance between the second outer magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the limit bracket remains relatively stable.

[0024] Optionally, when the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the first internal magnetic bearing and the stator assembly is greater than the distance between the first external magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the limit bracket remains relatively stable.

[0025] Optionally, the rotor assembly further includes a displacement sensor module and an induction coil, the displacement sensor module being disposed on the rotor assembly, and the induction coil being disposed on the inner wall of the housing; the displacement sensor module being located on a side of the first internal magnetic bearing away from the stator assembly, and in a radial projection direction, an axial position of the induction coil partially overlaps with a radial projection surface of the displacement sensor module, and the blood pump driving method further includes:

[0026] Based on the feedback signal of the induction coil, the stator assembly is controlled to provide the magnitude and direction of the regulating force to the rotor assembly.

[0027] As a second aspect of the present invention, there is provided an electronic device, comprising:

[0028] one or more processors;

[0029] A memory having one or more computer programs stored thereon, which, when executed by the one or more processors, enables the one or more processors to implement the aforementioned blood pump driving method.

[0030] In the present invention, the rotor assembly and stator assembly of the blood pump are coaxially spaced apart and arranged in the housing. The stator assembly can generate a rotating magnetic field to drive the rotor assembly to rotate and drive the fluid to flow through the blades. In addition, the driving method of the blood pump provided by the embodiment of the present invention controls the stator assembly to apply an axial adjustment force to the rotor assembly, so that the rotor assembly is located in a magnetic suspension position maintaining a first preset distance from the stator assembly, thereby ensuring the stability of the axial position of the rotor assembly, and can effectively prevent the rotor assembly from contacting with the internal structure of the housing and causing friction and collision, thereby ensuring the service life of the blood pump and the safety of medical operations. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] The present invention will be further described below in conjunction with the accompanying drawings:

[0032] Figure 1 is a schematic cross-sectional structural diagram of a blood pump provided by an embodiment of the present invention;

[0033] Figure 2 yes Figure 1 Schematic diagram of the internal fluid flow path of the blood pump;

[0034] Figure 3 yes Figure 1 A partial enlarged schematic diagram of the blood pump in area A;

[0035] Figure 4 yes Figure 2 A partial enlarged schematic diagram of the blood pump in area B;

[0036] Figure 51 is a schematic diagram of force analysis of a rotor assembly at a defined rear end position in a blood pump provided by an embodiment of the present invention;

[0037] Figure 6 1 is a schematic diagram of force analysis of a rotor assembly in a working position in a blood pump provided by an embodiment of the present invention;

[0038] Figure 7 is a schematic diagram of an exploded structure of a blood pump provided by an embodiment of the present invention;

[0039] Figure 8 is a schematic cross-sectional structural diagram of a blood pump provided by an embodiment of the present invention;

[0040] Figure 9 yes Figure 8 Schematic diagram of the internal fluid flow path of the blood pump;

[0041] Figure 10 is a schematic diagram of force analysis of a rotor assembly in an idle position in a blood pump provided by an embodiment of the present invention;

[0042] Figure 11 1 is a schematic diagram of force analysis of a rotor assembly in a working position in a blood pump provided by an embodiment of the present invention;

[0043] Figure 12 is a schematic structural diagram of a rotor assembly in a blood pump provided by an embodiment of the present invention;

[0044] Figure 13 is a schematic diagram of an exploded structure of a blood pump provided by an embodiment of the present invention;

[0045] Figure 14 is a flow chart of a method for driving a blood pump provided by an embodiment of the present invention;

[0046] Figure 15 is a schematic flow chart of a method for driving a blood pump provided by an embodiment of the present invention;

[0047] Figure 16 is a flow chart of a method for driving a blood pump provided by an embodiment of the present invention;

[0048] Figure 17 It is a structural diagram of an electronic device provided by an embodiment of the present invention.

[0049] Description of Reference Numerals

[0050] 100: Rotor assembly 110: Impeller

[0051] 111: Fixed cylinder 112: Blade

[0052] 120: Second internal magnetic bearing 130: First internal magnetic bearing

[0053] 201: Power magnetic ring 150: Center axis

[0054] 160: rotor housing 168: boss portion

[0055] 170: Displacement sensor module 180: Impeller hub

[0056] 182: Receiving piece 183: Contact piece

[0057] 200: stator assembly 210: housing panel

[0058] 220: Winding 230: Circuit board

[0059] 240: Insulation ring 300: Shell

[0060] 301: guide shell 302: fluid inlet

[0061] 310: First housing 311: First guide tube

[0062] 312: First connecting strip 313: First fluid outlet

[0063] 314: Annular transition platform 320: Second housing

[0064] 321: Second guide tube 322: Second connecting strip

[0065] 323: Second fluid outlet 324: Annular guide platform

[0066] 325: Lead hole 326: First wire groove

[0067] 330: stator housing 331: second annular protrusion

[0068] 332: Second wire groove 340: Shrink housing

[0069] 350: Second external magnetic bearing 351: Second bearing sleeve

[0070] 360: First external magnetic bearing 361: First bearing sleeve

[0071] 370: Induction coil 380: Coil fixing ring

[0072] 381: Lead-out groove 390, limit bracket

[0073] 391: Contact portion 392: Connecting portion

[0074] 393: Fixed ring 394: Limiting groove

[0075] 400: Catheter DETAILED DESCRIPTION

[0076] The following describes embodiments of the present invention in detail, examples of which are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described in the embodiments are intended to explain the present invention and are not to be construed as limiting the present invention.

[0077] References in this specification to "one embodiment," "an example," or "an example" mean that a particular feature, structure, or characteristic described in connection with the embodiment itself can be included in at least one embodiment disclosed herein. The appearances of the phrase "in one embodiment" in various places in the specification are not necessarily all referring to the same embodiment.

[0078] A blood pump typically includes a flow channel defined by a housing, a rotor disposed in the flow channel, and a stator that provides power to the rotor. The stator drives the rotor to rotate in the flow channel, thereby driving blood to flow along the flow channel through blades on the rotor, thereby ensuring the normal flow of blood in the patient's blood vessels.

[0079] In related technologies, in order to minimize the resistance to rotor rotation and reduce the heat generation of the blood pump, the method of connecting the shaft structure in the rotor with the mechanical bearing in the housing is often abandoned, and instead a magnetic levitation connection method is used to suspend the rotor in the housing. However, although this solution can effectively reduce the resistance to rotor rotation and improve the heat generation situation, the position of the rotor along the axial direction lacks positioning. During storage and transportation, the rotor is very likely to shake along the axial direction, which in turn causes the rotor to easily contact the internal structure of the housing and cause friction and collision, affecting the service life of the blood pump and the safety of medical operations.

