Blood pump

Abstract

The utility model provides a blood pump which comprises a rotor assembly, a stator assembly and a shell, the rotor assembly and the stator assembly are arranged in the shell in a spaced mode in the rotation axis direction of the rotor assembly, the rotor assembly comprises an impeller, a power magnetic ring and a center shaft, and the blood pump further comprises a first magnetic bearing assembly. The first magnetic bearing assembly comprises a first inner magnetic bearing and a first outer magnetic bearing which are matched with each other, the first outer magnetic bearing is arranged on the inner wall of the shell, and the impeller, the first inner magnetic bearing and the power magnetic ring are all fixedly arranged on the center shaft; the rotor assembly can rotate around the axis of the rotor assembly so as to drive fluid to flow into and out of the shell, and in the power-on state, the rotor assembly can be spaced from the stator assembly by a first preset distance in the rotating process. All the components of the rotor assembly are fixed on the central shaft, so that the stability of relative positions of all the components is guaranteed, the overall structural strength of the rotor assembly is improved, the stability of operation of the blood pump is guaranteed, and the service life of the blood pump is prolonged.

Description

Technical Field

[0001] This utility model relates to the field of medical supplies, specifically to a blood pump. Background Technology

[0002] A blood pump is a commonly used medical device that provides the power to flow blood. For example, the heart is the body's vital organ, and its main function is to power blood flow, transporting blood to all parts of the body. When a patient's heart malfunctions and cannot provide sufficient power for blood flow, a blood pump needs to be inserted into the patient's heart to replace the heart in providing the power for blood flow and to prevent life-threatening situations.

[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, thus ensuring normal blood flow in the patient's blood vessels.

[0004] However, in actual medical operations, the reaction force of blood flow on the blood pump rotor fluctuates significantly, resulting in poor rotor stability and a generally short service life for blood pumps. Therefore, providing a structurally stable blood pump has become a pressing technical problem to be solved in this field. Utility Model Content

[0005] This invention aims to address one of the technical problems in related technologies to a certain extent. Therefore, this invention provides a blood pump that ensures the stability of the rotor's operating position and guarantees the service life of the blood pump.

[0006] To achieve the above objectives, this utility model provides a blood pump, including 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. The rotor assembly includes an impeller, a power magnetic ring, and a central shaft. The blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing and a first outer magnetic bearing that cooperate with each other. The first outer magnetic bearing is disposed on the inner wall of the housing. The impeller, the first inner magnetic bearing, and the power magnetic ring are all fixedly disposed on the central shaft.

[0007] The rotor assembly can rotate around 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 in the energized state, the rotor assembly can be spaced at a first preset distance from the stator assembly during rotation.

[0008] Optionally, the central shaft includes a stage and a power section. The power section is located on the axial side of the stage facing the stator assembly. The diameter of the central shaft on the stage is larger than the diameter of the two axial portions of the central shaft on the stage. The power magnetic ring and the first inner magnetic bearing are both sleeved on the central shaft. The power magnetic ring is located on the power section and corresponds to the end face of the stage. The first inner magnetic bearing is located on the side of the stage away from the stator assembly and corresponds to the end face of the stage.

[0009] Optionally, the rotor assembly further includes a rotor housing, which is sleeved on the central shaft, and the rotor housing has a bearing housing cavity and a power housing cavity, wherein the first inner magnetic bearing is housed in the bearing housing cavity and the power magnetic ring is housed in the power housing cavity.

[0010] Optionally, the blood pump further includes a second magnetic bearing assembly, which includes a second inner magnetic bearing and a second outer magnetic bearing, the second outer magnetic bearing being disposed on the inner wall of the housing;

[0011] The rotor assembly further includes an impeller hub, the impeller is sleeved on the central shaft, the impeller is located on the axial side of the rotor housing away from the stator assembly and is fixedly connected to the rotor housing, the impeller hub is fixedly connected to the end of the impeller away from the stator assembly or is integrally formed with the impeller, and the second internal magnetic bearing is disposed inside the impeller hub.

[0012] Optionally, the second inner magnetic bearing is sleeved on the central shaft.

[0013] Optionally, the blood pump further includes a displacement sensor module and an induction coil, the induction coil being disposed on the inner wall of the housing; in the radial projection direction, the axial position of the induction coil partially overlaps with the radial projection surface of the displacement sensor module;

[0014] The central shaft further includes a first positioning section and a second positioning section. The first positioning section is connected to the axial side of the stage away from the stator assembly, and the second positioning section is connected to the axial side of the first positioning section away from the stator assembly. The diameter of the first positioning section is smaller than the diameter of the stage, and the diameter of the second positioning section is smaller than the diameter of the first positioning section. The first inner magnetic bearing is sleeved on the first positioning section, and the displacement sensor module and the impeller are both sleeved on the second positioning section, with the displacement sensor module corresponding to the end face of the first positioning section.

[0015] Optionally, the central shaft further includes a third positioning section, which is connected to the second positioning section on the axial side away from the stator assembly, and the diameter of the third positioning section is smaller than the diameter of the second positioning section; the second inner magnetic bearing is sleeved on the third positioning section.

[0016] Optionally, the rotor assembly has a flow channel, the flow channel having at least one liquid inlet on the surface of the rotor assembly, the flow channel including an in-shaft flow channel formed in the central shaft, the in-shaft flow channel having a liquid outlet at one end of the central shaft facing the stator assembly.

