blood pump

Abstract

This invention provides a blood pump, including a rotor assembly, a stator assembly, and a housing. The rotor assembly and stator assembly are axially spaced within the housing along the fluid flow direction. The rotor assembly can rotate around its own axis under the influence of the magnetic field generated by the stator assembly, thereby driving fluid flow. A flow channel is formed in the rotor assembly, having an outlet and an inlet, with the outlet located on the side of the rotor assembly facing the stator assembly. This invention utilizes the flow channel in the rotor assembly to guide blood to the proximal end of the rotor assembly, ensuring the blood flow velocity in the area between the proximal end of the rotor assembly and the stator assembly. This avoids blood clotting caused by a decrease in blood flow velocity within the blood pump, ensuring the smooth rotation of the rotor assembly, and thus guaranteeing the stability of the blood pump operation and the safety of medical procedures.

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, existing blood pumps often exhibit slow blood flow areas within the pump during medical procedures, which can easily lead to thrombus formation and increased rotor resistance, resulting in poor operational stability. Therefore, providing a blood pump capable of stable operation 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. To this end, this invention provides a blood pump that can ensure the flow rate of blood throughout the pump, prevent particle accumulation, and guarantee the stability of the pump's operation.

[0006] To achieve the above objectives, this utility model provides a blood pump, including a rotor assembly, a stator assembly, and a housing. Along the fluid flow direction, the rotor assembly and the stator assembly are axially spaced apart in the housing. The rotor assembly can rotate around its own axis under the action of the magnetic field generated by the stator assembly to drive fluid flow. A flow channel is formed in the rotor assembly, and the flow channel has an outlet and an inlet. The outlet is located on the side of the rotor assembly facing the stator assembly.

[0007] Optionally, the flow channel includes a central flow channel, which is arranged axially along the rotor assembly, and the two ends of the central flow channel are respectively connected to the liquid inlet and the liquid outlet.

[0008] Optionally, the flow passage further includes at least one branch channel, one end of which is formed on the outer surface of the rotor assembly, and the other end of which is connected to the central flow channel.

[0009] Optionally, the flow channel is arranged circumferentially along the axis of the rotor assembly.

[0010] Optionally, the flow divider is located between the blades of the rotor assembly and the stator assembly.

[0011] Optionally, the angle between the axis of the branch channel and the axis of the central channel is 10° to 80°.

[0012] Optionally, the blood pump further includes a flow guide located between the rotor assembly and the stator assembly; the flow guide has a plurality of flow guide fins facing one side of the rotor assembly.

[0013] Optionally, the guide fins are arranged circumferentially around the axis of the rotor assembly, the height of the guide fins along the axis of the rotor assembly gradually decreases along the direction toward the side wall of the housing, the thickness of the guide fins first gradually increases and then gradually decreases along the extension direction of the guide fins, and the angle between each point of the guide fins and the radial direction of the rotor assembly gradually increases along the direction toward the side wall of the housing.

[0014] Optionally, the flow guide is integrally formed with the stator assembly or fixedly installed on the stator assembly.

[0015] Optionally, the outlet of the flow channel has a flow guiding space between it and the surface of the stator assembly facing the rotor assembly, and a plurality of flow guiding fins surround the flow guiding space.

[0016] Optionally, the rotor assembly has a flow guide hole at one end facing the stator assembly, the diameter of the flow guide hole gradually increasing in the direction towards the stator assembly; the flow guide hole is connected to the flow channel, and the portion of the flow guide fin facing the rotor assembly is located in the flow guide hole.

[0017] Optionally, the flow guide includes a positioning plate and a plurality of flow guide fins located on the positioning plate. The positioning plate also has a first annular protrusion around its perimeter. The surface of the first annular protrusion facing away from the flow guide fins is flush with the surface of the positioning plate facing away from the flow guide fins. A second annular protrusion is also formed on the inner wall of the stator housing facing the fluid inlet. The positioning plate is correspondingly disposed in the second annular protrusion, and the first annular protrusion abuts against the side of the second annular protrusion facing away from the fluid inlet.