[0080] In order to solve the above technical problems, as one aspect of the present invention, a method for driving a blood pump is provided, such as Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the blood pump includes a rotor assembly 100, a stator assembly 200 and a housing 300. The rotor assembly 100 and the stator assembly 200 are spaced apart in the housing 300 along the rotation axis of the rotor assembly 100, and the rotor assembly 100 can rotate around its own axis under the action of the magnetic field generated by the stator assembly 200 to drive the fluid to flow into and out of the housing 300. The blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing 130 and a first outer magnetic bearing 360 that interact with each other. The first outer magnetic bearing 360 is arranged on the inner wall of the housing 300, and the first inner magnetic bearing 130 is arranged on the rotor assembly 100. Figure 14 As shown, the driving method of the blood pump includes:

[0081] Step S10: Control the stator assembly 200 to drive the rotor assembly 100 to rotate around its own axis;

[0082] Step S20: Control the stator assembly 200 to apply an adjustment force along the rotation axis of the rotor assembly 100 to the rotor assembly 100 through the electromagnetic field between the stator assembly 200 and the rotor assembly 100, so as to adjust the position of the rotor assembly 100 in the housing 300, so that the rotor assembly 100 maintains a first preset distance h1 (i.e., Figure 2 、 Figure 6 、 Figure 9 、 Figure 11 The position of the rotor assembly 100).

[0083] In the present invention, the rotor assembly 100 and the stator assembly 200 of the blood pump are coaxially spaced apart and arranged in the housing 300. The stator assembly 200 can generate a rotating magnetic field to drive the rotor assembly 100 to rotate and drive the fluid to flow through the blades 112. In addition, the driving method of the blood pump provided in the embodiment of the present invention controls the stator assembly 200 to apply an axial adjustment force to the rotor assembly 100, so that the rotor assembly 100 is located in a magnetic suspension position maintaining a first preset distance h1 from the stator assembly 200, thereby ensuring the stability of the axial position of the rotor assembly 100, and can effectively prevent the rotor assembly 100 from contacting and rubbing or colliding with the internal structure of the housing (such as the first bearing sleeve 361 and the annular transition platform 314), thereby ensuring the service life of the blood pump and the safety of medical operations.

[0084] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the blood pump also includes a second magnetic bearing assembly, which includes a second inner magnetic bearing 120 and a second outer magnetic bearing 350 that interact with each other. The second outer magnetic bearing 350 is arranged on the inner wall of the shell 300, and the second inner magnetic bearing 120 is arranged on the rotor assembly 100.

[0085] As an optional embodiment of the present invention, when the stator assembly 200 is not powered on, the distance between the first inner magnetic bearing 130 and the stator assembly 200 is different from the distance between the first outer magnetic bearing 360 and the stator assembly 200, and the distance between the second inner magnetic bearing 120 and the stator assembly 200 is different from the distance between the second outer magnetic bearing 350 and the stator assembly 200.

[0086] That is, in the embodiment of the present invention, when the stator assembly 200 is not powered, the inner and outer magnetic rings of the first magnetic bearing assembly and the second magnetic bearing assembly are both axially offset, so that both can provide an axial force to the rotor assembly 100, so that the rotor assembly 100 is axially close to one end of the housing 300 and is parked in a stable position on that side under the limiting effect of the end structure of the housing 300 (for example, Figure 1 、 Figure 5 As shown, it is docked at the rear end of the housing 300, or as shown Figure 8 、 Figure 10 As shown, the rotor assembly 100 is docked at the front end of the housing 300, thereby maintaining the relative position between the rotor assembly 100 and the housing 300 when the stator assembly is not powered, ensuring the position stability of the rotor assembly 100 inside the housing 300 during storage and transportation of the blood pump, avoiding collision and friction between the rotor assembly 100 and the structures on the inner wall of the housing 300 (such as the first bearing sleeve 361 and the annular transition platform 314), and thus ensuring the service life of the blood pump.

[0087] Furthermore, since the rotor assembly 100 is precisely positioned to a position where it contacts a certain end of the housing 300 when the stator assembly is not energized, when the blood pump needs to be used, it is possible to directly determine that the rotor assembly 100 is in the idle position, and based on the premise that the rotor assembly 100 is in the idle position, the rotor assembly 100 is adjusted in the axial position accordingly, thereby improving the efficiency of determining and adjusting the axial position of the rotor assembly 100 and thereby ensuring the efficiency of medical operations.

[0088] As an optional embodiment of the present invention, in step S20, controlling the stator assembly 200 to apply an adjustment force along the rotation axis of the rotor assembly 100 to the rotor assembly 100 through the electromagnetic field between the stator assembly 200 and the rotor assembly 100 specifically includes:

[0089] The stator assembly 200 is controlled to apply an adjustment force to the rotor assembly 100 along the direction of the rotation axis of the rotor assembly 100 through the electromagnetic field between the stator assembly 200 and the rotor assembly 100, so that the distance between the first inner magnetic bearing 130 and the stator assembly 200 is smaller than the distance between the first outer magnetic bearing 360 and the stator assembly 200, and the second magnetic bearing assembly can only generate a radial force.

[0090] That is, Figure 2 、 Figure 6 、 Figure 9 、 Figure 11 As shown, when the rotor assembly 100 is fully suspended (spaced a first preset distance h1 from the stator assembly 200), the axial position of the second inner magnetic bearing 120 corresponds to the second outer magnetic bearing 350, and the center of the first inner magnetic bearing 130 is located on the side of the center of the first outer magnetic bearing 360 toward the stator assembly 200.

[0091] That is, in the embodiment of the present invention, when the rotor assembly 100 is in the magnetic suspension position, the position of the second inner magnetic bearing 120 corresponds to the second outer magnetic bearing 350, and no relative force in the axial direction is generated between the two. Figure 6 、 Figure 11 As shown, only the first outer magnetic bearing 360 applies a force F2 ′ to the second inner magnetic bearing 120 directed toward the stator assembly 200 .

[0092] In other embodiments of the present invention, when the rotor assembly 100 is in the magnetic suspension position, the axial position of the first inner magnetic bearing 130 corresponds to the first outer magnetic bearing 360, and the center of the second inner magnetic bearing 120 is located on the side of the center of the second outer magnetic bearing 350 toward the stator assembly 200, that is, only the second outer magnetic bearing 350 applies a force directed toward the stator assembly 200 to the second inner magnetic bearing 120.