[0017] Optionally, the internal flow channel includes a central hole and at least one inlet branch hole. The central hole extends along the axial direction of the central shaft and one end of the central hole forms the liquid outlet. One end of the inlet branch hole communicates with the central hole, and the other end of the inlet branch hole forms an opening on the surface of the central shaft.

[0018] The rotor assembly has at least one flow guide branch hole, and the flow guide branch hole corresponds one-to-one with the inlet branch hole. One end of the flow guide branch hole forms the liquid inlet on the surface of the rotor assembly, and the other end of the flow guide branch hole is connected to the corresponding inlet branch hole.

[0019] Optionally, the flow channel further includes a hub channel formed in the impeller hub, the end of the hub channel facing the stator assembly being connected to the shaft flow channel, and the end of the hub channel away from the stator assembly being formed as the liquid inlet.

[0020] In the blood pump provided by this utility model, the rotor assembly achieves radial positioning through the radial repulsion between the inner and outer magnetic bearings. Compared with the traditional positioning method using mechanical bearings, this effectively reduces rotor rotation resistance and improves the blood pump's heat generation. Furthermore, components such as the impeller and the first inner magnetic bearing in the rotor assembly are fixed to the central shaft, ensuring the stability of the relative positions of the components, improving the overall structural strength of the rotor assembly, and reducing the deformation amplitude caused by the flow field during rotation. This further enhances the stability of the rotor assembly's position within the housing, allowing it to remain stably suspended in a completely suspended state. This ensures the stability of the blood pump's operation, reduces friction and wear between components on the rotor assembly, and extends the blood pump's service life.

[0021] Furthermore, in this invention, the stator assembly and the rotor assembly are spaced apart along the axial direction. That is, in the embodiment of this invention, the motor structure formed by the power magnetic rings in the stator assembly and the rotor assembly is an axial magnetic field motor (disc motor). The outer diameter of the magnetic ring in the rotor assembly is not limited by the internal dimensions of the stator, which can effectively ensure the transmission efficiency of the motor and improve the blood pump's blood transfusion capacity. Attached Figure Description

[0022] The present invention will be further described below with reference to the accompanying drawings:

[0023] Figure 1 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0024] Figure 2 yes Figure 1 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0025] Figure 3 yes Figure 1 Schematic diagram of the internal fluid flow path of a blood pump;

[0026] Figure 4 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0027] Figure 5 yes Figure 4 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0028] Figure 6 yes Figure 4 Schematic diagram of the internal fluid flow path of a blood pump;

[0029] Figure 7 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0030] Figure 8 yes Figure 7 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0031] Figure 9 yes Figure 7 Schematic diagram of the internal fluid flow path of a blood pump;

[0032] Figure 10 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0033] Figure 11 yes Figure 10 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0034] Figure 12 yes Figure 10 Schematic diagram of the internal fluid flow path of a blood pump;

[0035] Figure 13 This is a schematic cross-sectional view of the rotor housing in the blood pump provided in this embodiment of the utility model;

[0036] Figure 14This is a schematic diagram of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0037] Figure 15 This is a front view of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0038] Figure 16 This is a side view of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0039] Figure 17 This is an exploded view of the blood pump structure provided in this embodiment of the utility model;

[0040] Figures 18 to 22 This is a schematic diagram of the assembly process of the blood pump provided in this embodiment of the utility model.

[0041] Explanation of reference numerals in the attached figures

[0042] 100: Rotor assembly; 101: Liquid inlet.

[0043] 102: Liquid outlet; 110: Impeller

[0044] 111: Fixed cylinder; 112: Blade

[0045] 120: Second internal magnetic bearing; 130: First internal magnetic bearing

[0046] 201: Power magnetic ring; 150: Central shaft

[0047] L1: Stage L2: Power Section

[0048] L3: First positioning segment L4: Second positioning segment

[0049] L5: Third positioning section 151: In-axis flow channel

[0050] 1511: Center hole; 1512: Inlet branch hole

[0051] 1512a: First inlet branch hole; 1512b: Second inlet branch hole

[0052] 160: Rotor housing; 160a: Split housing

[0053] 161: Bearing housing cavity 162: Power housing cavity

[0054] 163: Induction receiving cavity; 164: First step hole

[0055] 165: Through hole; 166: Second step hole

[0056] 167: Third step hole; 168: Boss part

[0057] 170: Displacement sensor module; 180: Impeller hub

[0058] 181: Hub flow channel; 190: Guide branch hole

[0059] 191: First guide branch hole; 192: Second guide branch hole

[0060] 200: Stator assembly; 210: Housing panel

[0061] 211: Guide fins 212: Positioning plate

[0062] 213: First annular protrusion; 214: Flow guiding space

[0063] 220: Winding 230: Circuit Board

[0064] 240: Insulating ring; 300: Housing

[0065] 301: Flow guide shell; 302: Fluid inlet

[0066] 310: First casing; 311: First deflector tube

[0067] 312: First connecting bar; 313: First fluid outlet

[0068] 314: Annular transition platform; 320: Second housing

[0069] 321: Second guide tube; 322: Second connecting strip

[0070] 323: Second fluid outlet; 324: Annular guide platform

[0071] 325: Outlet hole; 326: First wire groove

[0072] 330: Stator housing; 331: Second annular protrusion

[0073] 332: Second guide tube groove; 340: Shrink housing

[0074] 350: Second external magnetic bearing; 351: Second bearing sleeve

[0075] 360: First external magnetic bearing; 361: First bearing sleeve

[0076] 370: Induction coil; 380: Coil retaining ring

[0077] 381: Outlet groove; 400: Conduit Detailed Implementation

[0078] The embodiments of this utility model are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described are intended to explain this utility model and should not be construed as limiting it.