[0018] Optionally, the liquid inlet of the flow channel is located at one end of the rotor assembly away from the stator assembly, and the flow channel extends along the axis of the rotor assembly.

[0019] Optionally, the flow passage further includes at least one branch channel, one end of which is formed on the outer surface of the rotor assembly, and the other end of which is connected to the central flow channel.

[0020] As an optional embodiment of this utility model, the flow channel is arranged circumferentially along the axis of the rotor assembly.

[0021] In the blood pump provided by this utility model, the rotor assembly can rotate under the action of the magnetic field generated by the stator assembly and drive blood to flow into and out of the housing to achieve the function of driving blood flow. Furthermore, a flow channel is formed in the rotor assembly, and the outlet of the flow channel is located at the proximal end of the rotor assembly. Thus, some of the blood entering the housing can flow into the flow channel and gush out from the fluid outlet at the proximal end of the flow channel, thereby flushing the area between the proximal end of the rotor assembly and the stator assembly and accelerating the blood flow rate in that area.

[0022] In this invention, blood is guided to the proximal end of the rotor assembly through the flow channel in the rotor assembly, ensuring the blood flow velocity in the area between the proximal end of the rotor assembly and the stator assembly. This effectively avoids blood clotting caused by the decrease in blood flow velocity in the blood pump, ensures the smooth rotation of the rotor assembly, and thus ensures the stability of the blood pump operation and the safety of medical procedures. Attached Figure Description

[0023] The present invention will be further described below with reference to the accompanying drawings:

[0024] Figure 1 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0025] Figure 2 yes Figure 1 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0026] Figure 3 yes Figure 1 Schematic diagram of the internal fluid flow path of a blood pump;

[0027] Figure 4 This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0028] Figure 5 yes Figure 4 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0029] Figure 6 yes Figure 4 Schematic diagram of the internal fluid flow path of a blood pump;

[0030] Figure 7This is a cross-sectional structural schematic diagram of the blood pump provided in this embodiment of the utility model;

[0031] Figure 8 yes Figure 7 A schematic diagram of the cross-sectional structure of the rotor assembly of a blood pump;

[0032] Figure 9 yes Figure 7 Schematic diagram of the internal fluid flow path of a blood pump;

[0033] Figure 10 This is a schematic cross-sectional view of the rotor housing in the blood pump provided in this embodiment of the utility model;

[0034] Figure 11 This is a schematic diagram of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0035] Figure 12 This is a front view of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0036] Figure 13 This is a side view of the flow guide panel in the blood pump provided in this embodiment of the utility model;

[0037] Figure 14 This is an exploded view of the blood pump structure provided in this embodiment of the utility model;

[0038] Figures 15 to 19 This is a schematic diagram of the assembly sequence of the blood pump provided in this embodiment of the utility model.

[0039] Explanation of reference numerals in the attached figures

[0040] 100: Rotor assembly; 101: Liquid inlet.