[0093] Alternatively, when the rotor assembly 100 is in the magnetic suspension position, the center of the second inner magnetic bearing 120 is located on the side of the center of the second outer magnetic bearing 350 facing the stator assembly 200, and the center of the first inner magnetic bearing 130 is located on the side of the center of the first outer magnetic bearing 360 facing the stator assembly 200.

[0094] As an optional embodiment of the present invention, step S10 specifically includes:

[0095] The stator assembly 200 is controlled to drive the rotor assembly 100 to rotate around its own axis, and the rotation speed of the rotor assembly 100 is maintained at a preset rated speed.

[0096] In order to further ensure the position stability of the rotor assembly 100 in the housing 300, as a preferred embodiment of the present invention, as shown in FIG. Figure 15 As shown, step S20 specifically includes:

[0097] Step S21: Control the stator assembly 200 to provide an adjustment repulsive force Fz to the rotor assembly 100 along the rotation axis of the rotor assembly 100, so that the rotor assembly 100 moves away from the stator assembly 200 along the rotation axis of the rotor assembly 100 to a first preset distance from the stator assembly 200;

[0098] Step S22 : controlling the stator assembly 200 to provide an adjusting balancing force Fz′ along the rotation axis of the rotor assembly 100 to the rotor assembly 100 through a magnetic field, so that the rotor assembly 100 maintains a first preset distance from the stator assembly 200 .

[0099] like Figure 1 、 Figure 3 、 Figure 5 As shown, when the stator assembly 200 is not powered, the rotor assembly 100 is in contact with the stator assembly 200, and the multiple internal magnetic bearings are respectively located on the side of the corresponding external magnetic bearing facing the stator assembly 200; Figure 2 、 Figure 4 、 Figure 6As shown, when the rotor assembly 100 is in the magnetic suspension position, the rotor assembly 100 is axially spaced from the stator assembly 200, and at least one internal magnetic bearing is located on the side of the corresponding external magnetic bearing facing the stator assembly 200 (the figure shows the case where the first internal magnetic bearing 130 is located on the side of the first external magnetic bearing 360 facing the stator assembly 200).

[0100] In an embodiment of the present invention, the rotor assembly 100 can contact and be adsorbed on the stator assembly 200 before starting the medical operation, thereby ensuring the position stability of the rotor assembly 100 inside the housing 300 during storage and transportation of the blood pump, avoiding collision and friction between the rotor assembly 100 and the structure on the inner wall of the housing 300, and further ensuring the service life of the blood pump.

[0101] As an optional embodiment of the present invention, Figure 5 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the second inner magnetic bearing 120 and the stator assembly 200 is smaller than the distance between the second outer magnetic bearing 350 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the stator assembly 200 remains relatively stable.

[0102] As an optional embodiment of the present invention, Figure 5 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the first inner magnetic bearing 130 and the stator assembly 200 is smaller than the distance between the first outer magnetic bearing 360 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the stator assembly 200 remains relatively stable.

[0103] Specifically, if Figure 5The figure shows a force analysis diagram when the rotor assembly 100 is located at the rear end limited position. When the rotor assembly 100 is located at the rear end limited position, the multiple sets of magnetic levitation bearings are all in a state where the internal magnetic bearings are located on the side of the bearing facing the stator assembly 200. The distance a1 by which the second internal magnetic bearing 120 exceeds the second external magnetic bearing 350 on the side of the stator assembly 200 is exceeded. The second external magnetic bearing 350 applies a repulsive force F1 axially directed toward the side of the stator assembly 200 to the rotor assembly 100. The distance a2 by which the first internal magnetic bearing 130 exceeds the first external magnetic bearing 360 on the side of the stator assembly 200 is exceeded. The first external magnetic bearing 360 applies a repulsive force F2 axially directed toward the side of the stator assembly 200 to the rotor assembly 100. The permanent magnetic structure on the rotor assembly 100 and the stator assembly 200 are attracted to each other, so that the rotor assembly 100 is subjected to an attractive force F3, and the blood flow applies a reaction force F4 to the rotor assembly 100. At this time, if the rotor assembly 100 needs to enter the moving position, the stator assembly 200 needs to be controlled to provide the rotor assembly 100 with an axial adjustment repulsive force Fz, so that the rotor assembly 100 overcomes the repulsive force F1, the repulsive force F2 and the attractive force F3 and moves away from the stator assembly 200.

[0104] like Figure 6 、 Figure 11 The figure shows a force analysis diagram of the rotor assembly 100 when it is in the magnetic levitation position. When the rotor assembly 100 is in the magnetic levitation position, the second inner magnetic bearing 120 corresponds to the second outer magnetic bearing 350 in position. The first inner magnetic bearing 130 extends beyond the first outer magnetic bearing 360 toward the stator assembly 200 by a distance a2'. The first outer magnetic bearing 360 applies a repulsive force F2' axially directed toward the stator assembly 200 to the rotor assembly 100. A magnetic levitation gap with a width of a first preset distance h1 is defined between the rotor assembly 100 and the stator assembly 200. The permanent magnet structure on the rotor assembly 100 and the stator assembly 200 are attracted to each other, causing the rotor assembly 100 to be subjected to an attractive force F3'. The blood flow applies a reaction force F4 to the rotor assembly 100. The stator assembly 200 provides an axial adjustment balancing force Fz' to the rotor assembly 100, so that the magnetic levitation gap between the rotor assembly 100 and the stator assembly 200 is maintained at the first preset distance h1.

[0105] As an optional embodiment of the present invention, the repulsive force Fz is adjusted to decrease as the distance (magnetic levitation gap) between the rotor assembly 100 and the stator assembly 200 increases, that is, the repulsive force Fz is adjusted mainly to offset the attractive force F3 exerted on the rotor assembly 100 due to the mutual adsorption between the permanent magnetic structure on the rotor assembly 100 and the stator assembly 200. The magnitude of the attractive force F3 decreases rapidly as the rotor assembly 100 and the stator assembly 200 move away from each other. Therefore, the repulsive force Fz can be adjusted to be correspondingly reduced to ensure the stability of the axial resultant force exerted on the rotor assembly 100, and thereby ensure the stability of the position switching process of the rotor assembly 100.