[0079] The terms "an embodiment," "example," or "trademark" used in this specification refer to a particular feature, structure, or characteristic described in connection with the embodiment itself that may be included in at least one embodiment disclosed in this utility model. The phrase "in an embodiment" appearing in various places throughout the specification does not necessarily refer to the same embodiment.

[0080] 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, thus ensuring normal blood flow in the patient's blood vessels.

[0081] In related technologies, in order to minimize the resistance to rotor rotation and reduce the heat generated by the blood pump, the method of connecting the solid shaft structure in the rotor to the bearing in the housing is often abandoned. Instead, a magnetic levitation connection 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, the connection strength between the rotor components (such as the bonding between the power magnetic ring, magnetic bearing and impeller) is low. The rotor is prone to deformation during rotation, which affects the alignment between the rotor and the housing, affects the stability of the rotor's operating position, and the rotor is prone to deformation and damage after being subjected to the forces of complex flow fields for a long time, resulting in a short service life of the blood pump.

[0082] To solve the above-mentioned technical problems, this utility model provides a blood pump, such as... Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17 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. The rotor assembly 100 includes an impeller 110, a power magnetic ring 201, and a central shaft 150. The blood pump also includes a first magnetic bearing assembly, which includes an interacting first inner magnetic bearing 130 and a first outer magnetic bearing 360. 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 impeller 110, the first inner magnetic bearing 130, and the power magnetic ring 201 are all fixedly disposed on the central shaft 150.

[0083] The rotor assembly 100 can rotate around its own axis under the influence of the magnetic field generated by the stator assembly 200, thereby driving fluid to flow into and out of the housing 300, and in the energized state, such as Figure 3 , Figure 6 , Figure 9 , Figure 12 As shown, the rotor assembly 100 can be separated from the stator assembly 200 by a first preset distance h1 during rotation (i.e., enter a fully suspended state).

[0084] In the blood pump provided by this utility model, the rotor assembly 100 achieves radial positioning through the radial repulsion between the inner and outer magnetic bearings. Compared with the traditional positioning scheme using mechanical bearings, this effectively reduces rotor rotation resistance and improves the blood pump's heat generation. Furthermore, components such as the impeller 110 and the first inner magnetic bearing 130 in the rotor assembly 100 are fixed to the central shaft 150, ensuring the stability of the relative positions of the components, improving the overall structural strength of the rotor assembly 100, reducing the deformation amplitude of the rotor assembly 100 under the influence of the flow field during rotation, and thus improving the stability of the rotor assembly 100's position within the housing 300. This allows the rotor assembly 100 to remain stably in a completely suspended state (i.e., the rotor assembly 100 does not contact the internal structure of the housing radially or axially), ensuring the stability of the blood pump's operation, reducing frictional wear between the components of the rotor assembly 100, and extending the blood pump's service life.

[0085] Furthermore, in this invention, the stator assembly 200 and the rotor assembly 100 are arranged axially at intervals. That is, in this embodiment of the invention, the motor structure formed by the power magnetic ring 201 in the stator assembly 200 and the rotor assembly 100 is an axial magnetic field motor (disc motor). The outer diameter of the magnetic ring in the rotor assembly 100 is not limited by the internal size of the stator, which can effectively ensure the transmission efficiency of the motor and improve the blood pumping capacity.

[0086] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, one end of the housing 300 has a fluid inlet 302, the stator assembly 200 is fixedly disposed on the axial side of the rotor assembly 100 away from the fluid inlet 302, and the side wall of the housing 300 has at least one fluid outlet (for example, it may include a first fluid outlet 313 and a second fluid outlet 323), and the fluid outlet is located between the fluid inlet 302 and the stator assembly 200.

[0087] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10As shown, the blood pump also includes a second magnetic bearing assembly, which includes an interacting second inner magnetic bearing 120 and a second outer magnetic bearing 350. The second outer magnetic bearing 350 is disposed on the inner wall of the housing 300, and the second inner magnetic bearing 120 is disposed on the rotor assembly 100.

[0088] As a preferred embodiment of this utility model, such as Figure 2 , Figure 5 , Figure 8 , Figure 11 As shown, the central shaft 150 includes a stage L1 and a power section L2. The power section L2 is located on the axial side of the stage L1 facing the stator assembly 200. The diameter of the central shaft 150 in the stage L1 is larger than the diameter of the two axial sides of the central shaft 150 in the stage L1. The power magnetic ring 201 and the first inner magnetic bearing 130 are both sleeved on the central shaft 150. The power magnetic ring 201 is located on the power section L2 and corresponds to the end face of the stage L1. The first inner magnetic bearing 130 is located on the side of the stage L1 away from the stator assembly 200 and corresponds to the end face of the stage L1.