[0041] 102: Liquid outlet; 103: Flow guide hole

[0042] 110: Impeller; 111: Fixed cylinder

[0043] 112: Blade; 120: Second internal magnetic bearing

[0044] 130: First internal magnetic bearing; 150: Central shaft

[0045] L1: Stage L2: Power Section

[0046] L3: First positioning segment L4: Second positioning segment

[0047] L5: Third positioning section 160: Rotor housing

[0048] 160a: Housing component; 161: Bearing housing cavity

[0049] 162: Power receiving cavity; 163: Induction receiving cavity

[0050] 164: First step hole; 165: Through hole

[0051] 166: Second step hole; 167: Third step hole

[0052] 168: Boss section; 170: Displacement sensor module

[0053] 180: Impeller hub; 190: Flow passage

[0054] 191: Central flow channel; 191a: Central bore

[0055] 191b: Hub runner; 192: Split runner

[0056] 1921: First branch channel; 1921a: First inlet branch channel

[0057] 1921b: First diversion channel; 1922: Second diversion channel

[0058] 1922a: Second inlet diversion channel; 1922b: Second diversion channel

[0059] 200: Stator assembly; 201: Power magnetic ring

[0060] 210: Flow guide 211: Flow guide fin

[0061] 212: Positioning plate; 213: First annular protrusion

[0062] 214: Guide space 220: Winding

[0063] 230: Circuit board; 240: Insulating ring

[0064] 300: Housing; 301: Flow guide housing

[0065] 302: Fluid inlet; 310: First casing

[0066] 311: First guide tube; 312: First connecting strip

[0067] 313: First fluid outlet; 314: Annular transition platform

[0068] 320: Second housing; 321: Second air deflector

[0069] 322: Second connecting strip; 323: Second fluid outlet

[0070] 324: Annular guide platform; 325: Outlet hole

[0071] 326: First conductor groove; 330: Stator housing

[0072] 331: Second annular protrusion; 332: Second guide groove

[0073] 340: Shrink housing; 350: Second external magnetic bearing

[0074] 351: Second bearing sleeve; 360: First external magnetic bearing

[0075] 361: First bearing sleeve; 370: Induction coil

[0076] 380: Coil retaining ring; 381: Lead-out slot

[0077] 400: Catheter 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] To reduce the frictional resistance experienced by the rotor, it is necessary to keep the rotor in a completely suspended state, meaning that neither end of the rotor is in contact with the relevant structure of the housing. However, in this case, there is a suspension gap between the downstream end of the rotor and the housing. Some blood will flow into this suspension gap and cannot be quickly discharged from the housing, thus forming a dead zone where blood flows slowly in the suspension gap. Blood is prone to coagulation and thrombus formation in the dead zone, which leads to increased rotor rotation resistance and poor stability of the blood pump operation.

[0082] To solve the above-mentioned technical problems, this utility model provides a blood pump, such as... Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 13As shown, the blood pump includes a rotor assembly 100, a stator assembly 200, and a housing 300. Along the fluid flow direction, the rotor assembly 100 and the stator assembly 200 are axially spaced in the housing 300. 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 fluid flow. A flow passage 190 is formed in the rotor assembly 100. The flow passage 190 has a liquid outlet 102 and a liquid inlet 101, and the liquid outlet 102 is located at the end of the rotor assembly 100 facing the stator assembly 200.

[0083] In the blood pump provided by this utility model, the rotor assembly 100 can rotate under the magnetic field generated by the stator assembly 200 and drive blood to flow into and out of the housing 300, thereby realizing the function of driving blood flow. Furthermore, a flow passage 190 is formed in the rotor assembly 100, and the outlet 102 of the flow passage 190 is located near the end of the rotor assembly 100 (e.g., ...). Figure 2 , Figure 5 , Figure 8 As shown, the proximal end refers to the end of the rotor assembly 100 closest to the stator assembly 200 in the x1 direction, while the distal end is the end of the rotor assembly 100 away from the stator assembly 200 in the x2 direction, thus... Figure 3 , Figure 6 , Figure 9 As shown ( Figure 3 , Figure 6 , Figure 9 This is a schematic diagram of the flow path of blood as it flows through the inside of the blood pump in some embodiments of the present invention (the arrows in the diagram indicate the direction of blood flow). Some of the blood entering the housing 300 can flow into the flow channel 190 and gush out from the fluid outlet at the proximal end of the flow channel 190, thereby flushing the area between the proximal end of the rotor assembly 100 and the stator assembly 200, and accelerating the blood flow rate in that area.

[0084] In this invention, blood is guided to the proximal end of the rotor assembly 100 through the flow channel 190 in the rotor assembly 100, ensuring the blood flow velocity in the area between the proximal end of the rotor assembly 100 and the stator assembly 200. This effectively avoids blood clotting caused by the decrease in blood flow velocity in the blood pump, ensures the smooth rotation of the rotor assembly 100, and thus ensures the stability of the blood pump operation and the safety of medical operations.