[0106] As an optional embodiment of the present invention, Figure 8 As shown, the blood pump further includes a limiting bracket 390, which is disposed in the housing 300 and is located on a side of the rotor assembly 100 away from the stator assembly 200 along the direction of the rotation axis of the rotor assembly 100. Figure 16 As shown, step S20 includes:

[0107] Step S201: Control the stator assembly 200 to provide an adjusted attraction force to the rotor assembly 100 along the rotation axis of the rotor assembly 100, so that the rotor assembly 100 moves closer to the stator assembly 200 along the rotation axis of the rotor assembly 100 to a first preset distance from the stator assembly 200;

[0108] Step S202 : Control the stator assembly 200 to provide an adjusting balancing force along the rotation axis of the rotor assembly 100 to the rotor assembly 100 through a magnetic field, so that the rotor assembly 100 maintains a first preset distance from the stator assembly 200 .

[0109] In the embodiment of the present invention, a limiting bracket 390 is provided at the fluid inlet 302 of the housing 300, and when the rotor assembly 100 is away from the stator assembly 200 and reaches an idle position and is in contact with the limiting bracket 390, the second inner magnetic bearing 120 is located on the side of the second outer magnetic bearing 350 away from the stator assembly 200, and the first inner magnetic bearing 130 is located on the side of the first outer magnetic bearing 360 away from the stator assembly 200, so that the repulsive force exerted by the first outer magnetic bearing 360 on the first inner magnetic bearing 130 and the repulsive force exerted by the second outer magnetic bearing 360 on the first inner magnetic bearing 130 are The repulsive force applied by the bearing 350 to the second internal magnetic bearing 120 has a component force directed along the axial direction toward the limit bracket 390, so that the rotor assembly 100 remains in contact with the limit bracket 390 when the stator assembly is not powered, ensuring the position stability of the rotor assembly 100 inside the shell 300 during storage and transportation of the blood pump, avoiding collision and friction between the rotor assembly 100 and the structures on the inner wall of the shell 300 (such as the first bearing sleeve 361 and the annular transition platform 314), and further ensuring the service life of the blood pump.

[0110] As an optional embodiment of the present invention, Figure 8 、 Figure 10 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the second inner magnetic bearing 120 and the stator assembly 200 is greater than the distance between the second outer magnetic bearing 350 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the limiting bracket remains relatively stable.

[0111] As an optional embodiment of the present invention, Figure 8 、 Figure 10As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the first inner magnetic bearing 130 and the stator assembly 200 is greater than the distance between the first outer magnetic bearing 360 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the limiting bracket remains relatively stable.

[0112] like Figure 8 、 Figure 10 As shown, when the stator assembly is not powered on, the rotor assembly 100 is in contact with the limit bracket 390. At this time, the two sets of magnetic suspension bearings are in a state where the inner magnetic bearings are located on the side of the bearing facing the limit bracket 390. The second inner magnetic bearing 120 exceeds the second outer magnetic bearing 350 by a distance a10 toward the side of the limit bracket 390. The second outer magnetic bearing 350 applies a repulsive force F10 axially pointing to the side of the limit bracket 390 to the rotor assembly 100. The first inner magnetic bearing 130 exceeds the first outer magnetic bearing 360 by a distance a20 toward the side of the limit bracket 390. The first outer magnetic axis The bearing 360 applies a repulsive force F20 to the rotor assembly 100 in the axial direction pointing to the side of the limit bracket 390. The distance between the rotor assembly 100 and the stator assembly 200 is h0. The permanent magnetic structure on the rotor assembly 100 and the stator assembly 200 are attracted to each other, so that the rotor assembly 100 is subjected to an attractive force F30. At this time, if the rotor assembly 100 needs to enter the moving position, it is necessary to first control the stator assembly 200 to provide an axial adjustment attractive force Fz0 to the rotor assembly 100, so that the rotor assembly 100 overcomes the repulsive force F10 and the repulsive force F20 and moves to the stator assembly 200. Figure 11 Magnetic levitation position shown.

[0113] As an optional embodiment of the present invention, Figure 1 、 Figure 8 As shown, the blood pump further includes a displacement sensor module 170 and an induction coil 360. The displacement sensor module is disposed on the rotor assembly 100, and the induction coil is disposed on the inner wall of the housing 300. In the radial projection direction, the axial position of the induction coil partially overlaps with the radial projection surface of the displacement sensor module. The driving method of the blood pump further includes:

[0114] Based on the feedback signal of the induction coil 360 , the magnitude and direction of the adjustment force provided by the stator assembly 200 to the rotor assembly 100 are determined.

[0115] The embodiment of the present invention determines the magnitude and direction of the regulating force in real time based on the feedback signal of the induction coil 360. Therefore, when the rotor assembly 100 deviates from the magnetic levitation position due to instability of the reaction force F4 of the blood flow, the magnitude and direction of the regulating force are changed in time to return the position of the rotor assembly 100 to the correct position, thereby further ensuring the stability of the blood pump operation.

[0116] As an optional embodiment of the present invention, when the rotor assembly 100 is in the magnetic suspension position, the induction coil 360 extends beyond the displacement sensor module 170 toward the side of the stator assembly 200;

[0117] The feedback signal includes the inductance of the induction coil 360 . The steps of determining the magnitude and direction of the balancing force Fz′ provided by the stator assembly 200 to the rotor assembly 100 based on the feedback signal of the induction coil 360 specifically include:

[0118] The inductance of the induction coil 360 is determined. When the inductance increases, the value of the balancing force Fz' directed toward the rotor assembly 100 is reduced. When the inductance decreases, the value of the balancing force Fz' directed toward the rotor assembly 100 is increased.

[0119] That is, when the adjustment balancing force Fz' is directed from the stator assembly 200 to the rotor assembly 100, when the inductance value increases, it means that the axial length of the displacement sensor module 170 entering the interior of the induction coil 360 increases, that is, the rotor assembly 100 is close to the stator assembly 200, and the adjustment balancing force Fz' should be increased at this time; and when the inductance value decreases, it means that the axial length of the displacement sensor module 170 entering the interior of the induction coil 360 decreases, that is, the rotor assembly 100 is away from the stator assembly 200, and the adjustment balancing force Fz' should be reduced or reversed to maintain the position of the rotor assembly 100.

[0120] As an optional implementation of the present invention, the feedback signal may further include a voltage value across the induction coil 360 .

[0121] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the rotor assembly 100 also includes a power magnetic ring 201, and the stator assembly 200 includes a casing panel 210 and a plurality of windings 220. The plurality of windings 220 are circumferentially distributed around the axis. The power magnetic ring 201 and the plurality of windings 220 are axially spaced apart. The windings 220 are used to generate a magnetic field to drive the power magnetic ring 201 to drive the rotor assembly 100 to rotate. The casing panel 210 is located between the rotor assembly 100 and the plurality of windings 220, and the casing panel 210 separates the fluid environment in which the rotor is located from the plurality of windings 220.