[0089] In this embodiment of the invention, the central shaft 150 has a stepped stage L1 with a diameter larger than the diameters of the two sides. This allows the axial position of the power magnetic ring 201 to be positioned using the step between the stepped stage L1 and the power section L2. The axial position of the first inner magnetic bearing 130 can also be positioned using the step between the stepped stage L1 and the part of the central shaft 150 facing away from the stator assembly 200. This further ensures the stability of the relative positional relationship between the components and improves the structural strength of the rotor assembly 100.

[0090] To further improve the structural strength of the rotor assembly 100, as a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 , Figure 13 As shown, the rotor assembly 100 also includes a rotor housing 160, which is sleeved on the central shaft 150. The rotor housing 160 has a bearing housing 161 and a power housing 162. The first inner magnetic bearing 130 is housed in the bearing housing 161, and the power magnetic ring 201 is housed in the power housing 162.

[0091] In this embodiment of the invention, the first inner magnetic bearing 130 and the power magnetic ring 201 are respectively housed in the bearing housing 161 and the power housing 162. This allows the rotor housing 160 to further position the axial positions of the first inner magnetic bearing 130 and the power magnetic ring 201, ensuring the stability of the relative positional relationship between the components and improving the structural strength of the rotor assembly 100. At the same time, it separates the blood from the first inner magnetic bearing 130 and the power magnetic ring 201, preventing them from directly contacting the liquid environment. This also prevents the components mounted on the central shaft 150 from being corroded, ensuring the service life of the blood pump.

[0092] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the rotor assembly 100 also includes an impeller hub 180, an impeller 110 is sleeved on the central shaft 150, the impeller 110 is located on the axial side of the rotor housing 160 facing the fluid inlet 302 and is fixedly connected to the rotor housing 160, the impeller hub 180 is fixedly connected to the end of the impeller 110 away from the stator assembly 200 or is integrally formed with the impeller 110, and the second inner magnetic bearing 120 is disposed inside the impeller hub 180.

[0093] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the impeller 110 includes a fixed cylinder 111 and multiple blades 112. The fixed cylinder 111 is sleeved and fixed on the central shaft 150, and the multiple blades 112 are fixedly disposed on the outer wall of the fixed cylinder 111, and the multiple blades 112 are circumferentially distributed around the axis of the rotor assembly 100.

[0094] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the impeller 110 includes a pair of blades 112.

[0095] To further improve the structural strength of the rotor assembly 100, as a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 , Figure 13 As shown, the rotor housing 160 has a boss 168 at the end facing the fluid inlet 302, and the fixed cylinder 111 of the impeller 110 has a connecting groove at the end away from the fluid inlet 302. The boss 168 is accommodated in the connecting groove, thereby achieving mechanical limiting by the engagement relationship between the boss 168 and the connecting groove, ensuring the alignment between the rotor housing 160 and the impeller 110, and further ensuring the overall structural strength of the rotor assembly 100 when it rotates.

[0096] As an optional embodiment of this utility model, the fixed cylinder 111 is bonded to the rotor housing 160.

[0097] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the impeller hub 180 has a streamlined design. Specifically, the end of the impeller hub 180 away from the impeller 110 has a diameter-changing section, and the diameter of the impeller hub 180 in the diameter-changing section gradually increases along the direction close to the impeller 110.

[0098] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 As shown, the second inner magnetic bearing 120 is mounted on the central shaft 150.

[0099] As a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the blood pump also includes a displacement sensor module 170 and an induction coil 370. The displacement sensor module 170 is disposed on the rotor assembly 100, and the induction coil 370 is disposed on the inner wall of the housing 300. In the radial projection direction, the radial projection surface of the induction coil 370 partially overlaps with the radial projection surface of the displacement sensor module 170.

[0100] In this embodiment of the present invention, a displacement sensor module 170 is provided on the rotor assembly 100, and an induction coil 370 is provided on the housing 300. The axial position of the induction coil 370 partially coincides with the axial position of the displacement sensor module 170. Thus, when the rotor assembly 100 moves axially, the length of the axial overlap between the induction coil 370 and the displacement sensor module 170 will also change accordingly. The axial position of the rotor assembly 100 can be determined by detecting parameters such as the inductance and voltage of the induction coil 370. By adjusting the force on the rotor assembly 100, feedback control of the rotor assembly 100 position can be achieved, ensuring that the rotor assembly 100 is in a fully suspended state, thereby ensuring the stability of the blood pump operation.

[0101] To further improve the structural strength of the rotor assembly 100, as a preferred embodiment of this utility model, such as Figure 2 , Figure 5 , Figure 8 , Figure 11 As shown, the central shaft 150 also includes a first positioning section L3 and a second positioning section L4. The first positioning section L3 is connected to the platform stage L1 on the axial side away from the stator assembly 200, and the second positioning section L4 is connected to the first positioning section L3 on the axial side away from the stator assembly 200. The diameter of the first positioning section L3 is smaller than the diameter of the platform stage L1, and the diameter of the second positioning section L4 is smaller than the diameter of the first positioning section L3. The first inner magnetic bearing 130 is sleeved on the first positioning section L3, and the displacement sensor module 170 and the impeller 110 are both sleeved on the second positioning section L4. The displacement sensor module corresponds to the end face position of the first positioning section L3.

[0102] In this embodiment of the utility model, the position of the displacement sensor module 170 corresponds to the connection position of the first positioning segment L3 and the second positioning segment L4. The step (shoulder) at the connection between the first positioning segment L3 and the second positioning segment L4 is used to axially position the displacement sensor module 170, ensuring the stability and accuracy of the axial position of the displacement sensor module 170, and further ensuring the overall structural strength of the rotor assembly 100.