[0085] As an optional embodiment of this utility model, the blood pump further includes at least one magnetic bearing assembly, which includes an inner magnetic bearing and an outer magnetic bearing that interact with each other. The outer magnetic bearing is disposed on the inner wall of the housing, and the first inner magnetic bearing is disposed on the rotor assembly 100, thereby ensuring the stability of the axis of the rotor assembly 100 through the repulsive force between the inner and outer magnetic bearings.

[0086] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, 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.

[0087] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As 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 an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 , Figure 13 As shown, one end of the housing 300 has a fluid inlet 302, the rotor assembly 100 is located between the fluid inlet 302 and the stator assembly 200, and 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).

[0089] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the flow channel 190 includes a central flow channel 191, which is arranged along the axial direction of the rotor assembly 100. The two ends of the central flow channel 191 are connected to the liquid inlet 101 and the liquid outlet 102, respectively.

[0090] As an optional embodiment of this utility model, such as Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the flow passage 190 also includes at least one branch channel 192, one end of which is formed on the outer surface of the rotor assembly 100 (and forms a liquid inlet 101 on the surface of the rotor assembly 100), and the other end of which is connected to the central flow passage 191.

[0091] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 7 , Figure 8 As shown, the central flow channel 191 extends through the rotor assembly 100 along the axial direction.

[0092] As an optional embodiment of this utility model, the flow channel 192 is arranged circumferentially along the axis of the rotor assembly 100.

[0093] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the flow channel 192 is located between the blade 112 of the rotor assembly 100 and the stator assembly 200.

[0094] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 7 , Figure 8 As shown, the branch channel 192 gradually moves away from the stator assembly in a direction away from the central channel 191, that is, the branch channel 192 has an angle with the axial direction, so that the blood around the rotor assembly 100 can flow from the branch channel 192 into the central channel 191.

[0095] As an optional embodiment of this utility model, the angle between the axis of the branch channel 192 and the axis of the central channel 191 is 10° to 80°.

[0096] As a preferred embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 14 As shown, the blood pump also includes a flow guide 210, which is located between the rotor assembly 100 and the stator assembly 200; the flow guide 210 has a plurality of flow guide fins 211, which face the rotor assembly 100.

[0097] In this embodiment of the invention, a guide fin 211 is provided at the proximal end of the blood flow path, with multiple fins facing the rotor assembly 100, thereby guiding the blood flowing out of the outlet 102 to flow quickly to the fluid outlet on the side, further ensuring the blood flow speed in the area between the rotor assembly 100 and the stator assembly 200, avoiding blood flow speed reduction and coagulation, and ensuring the smooth rotation of the rotor assembly 100.

[0098] As a preferred embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 14 As shown, the guide fins 211 are arranged circumferentially around the axis of the rotor assembly 100.

[0099] In this embodiment of the invention, multiple guide fins 211 extend outwards in a radiating pattern, thereby guiding the blood flowing out of the outlet 102 to flow rapidly to the surrounding fluid outlets, further ensuring the blood flow velocity in the area between the rotor assembly 100 and the stator assembly 200, preventing blood flow velocity from decreasing and causing coagulation, and ensuring the smooth rotation of the rotor assembly 100.

[0100] As a preferred embodiment of this utility model, such as Figure 11 , Figure 13 As shown, the height of the guide fins 211 along the axis of the rotor assembly 100 gradually decreases along the side wall towards the housing 300. That is, the guide fins 211 are high in the central region and low in the edge region, thereby ensuring that the blood is quickly diverted when it rushes towards the stator assembly 200, avoiding turbulence between the rotor assembly 100 and the stator assembly 200, and ensuring the smooth flow of blood.

[0101] As a preferred embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the rotor assembly 100 also has a flow guide hole 103 at one end facing the stator assembly 200. The diameter of the flow guide hole 103 gradually increases along the direction towards the stator assembly 200. The flow guide hole 103 is connected to the flow passage 190. The part of the flow guide fin 211 facing the fluid inlet 302 is located in the flow guide hole 103.