[0122] As a second aspect of the present invention, there is provided an electronic device, such as Figure 17 As shown, the electronic equipment includes:

[0123] One or more processors 101;

[0124] The memory 102 stores one or more computer programs. When the one or more computer programs are executed by the one or more processors 101, the one or more processors 101 implement the blood pump driving method provided by the embodiment of the present invention.

[0125] In the present invention, the electronic device can control the stator assembly 200 of the blood pump to apply an axial adjustment force to the rotor assembly 100, so that the rotor assembly 100 is located in a magnetic suspension position maintaining a first preset distance h1 from the stator assembly 200, thereby ensuring the stability of the axial position of the rotor assembly 100, and effectively preventing the rotor assembly 100 from contacting and rubbing or colliding with the internal structure of the housing (such as the first bearing sleeve 361 and the annular transition platform 314), thereby ensuring the service life of the blood pump and the safety of medical operations.

[0126] As an optional embodiment of the present invention, Figure 17 As shown, the electronic device further includes at least one I / O interface 103 , and the electronic device is connected to the blood pump via the I / O interface 103 .

[0127] As a third aspect of the present invention, there is provided a blood pump, such as Figure 1 、 Figure 8 As shown, the blood pump includes a controller, a rotor assembly 100, a stator assembly 200, and a housing 300. The rotor assembly 100 and the stator assembly 200 are coaxially spaced apart in the housing 300. The rotor assembly 100 and the stator assembly 200 are spaced apart in the housing 300 along the rotation axis of the rotor assembly 100. The rotor assembly 100 can rotate about its own axis under the action of the magnetic field generated by the stator assembly 200 to drive the fluid into and out of the housing 300. The blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing 130 and a first outer magnetic bearing 360 that interact with each other. The first outer magnetic bearing 360 is disposed on the inner wall of the housing 300, and the first inner magnetic bearing 130 is disposed on the rotor assembly 100. The controller is used to implement the driving method of the blood pump provided in the embodiment of the present invention.

[0128] In the present invention, the rotor assembly 100 and the stator assembly 200 of the blood pump are coaxially spaced apart and arranged in the housing 300. The stator assembly 200 can generate a rotating magnetic field to drive the rotor assembly 100 to rotate and drive the fluid flow through the blades 112. The controller can control the stator assembly 200 to apply an axial adjustment force to the rotor assembly 100, so that the rotor assembly 100 is located in a magnetic suspension position maintaining a first preset distance h1 from the stator assembly 200, thereby ensuring the stability of the axial position of the rotor assembly 100, and can effectively prevent the rotor assembly 100 from contacting and rubbing or colliding with the internal structure of the housing (such as the first bearing sleeve 361 and the annular transition platform 314), thereby ensuring the service life of the blood pump and the safety of medical operations.

[0129] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the blood pump also includes a second magnetic bearing assembly, which includes a second inner magnetic bearing 120 and a second outer magnetic bearing 350 that interact with each other. The second outer magnetic bearing 350 is arranged on the inner wall of the shell 300, and the second inner magnetic bearing 120 is arranged on the rotor assembly 100.

[0130] As an optional embodiment of the present invention, Figure 2 、 Figure 6 、 Figure 9 、 Figure 11 As shown, when the rotor assembly 100 is in the magnetic suspension position, the axial position of the second inner magnetic bearing 120 corresponds to the second outer magnetic bearing 350 , and the first inner magnetic bearing 130 extends beyond the first outer magnetic bearing 360 toward the stator assembly 200 .

[0131] As an optional embodiment of the present invention, Figure 5 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the second inner magnetic bearing 120 and the stator assembly 200 is smaller than the distance between the second outer magnetic bearing 350 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the stator assembly 200 remains relatively stable.

[0132] As an optional embodiment of the present invention, Figure 5 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the first inner magnetic bearing 130 and the stator assembly 200 is smaller than the distance between the first outer magnetic bearing 360 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the stator assembly 200 remains relatively stable.

[0133] As an optional embodiment of the present invention, Figure 8 As shown, the blood pump further includes a limiting bracket 390 , which is disposed in the housing 300 and located on a side of the rotor assembly 100 away from the stator assembly 200 along the direction of the rotation axis of the rotor assembly 100 .

[0134] As an optional embodiment of the present invention, Figure 8 、 Figure 10As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the second inner magnetic bearing 120 and the stator assembly 200 is greater than the distance between the second outer magnetic bearing 350 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the limiting bracket remains relatively stable.

[0135] As an optional embodiment of the present invention, Figure 8 、 Figure 10 As shown, when the stator assembly 200 is not powered on, in the direction of the rotation axis of the rotor assembly 100, the distance between the first inner magnetic bearing 130 and the stator assembly 200 is greater than the distance between the first outer magnetic bearing 360 and the stator assembly 200, so that the positional relationship between the rotor assembly 100 and the limiting bracket remains relatively stable.

[0136] As an optional embodiment of the present invention, Figure 1 、 Figure 8 As shown, the blood pump further includes a displacement sensor module 170 and an induction coil 360. The displacement sensor module is arranged on the rotor assembly 100, and the induction coil is arranged on the inner wall of the shell 300. In the radial projection direction, the axial position of the induction coil partially overlaps with the radial projection surface of the displacement sensor module.

[0137] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the housing 300 has at least one fluid outlet (for example, it can include a first fluid outlet 313 and a second fluid outlet 323 ), and the rotor assembly 100 can drive the fluid to flow into the housing 300 from the fluid inlet 302 through the blades 112 and flow out of the housing 300 through the fluid outlet.

[0138] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the limiting bracket 390 includes a contact portion 391 and a plurality of connecting portions 392 , the contact portion 391 is used to contact the end of the rotor assembly 100 , the plurality of connecting portions 392 are distributed circumferentially, the contact portion 391 is fixed to the shell 300 through the plurality of connecting portions 392 , and an inlet channel is formed between adjacent connecting portions 392 .

[0139] In order to further ensure the stability of the position of the rotor assembly 100, as a preferred embodiment of the present invention, as Figure 1 、 Figure 7 、 Figure 8 、 Figure 13As shown, a limiting groove 394 is formed on the surface of the contact portion 391 facing the rotor assembly 100 , and one end of the rotor assembly 100 facing the contact portion 391 can be accommodated in the limiting groove 394 .

[0140] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the diameter of one end of the rotor assembly 100 facing the contact portion 391 gradually decreases in a direction toward the contact portion 391 .