[0103] As an optional embodiment of this utility model, such as Figure 13 As shown, the rotor housing 160 also has a sensing cavity 163, in which the displacement sensor module 170 is housed.

[0104] As an optional embodiment of this utility model, such as Figure 13As shown, the rotor housing 160 also has a first stepped hole 164, a through hole 165, a second stepped hole 166, and a third stepped hole 167, all of which are coaxially arranged with the rotor housing 160. Specifically, the through hole 165 extends from the power receiving cavity 162 to the surface of the rotor housing 160 facing away from the fluid inlet 302, and its diameter corresponds to the diameter of the power section L2; the first stepped hole 164 connects the bearing receiving cavity 161 and the power receiving cavity 162, and its diameter corresponds to the diameter of the stepped section L1; the second stepped hole 166 connects the sensing receiving cavity 163 and the bearing receiving cavity 161, and its diameter corresponds to the diameter of the first positioning section L3; the third stepped hole 167 extends from the sensing receiving cavity 163 to the surface of the rotor housing 160 facing the fluid inlet 302, and its diameter corresponds to the diameter of the second positioning section L4.

[0105] As an optional embodiment of this utility model, such as Figure 17 , Figure 18 As shown, the rotor housing 160 includes a pair of housing parts 160a. The two housing parts 160a are respectively embraced by the central shaft 150, the displacement sensor module 170, the first inner magnetic bearing 130 and the two sides of the power magnetic ring 201, and the mating surfaces of the housing parts 160a are bonded together.

[0106] In a preferred embodiment of this utility model, the rotor housing 160 is an integral injection molded part, which can ensure the circumferential uniformity of the rotor housing 160 and prevent the steps between the internal chambers and through-hole structures of the rotor housing 160 from causing over-positioning of the components on the central shaft, reduce the stress concentration problem inside the rotor assembly, and ensure the reliability of the overall structure of the blood pump.

[0107] As an optional embodiment of this utility model, such as Figure 5 As shown, the central shaft 150 also includes a third positioning section L5, which is connected to one side of the second positioning section L4 away from the stage L1. The diameter of the third positioning section L5 is smaller than the diameter of the second positioning section L4. The second inner magnetic bearing 120 is sleeved on the third positioning section L5.

[0108] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17As shown, the housing 300 includes a flow guide shell 301 and a stator housing 330. The flow guide shell 301 and the stator housing 330 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 flow guide shell 301. Multiple windings 220 are arranged in the stator housing 330. The housing panel 210 closes the opening of the stator housing 330 facing the fluid inlet 302.

[0109] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17 As shown, the flow guide shell 301 includes a first housing 310 and a second housing 320. The first housing 310 includes a first flow guide cylinder 311 and a plurality of first connecting strips 312. The second housing 320 includes a second flow guide cylinder 321 and a plurality of second connecting strips 322. The first flow guide cylinder 311, the second flow guide cylinder 321 and the stator housing 330 are coaxially arranged. One end of the first flow guide cylinder 311 has a fluid inlet 302. The plurality of first connecting strips 312 are connected between the other end of the first flow guide cylinder 311 and the end of the second flow guide cylinder 321 facing the fluid inlet 302. The plurality of second connecting strips 322 are connected between the end of the second flow guide cylinder 321 away from the fluid inlet 302 and the end of the stator housing 330 facing the fluid inlet 302.

[0110] 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;

[0111] The second external magnetic bearing 350 is fixed on the inner wall of the first guide tube 311, and the first external magnetic bearing 360 is fixed on the inner wall of the second guide tube 321.

[0112] like Figure 3 , Figure 6 , Figure 9 , Figure 12 The diagram shows the flow path of blood as it flows through the inside of the blood pump in some embodiments of the present invention. Blood (arrows in the diagram indicate 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, while the rest continues to flow into the second housing 320. After flowing through the second flow channel between the inner wall of the second housing 320 and the rotor assembly 100, the blood flows out of the blood pump through the second fluid outlet 323 between the second connecting bars 322.

[0113] As an optional embodiment of this utility model, such as Figure 17As shown, the first guide tube 311 and multiple first connecting strips 312 are integrated into one unit.

[0114] As an optional embodiment of this utility model, the first connecting strip 312 is welded to the second housing 320.

[0115] As an optional embodiment of this utility model, such as Figure 17 As shown, the second guide tube 321 is integrated with multiple second connecting strips 322.

[0116] As an optional embodiment of this utility model, the second connecting strip 322 is welded to the stator housing 330.

[0117] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the blood pump also includes a second bearing sleeve 351, which is coaxial with the first guide tube 311 and fixedly disposed 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.

[0118] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the inner diameter of the first guide tube 311 gradually increases on the side facing the fluid inlet 302, thereby ensuring the smoothness of the blood flow channel surface inside the shell 300, avoiding dead zones that could cause coagulation, and improving the safety of medical operations.

[0119] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the inner wall of the first guide tube 311 has an annular transition platform 314 extending around the axis. The annular transition platform 314 abuts against the axial side of the first guide tube 311 away from the fluid inlet 302. The inner diameter of the annular transition platform 314 facing the fluid inlet 302 corresponds to the inner diameter of the end of the first guide tube 311 away from the fluid inlet 302. The inner diameter of the annular transition platform 314 gradually increases along the direction away from the fluid inlet 302, thereby ensuring the smoothness of the blood flow channel surface inside the shell 300, avoiding the formation of dead zones that may cause coagulation, and improving the safety of medical operations.