[0102] In this embodiment of the invention, the top of the guide fin 211 facing the fluid inlet 302 is inserted into the guide hole 103, so that when the blood flows into the guide hole 103, the blood is diverted in advance by the protruding top structure of the guide fin 211, so that the blood is quickly diverted to the area between adjacent guide fins 211, further ensuring the smoothness of blood flow.

[0103] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the guide hole 103 is tapered.

[0104] As an optional embodiment of this utility model, such as Figure 11 , Figure 12 As shown, the thickness of the guide fin 211 gradually increases and then gradually decreases along the extension direction of the guide fin 211.

[0105] As a preferred embodiment of this utility model, such as Figure 11 , Figure 12 As shown, the angle between the guide fins 211 and the radial direction of the rotor assembly 100 gradually increases along the sidewall of the housing 300. That is, the guide fins 211 extend spirally around the axis of the rotor assembly 100, so that the flow channel shape between each pair of adjacent guide fins 211 is spiral, in order to adapt to the flow direction of blood in the rotating flow channel 190, avoid excessive impact on the blood flow, and thus improve the safety of medical operations.

[0106] In this embodiment of the invention, the spiral direction of the guide fins 211 is not specifically limited, as long as it is consistent with the rotation direction of the rotor assembly 100. For example, as an optional implementation of this invention, such as... Figure 11 , Figure 12 As shown, multiple guide fins 211 extend counterclockwise toward the sidewall of the housing 300.

[0107] Alternatively, as another optional embodiment of this utility model, the plurality of guide fins 211 may also extend clockwise toward the sidewall of the housing 300.

[0108] As an optional embodiment of this utility model, the flow guide 210 is integrally formed with the stator assembly 200 or fixedly installed on the stator assembly 200.

[0109] As a preferred embodiment of this utility model, such as Figure 12 As shown, there is a flow guiding space 214 between the outlet 102 of the flow channel 190 and the surface of the stator assembly 200 facing the rotor assembly 100. Multiple flow guiding fins 211 surround the flow guiding space 214. That is, in this embodiment of the present invention, the multiple flow guiding fins 211 do not contact each other in the center of the flow guiding plate, but leave a flow guiding space 214 in the center that allows blood to flow in. This avoids the formation of dead zones in blood flow at the intersection of adjacent flow guiding fins 211, further preventing blood clotting inside the blood pump and improving the safety of medical operations.

[0110] As a preferred embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 14 As shown, the stator assembly 200 includes multiple windings 220, and the rotor assembly 100 is provided with a power magnetic ring 201. The multiple windings 220 are circumferentially distributed around the axis. The multiple windings 220 are used to generate a magnetic field when energized, so as to drive the power magnetic ring 201 to drive the rotor assembly 100 to rotate. The flow guide 210 separates the fluid environment where the rotor is located from the multiple windings 220.

[0111] In this embodiment of the present invention, the power magnetic rings 201 provided on the stator assembly 200 and the rotor assembly 100 are spaced apart along the axial direction. That is, in this embodiment of the present invention, the motor structure formed by the stator assembly 200 and the power magnetic rings 201 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.

[0112] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 , Figure 14 As 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 flow guide 210 closes the opening of the stator housing 330 facing the fluid inlet 302.

[0113] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the flow guide 210 includes a positioning plate 212 and a plurality of flow guide fins 211 located on the positioning plate 212. 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 flow guide fins 211 is flush with the surface of the positioning plate 212 facing away from the flow guide fins 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.

[0114] As an optional embodiment of the present invention, the stator assembly 200 further 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.

[0115] As an optional embodiment of the present invention, the stator assembly 200 further includes an insulating ring 240, which is disposed between multiple windings 220 to maintain the spacing between the multiple windings 220 so as to avoid short circuits between the windings 220.

[0116] As an optional embodiment of the present invention, the housing 300 further includes a shrink housing 340, and the blood pump further 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.