[0141] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the rotor assembly 100 further includes an impeller 110 and an impeller hub 180 , the blades 112 are located on the impeller 110 , the first internal magnetic bearing 130 is located between the impeller 110 and the stator assembly 200 , and the second internal magnetic bearing 120 is located on the side of the impeller 110 away from the first internal magnetic bearing 130 .

[0142] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the housing 300 has a plurality of first fluid outlets 313 , which are circumferentially distributed around the axis, and the axial positions of the plurality of first fluid outlets 313 correspond to the axial positions of the impeller 110 .

[0143] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the housing 300 has a plurality of second fluid outlets 323 , which are circumferentially distributed around the axis, and the axial positions of the plurality of second fluid outlets 323 are located between the first external magnetic bearing 360 and the stator assembly 200 .

[0144] like Figure 2 、 Figure 9The figure shows a schematic diagram of the flow path of blood when flowing through the interior of a blood pump in some embodiments of the present invention. The blood (the arrow in the figure indicates the direction of blood flow) flows into the first housing 310 from the fluid inlet 302 and flows through the first flow channel between the inner wall of the first housing 310 and the rotor assembly 100. Part of the blood flows directly out of the blood pump through the first fluid outlet 313 between the first connecting bars 312, and part of the blood continues to flow into the second housing 320 and flows through the second flow channel between the inner wall of the second housing 320 and the rotor assembly 100. Then, it flows out of the blood pump through the second fluid outlet 323 between the second connecting bars 322.

[0145] In order to ensure the reliability of the blood pump, as a preferred embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the impeller hub 180 includes a receiving member 182 and a contact member 183. The receiving member 182 is fixedly connected to the contact member 183. The second internal magnetic bearing 120 is fixedly arranged inside the receiving member 182. The contact member 183 is located on the side of the receiving member 182 away from the impeller 110. The contact member 183 can be accommodated in the limiting groove 394.

[0146] In an embodiment of the present invention, the impeller hub 180 includes a receiving member 182 and a contact member 183, and the contact member 183 at the end contacts the contact portion 391, so that after the contact member 183 is worn, only the contact member 183 can be replaced, thereby ensuring the reliability of the blood pump and extending the service life of the blood pump.

[0147] To further ensure the reliability of the blood pump, as a preferred embodiment of the present invention, the material of the contact member 183 can be selected to be a material with high hardness and wear resistance. For example, the material of the contact member 183 can include sapphire or ceramic.

[0148] Optionally, the contact member 183 is made of sapphire or ceramic.

[0149] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the rotor assembly 100 further includes a central shaft 150 , and the impeller 110 , the second internal magnetic bearing 120 and the first internal magnetic bearing 130 are all fixedly disposed on the central shaft 150 .

[0150] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 12 、 Figure 13As shown, the impeller 110 includes a fixed cylinder 111 and a plurality of blades 112 . The fixed cylinder 111 is sleeved and fixed on the central shaft 150 . The plurality of blades 112 are fixedly arranged on the outer wall of the fixed cylinder 111 , and the plurality of blades 112 are circumferentially distributed around the axis of the rotor assembly 100 .

[0151] As an optional embodiment of the present invention, the impeller 110 includes a pair of blades 112 .

[0152] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the limiting bracket 390 further includes a fixing ring 393 , the outer side surface of the fixing ring 393 is fixedly connected to the inner wall of the shell 300 , and a plurality of connecting portions 392 are connected between the contact portion 391 and the fixing ring 393 .

[0153] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the inner diameter of the fixing ring 393 gradually increases toward the stator assembly 200 .

[0154] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the rotor assembly 100 also includes a power magnetic ring 201, and the stator assembly 200 includes a casing panel 210 and a plurality of windings 220. The plurality of windings 220 are circumferentially distributed around the axis. The power magnetic ring 201 and the plurality of windings 220 are axially spaced apart. The windings 220 are used to generate a magnetic field to drive the power magnetic ring 201 to drive the rotor assembly 100 to rotate. The casing panel 210 is located between the rotor assembly 100 and the plurality of windings 220, and the casing panel 210 separates the fluid environment in which the rotor is located from the plurality of windings 220.

[0155] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the shell 300 includes a guide shell 301 and a stator shell. The guide shell 301 and the stator shell are distributed along the axial direction and fixedly connected to each other. The fluid inlet 302 and the fluid outlet are both located on the guide shell 301. Multiple windings 220 are arranged in the stator shell, and the shell panel 210 closes the opening of the stator shell on the side facing the fluid inlet 302.

[0156] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the stator assembly 200 further includes a circuit board 230 , which is fixedly connected to the plurality of windings 220 . The circuit board 230 is used to supply power to the plurality of windings 220 so that the windings 220 generate a magnetic field.

[0157] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the stator assembly 200 further includes an insulating ring 240 , which is disposed between the plurality of windings 220 to maintain spacing between the plurality of windings 220 to prevent short circuits between the windings 220 .

[0158] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the housing 300 further includes a contraction housing 340 , and the blood pump further includes a conduit 400 . The diameter of the conduit 400 is smaller than that of the stator housing 330 . The contraction housing 340 is transitionally connected between the conduit 400 and the end of the stator housing 330 away from the fluid inlet 302 .

[0159] As an optional embodiment of the present invention, Figure 7 、 Figure 13 As shown, the guide housing 301 includes a first housing 310 and a second housing 320. The first housing 310 includes a first guide tube 311 and a plurality of first connecting bars 312. The second housing 320 includes a second guide tube 321 and a plurality of second connecting bars 322. The first guide tube 311, the second guide tube 321 and the stator housing 330 are coaxially arranged. One end of the first guide tube 311 has a fluid inlet 302. The plurality of first connecting bars 312 are connected between the other end of the first guide tube 311 and an end of the second guide tube 321 facing the fluid inlet 302. The plurality of second connecting bars 322 are connected between an end of the second guide tube 321 facing away from the fluid inlet 302 and an end of the stator housing 330 facing the fluid inlet 302.

[0160] The fluid outlets include a plurality of first fluid outlets 313 located between adjacent first connecting bars 312 , and a plurality of second fluid outlets 323 located between adjacent second connecting bars 322 .

[0161] As an optional embodiment of the present invention, Figure 7 、 Figure 13 As shown, the first guide tube 311 and the plurality of first connecting bars 312 are formed as one body.

[0162] As an optional embodiment of the present invention, the first connecting bar 312 is connected to the second housing 320 by welding.