[0120] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10As shown, the blood pump also includes a first bearing sleeve 361, which is coaxial with the second guide tube 321 and fixedly disposed 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.

[0121] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the second guide tube 321 has an annular guide platform 324 at one end facing the fluid inlet 302. The annular guide platform 324 is located between a plurality of first connecting strips 312 at one end facing the fluid inlet 302. The surface of the annular guide platform 324 facing the fluid inlet 302 gradually decreases in height along the direction away from the stator assembly 200 and along the direction away from the axis, thereby forming a smooth slope at one end of the annular guide platform 324 facing the fluid inlet 302, which improves the smoothness of blood diversion.

[0122] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the second annular groove is connected to the end face of the first bearing sleeve 361 facing the fluid inlet 302, and the first external magnetic bearing 360 abuts against the end of the annular guide platform 324 away from the fluid inlet 302.

[0123] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 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 could cause coagulation, and improving the safety of medical operations.

[0124] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the induction coil 370 is fixed in the second guide tube 321.

[0125] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10As shown, the blood pump also includes a coil fixing ring 380. The inner wall of the annular guide platform 324 has a first coil receiving groove. The coil fixing ring 380 and the annular guide platform 324 are coaxially housed in the first coil receiving groove. A second coil receiving groove is formed on the outer wall of the coil fixing ring 380. The induction coil 370 is wound and fixed in the second coil receiving groove.

[0126] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 As shown, the outer wall of the coil fixing ring 380 also has a lead-out groove 381 that communicates with the second coil receiving groove. The bottom of the first coil receiving groove has a lead-out hole 325 that extends through to 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. The lead-out end of the induction coil 370 passes through the lead-out groove 381 and the lead-out hole 325.

[0127] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 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 disposed in the first wire groove 326 and the second wire groove 332.

[0128] As an optional embodiment of this utility model, both the first wire groove 326 and the second wire groove 332 are filled with filler glue, and the lead-out end of the induction coil 370 is fixed in the first wire groove 326 and the second wire groove 332 by the filler glue.

[0129] As an optional embodiment of this utility model, 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), it passes through the conduit 400 out of the human body and is connected to the external control unit.

[0130] As a preferred embodiment of this utility model, such as Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11As shown, a flow channel is formed in the rotor assembly 100. The flow channel has at least one liquid inlet 101 on the rotor assembly 100. The flow channel includes an in-shaft flow channel 151 formed in the central shaft 150. The in-shaft flow channel 151 has a liquid outlet 102 at one end of the central shaft 150 facing the stator assembly 200 (i.e., the end close to the stator assembly 200, hereinafter referred to as the proximal end).

[0131] like Figure 6 , Figure 9 , Figure 12 As shown, some blood flows into the first housing 310 through the fluid inlet 302, and some flows into the hub channel 181 through the inlet 101. After flowing through the first channel, some of the blood flowing into the first housing 310 flows directly out of the blood pump through the first fluid outlet 313, and some continues to flow into the second housing 320. After flowing through the second channel, it flows out of the blood pump through the second fluid outlet 323. The blood flowing into the hub channel 181 continues to flow into the shaft channel 151, and flows out through the outlet 102 and is discharged out of the blood pump through the second fluid outlet 323.

[0132] In this embodiment of the invention, a flow channel is also formed in the rotor assembly 100. The flow channel has a liquid outlet 102 at the proximal end of the central shaft 150, thereby increasing the blood flow rate between the proximal end of the central shaft 150 and the stator assembly 200, avoiding coagulation reaction at the proximal end of the central shaft 150, and further improving the safety of medical operations.

[0133] As another optional embodiment of this utility model, such as Figure 7 , Figure 8 , Figure 10 , Figure 11 As shown, the internal flow channel 151 includes a central hole 1511 and at least one inlet branch hole 1512. The central hole 1511 extends along the axial direction of the central shaft 150 and one end of the central hole 1511 is formed as a liquid outlet 102. One end of the inlet branch hole 1512 communicates with the central hole 1511, and the other end of the inlet branch hole 1512 forms an opening on the surface of the central shaft 150.

[0134] The rotor assembly 100 has at least one flow guide branch hole 190, and the flow guide branch hole 190 corresponds to the position of the inlet branch hole 1512. One end of the flow guide branch hole 190 forms a liquid inlet 101 on the surface of the rotor assembly 100, and the other end of the flow guide branch hole 190 is connected to the corresponding inlet branch hole 1512.

[0135] As an optional embodiment of this utility model, such as Figure 7 , Figure 8 , Figure 10 , Figure 11As shown, the internal flow channel 151 includes at least one first inlet branch hole 1512a and at least one second inlet branch hole 1512b. At least one first guide branch hole 191 is formed in the impeller 110. The position of the first inlet branch hole 1512a corresponds one-to-one with the position of the first guide branch hole 191. The rotor housing 160 has at least one second guide branch hole 192. The position of the second inlet branch hole 1512b corresponds one-to-one with the position of the second guide branch hole 192.