[0117] As an optional embodiment of this utility model, 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.

[0118] 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;

[0119] The first external magnetic bearing 360 is fixed on the inner wall of the first guide tube 311, and the second external magnetic bearing 350 is fixed on the inner wall of the second guide tube 321.

[0120] As an optional embodiment of this utility model, such as Figure 14 As shown, the first guide tube 311 and multiple first connecting strips 312 are integrated into one unit.

[0121] As an optional embodiment of this utility model, the first connecting strip 312 is welded to the second housing 320.

[0122] As an optional embodiment of this utility model, such as Figure 14 As shown, the second guide tube 321 is integrated with multiple second connecting strips 322.

[0123] As an optional embodiment of this utility model, the second connecting strip 322 is welded to the stator housing 330.

[0124] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7As shown, the blood pump also includes a first bearing sleeve 361, 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 first bearing sleeve 361 has a first annular groove extending around the axis, and the first external magnetic bearing 360 is accommodated in the first annular groove.

[0125] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 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.

[0126] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 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 side of the first guide tube 311 away from the fluid inlet 302. The inner diameter of the side 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 surface of the blood flow channel inside the shell 300, avoiding the generation of dead zones that may cause coagulation, and improving the safety of medical operations.

[0127] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the blood pump also includes a second bearing sleeve 351, 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 second bearing sleeve 351 has a second annular groove extending around the axis, and the second external magnetic bearing 350 is accommodated in the second annular groove.

[0128] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 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.

[0129] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the second annular groove is connected to the end face of the second bearing sleeve 351 facing the fluid inlet 302, and the second external magnetic bearing 350 abuts against the end of the annular guide platform 324 away from the fluid inlet 302.

[0130] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the inner diameter of the second bearing sleeve 351 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.

[0131] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As shown, the induction coil 370 is fixed in the second guide tube 321.

[0132] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 As 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.

[0133] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7 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.

[0134] As an optional embodiment of this utility model, such as Figure 1 , Figure 4 , Figure 7As 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.

[0135] 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.

[0136] 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.

[0137] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 7 , Figure 8 As shown, the liquid inlet 101 of the flow channel 190 is located at one end of the rotor assembly 100 away from the stator assembly 200, and the flow channel 190 extends along the axis of the rotor assembly 100.

[0138] like Figure 3 As shown, part of the blood flows into the first housing 310 through the fluid inlet 302, and part flows into the flow channel 190 through the liquid inlet 101. After flowing through the first flow channel, part of the blood flowing into the first housing 310 flows directly out of the blood pump through the first fluid outlet 313, and part continues to flow into the second housing 320. After flowing through the second flow channel, it flows out of the blood pump through the second fluid outlet 323. Finally, the blood flowing into the flow channel 190 flows out through the liquid outlet 102 and is discharged out of the blood pump through the second fluid outlet 323.

[0139] As a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8As shown, the rotor assembly 100 includes an impeller 110, a first inner magnetic bearing 130, and a second inner magnetic bearing 120. Blades 112 are located on the impeller 110. The impeller 110, the first inner magnetic bearing 130, the second inner magnetic bearing 120, and the power magnetic ring 201 are fixedly connected to each other. The inner wall of the housing 300 is also provided with a first outer magnetic bearing 360 and a second outer magnetic bearing 350. The first outer magnetic bearing 360 is sleeved on the outside of the first inner magnetic bearing 130, and the second outer magnetic bearing 350 is sleeved on the outside of the second inner magnetic bearing 120. There is a radial repulsive force between the first outer magnetic bearing 360 and the first inner magnetic bearing 130, and there is a radial repulsive force between the second outer magnetic bearing 350 and the second inner magnetic bearing 120.

[0140] In this embodiment of the invention, the rotor assembly 100 achieves radial positioning through the radial repulsion between the first inner magnetic bearing 130 and the first outer magnetic bearing 360 and the radial repulsion between the second inner magnetic bearing 120 and the second outer magnetic bearing 350. Compared with the traditional positioning scheme through mechanical bearings, this can effectively reduce the rotor rotation resistance and improve the heating of the blood pump, thereby ensuring the safety of medical operations.