[0163] As an optional embodiment of the present invention, Figure 7 、 Figure 13 As shown, the second guide tube 321 and the plurality of second connecting bars 322 are formed as one body.

[0164] As an optional embodiment of the present invention, the second connecting bar 322 is welded to the stator housing 330 .

[0165] In the case where the blood pump does not include the limiting bracket 390, as an optional embodiment of the present invention, as shown in FIG. Figure 1 As shown, the blood pump also includes a second bearing sleeve 351, which is coaxial with the first guide tube 311 and fixedly arranged on the inner wall of the first guide tube 311. The outer wall of the second bearing sleeve 351 has a first annular groove extending around the axis, and the second external magnetic bearing 350 is accommodated in the first annular groove.

[0166] In the case where the blood pump includes a limiting bracket 390, as an optional embodiment of the present invention, as shown in FIG. Figure 8 As shown, the blood pump further includes a second bearing sleeve 351. The inner wall of the first flow guide sleeve 311 has an annular transition platform 314 extending around the axis. The second bearing sleeve 351 is coaxial with and sleeved within the second internal magnetic bearing 120. The annular transition platform 314 abuts the side of the second internal magnetic bearing 120 facing away from the fluid inlet 302. The ends of the second bearing sleeve 351 abut the annular transition platform 314 and the retaining ring 393, respectively. The inner diameter of the second bearing sleeve 351 corresponds to the maximum inner diameter of the annular transition platform 314 and the retaining ring 393. The inner diameter of the annular transition platform 314 on the side facing the fluid inlet 302 corresponds to the inner diameter of the end of the first flow guide sleeve 311 facing away from the fluid inlet 302. The inner diameter of the annular transition platform 314 gradually increases away from the fluid inlet 302, thereby ensuring a smooth surface of the blood flow path within the housing 300, preventing the formation of dead zones that could cause clotting, and improving the safety of medical procedures.

[0167] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the blood pump also includes a first bearing sleeve 361, which is coaxial with the second guide tube 321 and fixedly arranged on the inner wall of the second guide tube 321. The outer wall of the first bearing sleeve 361 has a second annular groove extending around the axis, and the first external magnetic bearing 360 is accommodated in the second annular groove.

[0168] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the end of the second guide tube 321 facing the fluid inlet 302 has an annular guide platform 324, and the end of the annular guide platform 324 facing the fluid inlet 302 is located between the multiple first connecting bars 312, and the height of the surface of the annular guide platform 324 facing the fluid inlet 302 gradually decreases along the direction away from the stator assembly 200, thereby forming a smooth inclined surface at the end of the annular guide platform 324 facing the fluid inlet 302, thereby improving the smoothness of blood diversion.

[0169] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the second annular groove is connected to the end surface of the first bearing sleeve 361 facing the fluid inlet 302 , and the first external magnetic bearing 360 is in contact with the end of the annular guide platform 324 facing away from the fluid inlet 302 .

[0170] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the inner diameter of the first bearing sleeve 361 on the side away from the fluid inlet 302 gradually increases in the direction away from the fluid inlet 302, thereby ensuring the smoothness of the blood flow channel surface inside the housing 300, avoiding the formation of dead zones that cause coagulation, and improving the safety of medical operations.

[0171] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the induction coil 370 is fixed in the second guide tube 321 .

[0172] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the blood pump also includes a coil fixing ring 380, and a first coil accommodating groove is provided on the inner wall of the annular guide platform 324. The coil fixing ring 380 and the annular guide platform 324 are coaxially accommodated in the first coil accommodating groove; a second coil accommodating groove is formed on the outer wall of the coil fixing ring 380, and the induction coil 370 is wound and fixed in the second coil accommodating groove.

[0173] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13As shown, the outer wall of the coil fixing ring 380 also has a lead-out groove 381 connected to the second coil accommodating groove, and the bottom of the first coil accommodating groove has a lead-out hole 325 that passes through the outer wall of the second guide tube 321. The position of the lead-out hole 325 corresponds to the position of the lead-out groove 381, and the lead-out end of the induction coil 370 passes through the lead-out groove 381 and the lead-out hole 325.

[0174] As an optional embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the outer wall of the second housing 320 has a first wire groove 326 extending along the axial direction, and the outer wall of the stator housing 330 has a second wire groove 332 extending along the axial direction. One end of the first wire groove 326 is connected to the lead-out hole 325, and the other end of the first wire groove 326 is connected to the second wire groove 332. The lead-out end of the induction coil 370 is set in the first wire groove 326 and the second wire groove 332.

[0175] As an optional embodiment of the present invention, the first wire groove 326 and the second wire groove 332 are both filled with filling glue, and the lead end of the induction coil 370 is fixed in the first wire groove 326 and the second wire groove 332 by the filling glue.

[0176] As an optional embodiment of the present invention, the lead end of the induction coil 370 extends through the shrink housing 340 into the conduit 400, and together with the power supply line of the stator assembly 200 (connected to the circuit board 230), passes through the conduit 400 out of the human body and is connected to the controller.

[0177] In order to further improve the structural strength of the rotor assembly 100, as a preferred embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 12 、 Figure 13 As shown, the rotor assembly 100 also includes a rotor housing 160, which is sleeved on the central shaft 150, and has a bearing accommodating cavity and a power accommodating cavity in the rotor housing 160. The first internal magnetic bearing 130 is accommodated in the bearing accommodating cavity, and the power magnetic ring 201 is accommodated in the power accommodating cavity.

[0178] In an embodiment of the present invention, the first internal magnetic bearing 130 and the power magnetic ring 201 are respectively accommodated in the bearing accommodating cavity and the power accommodating cavity, so that the axial position of the first internal magnetic bearing 130 and the power magnetic ring 201 is further positioned by using the rotor housing 160, thereby ensuring the stability of the relative position relationship between the components, improving the structural strength of the rotor assembly 100, and at the same time separating the blood from the first internal magnetic bearing 130 and the power magnetic ring 201, avoiding direct contact between the first internal magnetic bearing 130 and the power magnetic ring 201 and the liquid environment, thereby preventing the various components mounted on the central shaft 150 from being corroded, and ensuring the service life of the blood pump.

[0179] As an optional embodiment of the present invention, Figure 12 As shown, the rotor housing 160 further has a sensing accommodating cavity, and the displacement sensor module 170 is accommodated in the sensing accommodating cavity.