[0136] As an optional embodiment of this utility model, such as Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the flow channel also includes a hub flow channel 181 formed in the impeller hub 180. The end of the hub flow channel 181 facing the stator assembly 200 is connected to the shaft flow channel 151 (specifically, connected to the center hole 1511), and the end of the hub flow channel 181 facing away from the stator assembly 200 is formed as a liquid inlet 101.

[0137] like Figure 9 , Figure 12 As shown, blood flows into the first housing 310 through the fluid inlet 302 (e.g., Figure 9 As shown, when a hub flow channel 181 is formed in the impeller hub 180, some blood flows directly into the central hole 1511 through the liquid inlet 101 at the top of the rotor assembly. After flowing through the first flow channel, some blood flows directly out of the blood pump through the first fluid outlet 313, some continues to flow into the second housing 320, and some flows into the central hole 1511 through the first guide branch hole 191 and the first inlet branch hole 1512a. The blood flowing into the second housing 320 flows out of the blood pump through the second flow channel through the second fluid outlet 323, and another part of the blood flows into the central hole 1511 through the second guide branch hole 192 and the second inlet branch hole 1512b. The blood in the central hole 1511 finally flows out through the liquid outlet 102 and is discharged out of the blood pump through the second fluid outlet 323.

[0138] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 10 , Figure 11 , Figure 17 As shown, the stator assembly 200 includes a housing panel 210 and a plurality of windings 220. The plurality of windings 220 are circumferentially distributed around the axis. The housing panel 210 is located between the rotor assembly 100 and the plurality of windings 220, and the housing panel 210 separates the fluid environment in which the rotor is located from the plurality of windings 220.

[0139] As an optional embodiment of this utility model, such as Figures 14 to 16 As shown, the housing panel 210 includes a positioning plate 212 and a plurality of guide fins 211 located on the positioning plate 212. The plurality of guide fins 211 are distributed around the axis of the rotor assembly 100 and extend toward the side wall of the housing 300.

[0140] In this embodiment of the invention, the housing panel 210 has a plurality of guide fins 211, which extend in a divergent manner, thereby increasing the speed at which blood discharged between the rotor assembly 100 and the housing panel 210 is discharged to the surrounding area, thereby ensuring the blood flow speed near the rotor assembly 100, further reducing the risk of coagulation, and ensuring the safety of medical operations.

[0141] As an optional embodiment of this utility model, such as Figure 14 , Figure 15 As shown, the height of the guide fin 211 along the axial direction of the rotor assembly 100 gradually decreases along the side wall direction toward the housing 300.

[0142] As an optional embodiment of this utility model, such as Figure 15 As shown, the width of the guide fin 211 gradually increases and then gradually decreases along the extension direction of the guide fin 211.

[0143] As an optional embodiment of this utility model, such as Figure 15 As shown, the angle between the guide fin 211 and the radial direction of the rotor assembly 100 gradually increases along the sidewall direction toward the housing 300. That is, the guide fin 211 extends helically around the axis of the rotor assembly 100.

[0144] As an optional embodiment of this utility model, such as Figure 15 As shown, multiple guide fins 211 extend counterclockwise toward the sidewall of the housing 300.

[0145] Alternatively, as another optional embodiment of this utility model, a plurality of guide fins 211 extend clockwise toward the sidewall of the housing 300.

[0146] As an optional embodiment of this utility model, such as Figure 15 As shown, there is a flow guiding space 214 between the liquid outlet 102 of the flow channel and the surface of the stator assembly 200 facing the rotor assembly 100, and a plurality of flow guiding fins 211 surround the flow guiding space 214.

[0147] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10As shown, the positioning plate 212 also has a first annular protrusion 213 around its perimeter. The surface of the first annular protrusion 213 facing away from the guide fin 211 is flush with the surface of the positioning plate 212 facing away from the guide fin 211. A second annular protrusion 331 is also formed on the inner wall of the stator housing 330 facing the fluid inlet 302. The positioning plate 212 is correspondingly disposed in the second annular protrusion 331, and the first annular protrusion 213 abuts against the side of the second annular protrusion 331 facing away from the fluid inlet 302.

[0148] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17 As shown, the stator assembly 200 also includes a circuit board 230, which is fixedly connected to a 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.

[0149] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17 As shown, the stator assembly 200 also includes an insulating ring 240, which is disposed between the plurality of windings 220 to maintain the spacing between the plurality of windings 220 in order to avoid short circuits between the windings 220.

[0150] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 10 , Figure 17 As shown, the housing 300 also includes a shrink housing 340, and the blood pump also includes a conduit 400. The diameter of the conduit 400 is smaller than the diameter of the stator housing 330. The shrink housing 340 is transitionally connected between the conduit 400 and the end of the stator housing 330 away from the fluid inlet 302.

[0151] For ease of understanding, the following provides the assembly process of the blood pump provided in this embodiment of the present invention:

[0152] First, such as Figures 18 to 19 As shown, the modules (first inner magnetic bearing 130, power magnetic ring 201, displacement sensor module 170) corresponding to each chamber in the rotor housing 160 are sequentially installed on the central shaft 150, so that each module contacts the corresponding step (shoulder), and the two housing parts 160a are joined together so that they surround the central shaft 150 and the sides of each module, and the two are glued together to form the rotor housing 160.