[0180] In order to further improve the structural strength of the rotor assembly 100, as a preferred embodiment of the present invention, Figure 1 、 Figure 7 、 Figure 8 、 Figure 12 As shown, the rotor housing 160 has a boss portion 168 at one end facing the fluid inlet 302, and the fixed cylinder 111 of the impeller 110 has a connecting groove at one end facing away from the fluid inlet 302, and the boss portion 168 is accommodated in the connecting groove, so that mechanical limiting is achieved by utilizing the snap-fit ​​relationship between the boss portion 168 and the connecting groove, thereby ensuring the concentricity between the rotor housing 160 and the impeller 110, and further ensuring the overall structural strength of the rotor assembly 100 during rotation.

[0181] As an optional embodiment of the present invention, impeller 110 is bonded to rotor housing 160. As a preferred embodiment of the present invention, rotor housing 160 is an injection-molded component, thereby ensuring circumferential uniformity of rotor housing 160 and preventing over-positioning of components on the central axis due to steps between the internal chamber and through-hole structure of rotor housing 160, thereby reducing stress concentration within the rotor assembly and ensuring the reliability of the blood pump's overall structure.

[0182] The above are only specific embodiments of the present invention, but the scope of protection of the present invention is not limited thereto. Those skilled in the art should understand that the present invention includes but is not limited to the contents described in the drawings and the above specific embodiments. Any modifications that do not deviate from the functional and structural principles of the present invention are intended to be included within the scope of the claims.

Claims

1. A method for driving a blood pump, characterized in that: The blood pump includes a rotor assembly, a stator assembly, and a housing. The rotor assembly and the stator assembly are spaced apart in the housing along the rotation axis of the rotor assembly, and the rotor assembly can rotate about its own axis under the action of the magnetic field generated by the stator assembly to drive fluid into and out of the housing. The blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing and a first outer magnetic bearing that interact with each other. The first outer magnetic bearing is arranged on the inner wall of the housing, and the first inner magnetic bearing is arranged on the rotor assembly. The driving method of the blood pump includes: Controlling the stator assembly to drive the rotor assembly to rotate around its own axis; The stator assembly is controlled to apply an adjustment force to the rotor assembly along the rotation axis of the rotor assembly through the electromagnetic field between the stator assembly and the rotor assembly, so as to adjust the position of the rotor assembly in the housing so that the rotor assembly maintains a first preset distance from the stator assembly during rotation.

2. The blood pump driving method according to claim 1, wherein: The blood pump further includes a second magnetic bearing assembly, the second magnetic bearing assembly including a second inner magnetic bearing and a second outer magnetic bearing interacting with each other, the second outer magnetic bearing being disposed on an inner wall of the housing, and the second inner magnetic bearing being disposed on the rotor assembly; When the stator assembly is not powered on, the distance between the first internal magnetic bearing and the stator assembly is different from the distance between the first external magnetic bearing and the stator assembly, and the distance between the second internal magnetic bearing and the stator assembly is different from the distance between the second external magnetic bearing and the stator assembly.

3. The blood pump driving method according to claim 2, characterized in that: The controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes: The stator assembly is controlled to apply an adjusting force to the rotor assembly along the direction of the rotation axis of the rotor assembly through the electromagnetic field between the stator assembly and the rotor assembly, so that the distance between the first inner magnetic bearing and the stator assembly is smaller than the distance between the first outer magnetic bearing and the stator assembly, and the second magnetic bearing assembly can only generate a radial force.

4. The blood pump driving method according to claim 2, wherein: The controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes: controlling the stator assembly to provide an adjustment repulsive force to the rotor assembly along the direction of the rotation axis of the rotor assembly, so that the rotor assembly moves away from the stator assembly along the direction of the rotation axis of the rotor assembly to be spaced apart from the stator assembly by the first preset distance; The stator assembly is controlled to provide an adjusting balancing force along the rotation axis of the rotor assembly to the rotor assembly through a magnetic field, so that the rotor assembly maintains the first preset distance from the stator assembly.

5. The blood pump driving method according to claim 4, characterized in that: When the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the second inner magnetic bearing and the stator assembly is smaller than the distance between the second outer magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the stator assembly remains relatively stable.

6. The method for driving a blood pump according to claim 4 or 5, characterized in that: When the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the first internal magnetic bearing and the stator assembly is smaller than the distance between the first external magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the stator assembly remains relatively stable.

7. The blood pump driving method according to claim 2, characterized in that: The blood pump further includes a limiting bracket, which is disposed in the housing and located on a side of the rotor assembly away from the stator assembly along the direction of the rotation axis of the rotor assembly; The controlling the stator assembly to apply an adjusting force along the rotation axis of the rotor assembly to the rotor assembly through an electromagnetic field between the stator assembly and the rotor assembly includes: controlling the stator assembly to provide an adjusted attraction force along the rotation axis of the rotor assembly to the rotor assembly, so that the rotor assembly moves closer to the stator assembly along the rotation axis of the rotor assembly to a first preset distance from the stator assembly; The stator assembly is controlled to provide an adjusting balancing force along the rotation axis of the rotor assembly to the rotor assembly through a magnetic field, so that the rotor assembly maintains the first preset distance from the stator assembly.

8. The blood pump driving method according to claim 7, characterized in that: The blood pump further includes a limiting bracket, which is disposed in the housing and located on a side of the rotor assembly away from the stator assembly along the direction of the rotation axis of the rotor assembly; When the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the second inner magnetic bearing and the stator assembly is greater than the distance between the second outer magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the limit bracket remains relatively stable.

9. The blood pump driving method according to claim 7 or 8, characterized in that: When the stator assembly is not powered on, in the direction of the rotation axis of the rotor assembly, the distance between the first internal magnetic bearing and the stator assembly is greater than the distance between the first external magnetic bearing and the stator assembly, so that the positional relationship between the rotor assembly and the limit bracket remains relatively stable.

10. The method for driving a blood pump according to any one of claims 1 to 5, 7 to 8, characterized in that: The rotor assembly further includes a displacement sensor module and an induction coil, wherein the displacement sensor module is disposed on the rotor assembly, and the induction coil is disposed on the inner wall of the housing; the displacement sensor module is located on a side of the first internal magnetic bearing away from the stator assembly, and in a radial projection direction, an axial position of the induction coil partially overlaps with a radial projection surface of the displacement sensor module. The blood pump driving method further includes: Based on the feedback signal of the induction coil, the stator assembly is controlled to provide the magnitude and direction of the regulating force to the rotor assembly.

11. An electronic device comprising: one or more processors; A memory having one or more computer programs stored thereon, wherein when the one or more computer programs are executed by the one or more processors, the one or more processors implement the blood pump driving method according to any one of claims 1 to 10.

Images