[0153] Then, as Figures 19 to 20 As shown, the first end of the central shaft 150 is passed through the second housing 320, so that the rotor housing 160 is accommodated in the second housing 320. The impeller 110, the second inner magnetic bearing 120 (not shown in the figure, which is blocked by the impeller hub 180) and the impeller hub 180 are sequentially installed on the central shaft 150 (at this time, because the impeller 110 and the rotor housing 160 are respectively locked from both sides, the rotor assembly 100 cannot be easily removed from the second housing 320).

[0154] Next, as Figures 20 to 21 As shown, multiple first connecting strips 312 of the first housing 310 are fixedly connected to the second housing 320 to assemble and form the flow guide shell 301;

[0155] Finally, as Figures 21 to 22 As shown, multiple second connecting strips 322 of the second housing 320 are fixedly connected to the stator housing 330 to install the stator assembly 200 to the near end of the aforementioned structure. Then, the shrink housing 340, the conduit 400 and other structures are sequentially installed to the near end of the second housing 320 to complete the installation operation.

[0156] The above are merely specific embodiments of this utility model, but the scope of protection of this utility model is not limited thereto. Those skilled in the art should understand that this utility model includes, but is not limited to, the contents described in the accompanying drawings and the specific embodiments above. Any modifications that do not depart from the functional and structural principles of this utility model will be included within the scope of the claims.

Claims

1. A blood pump, characterized in that, The 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. The rotor assembly includes an impeller, a power magnetic ring, and a central shaft. The blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing and a first outer magnetic bearing that cooperate with each other. The first outer magnetic bearing is disposed on the inner wall of the housing. The impeller, the first inner magnetic bearing, and the power magnetic ring are all fixedly disposed on the central shaft. The rotor assembly can rotate around 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 in the energized state, the rotor assembly can be spaced at a first preset distance from the stator assembly during rotation.

2. The blood pump of claim 1, wherein, The central shaft includes a stage and a power section. The power section is located on the axial side of the stage facing the stator assembly. The diameter of the central shaft in the stage is larger than the diameter of the two axial portions of the central shaft in the stage. The power magnetic ring and the first inner magnetic bearing are both sleeved on the central shaft. The power magnetic ring is located on the power section and corresponds to the end face of the stage. The first inner magnetic bearing is located on the side of the stage away from the stator assembly and corresponds to the end face of the stage.

3. The blood pump of claim 2, wherein, The rotor assembly further includes a rotor housing, which is sleeved on the central shaft and has a bearing housing cavity and a power housing cavity. The first inner magnetic bearing is housed in the bearing housing cavity, and the power magnetic ring is housed in the power housing cavity.

4. The blood pump of claim 3, wherein, The blood pump also includes a second magnetic bearing assembly, which includes a second inner magnetic bearing and a second outer magnetic bearing, with the second outer magnetic bearing disposed on the inner wall of the housing. The rotor assembly further includes an impeller hub, the impeller is sleeved on the central shaft, the impeller is located on the axial side of the rotor housing away from the stator assembly and is fixedly connected to the rotor housing, the impeller hub is fixedly connected to the end of the impeller away from the stator assembly or is integrally formed with the impeller, and the second internal magnetic bearing is disposed inside the impeller hub.

5. The blood pump of claim 4, wherein, The second inner magnetic bearing is sleeved on the central shaft.

6. The blood pump according to claim 4 or 5, characterized in that, The blood pump also includes a displacement sensor module and an induction coil, the induction coil being disposed on the inner wall of the housing; 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 central shaft further includes a first positioning section and a second positioning section. The first positioning section is connected to the axial side of the stage away from the stator assembly, and the second positioning section is connected to the axial side of the first positioning section away from the stator assembly. The diameter of the first positioning section is smaller than the diameter of the stage, and the diameter of the second positioning section is smaller than the diameter of the first positioning section. The first inner magnetic bearing is sleeved on the first positioning section, and the displacement sensor module and the impeller are both sleeved on the second positioning section, with the displacement sensor module corresponding to the end face of the first positioning section.

7. The blood pump according to claim 6, characterized in that, The central shaft also includes a third positioning section, which is connected to the second positioning section on the axial side away from the stator assembly. The diameter of the third positioning section is smaller than that of the second positioning section. The second inner magnetic bearing is sleeved on the third positioning section.

8. The blood pump according to claim 7, characterized in that, The rotor assembly has a flow channel, the flow channel having at least one liquid inlet on the surface of the rotor assembly, the flow channel including an in-shaft flow channel formed in the central shaft, the in-shaft flow channel having a liquid outlet at the end of the central shaft facing the stator assembly.

9. The blood pump according to claim 8, characterized in that, The internal flow channel includes a central hole and at least one inlet branch hole. The central hole extends along the axial direction of the central shaft and one end of the central hole forms the liquid outlet. One end of the inlet branch hole communicates with the central hole, and the other end of the inlet branch hole forms an opening on the surface of the central shaft. The rotor assembly has at least one flow guide branch hole, and the flow guide branch hole corresponds one-to-one with the inlet branch hole. One end of the flow guide branch hole forms the liquid inlet on the surface of the rotor assembly, and the other end of the flow guide branch hole is connected to the corresponding inlet branch hole.

10. The blood pump according to claim 8, characterized in that, The flow passage also includes a hub flow channel formed in the impeller hub, one end of the hub flow channel facing the stator assembly is connected to the shaft flow channel, and the other end of the hub flow channel away from the stator assembly is formed as the liquid inlet.

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