[0141] As a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the rotor assembly 100 also includes a central shaft 150, and the impeller 110, the first inner magnetic bearing 130, the second inner magnetic bearing 120 and the power magnetic ring 201 are all fixedly mounted on the central shaft 150.

[0142] In this embodiment of the present invention, the impeller 110, the first internal magnetic bearing 130, the second internal magnetic bearing 120, and other components in the rotor assembly 100 are all fixed on the central shaft 150, which ensures the stability of the relative positions of the components, improves the overall structural strength of the rotor assembly 100, reduces the amplitude of deformation of the rotor assembly 100 under the action of the flow field during rotation, thereby improving the stability of the rotor assembly 100's position inside the housing 300, ensuring the stability of the blood pump's operation, and reducing the friction and wear between the components on the rotor assembly 100, thus extending the service life of the blood pump.

[0143] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8As 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.

[0144] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the impeller 110 includes a pair of blades 112.

[0145] As an optional embodiment of this utility model, such as Figure 5 , Figure 8 As shown, the flow channel 190 includes a set of first branch channels 1921. One end of the first branch channel 1921 is connected to the central flow channel 191, and the other end of the first branch channel 1921 has a liquid inlet 101 on the surface of the fixed cylinder 111.

[0146] As an optional embodiment of this utility model, such as Figure 5 , Figure 8 As shown, the first diversion channel 1921 includes a first inflow diversion channel 1921a located in the central shaft 150 and a first flow guiding diversion channel 1921b located in the fixed cylinder 111. One end of the first inflow diversion channel 1921a is connected to the central channel 191, and the other end is connected to one end of the first flow guiding diversion channel 1921b. The other end of the first flow guiding diversion channel 1921b has a liquid inlet 101 on the surface of the fixed cylinder 111 of the impeller 110.

[0147] As a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the central shaft 150 includes a stage L1 and a power section L2. The power section L2 is located on the side of the stage L1 away from the fluid inlet 302. The diameter of the central shaft 150 in the stage L1 is larger than the diameter of the two sides of the central shaft 150 in the stage L1. The power magnetic ring 201 is located on the power section L2. The second inner magnetic bearing 120 is located on the side of the stage L1 away from the power section L2.

[0148] In this embodiment of the invention, the central shaft 150 has a stepped platform 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 platform L1 and the power section L2. The axial position of the second inner magnetic bearing 120 can also be positioned using the step between the stepped platform L1 and the part of the central shaft 150 located on the other side of the stepped platform L1. This further ensures the stability of the relative positional relationship between the components and improves the structural strength of the rotor assembly 100.

[0149] To further improve the structural strength of the rotor assembly 100, as a preferred embodiment of this utility model, such as Figure 10 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 second inner magnetic bearing 120 is housed in the bearing housing 161, and the power magnetic ring 201 is housed in the power housing 162.

[0150] In this embodiment of the invention, the second inner magnetic bearing 120 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 second inner magnetic bearing 120 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 second inner magnetic bearing 120 and the power magnetic ring 201, preventing them from directly contacting the liquid environment. This, in turn, prevents the components mounted on the central shaft 150 from being corroded, thus ensuring the service life of the blood pump.

[0151] As an optional embodiment of this utility model, such as Figure 5 , Figure 8 As shown, the flow channel 190 includes a set of second branch channels 1922. One end of the second branch channel 1922 is connected to the central flow channel 191, and the other end of the second branch channel 1922 has a liquid inlet 101 on the surface of the rotor housing 160.

[0152] As an optional embodiment of this utility model, such as Figure 5 , Figure 8 As shown, the second diversion channel 1922 includes a second inflow diversion channel 1922a located in the central shaft 150 and a second flow guide diversion channel 1922b located in the rotor housing 160. One end of the second inflow diversion channel 1922a is connected to the central flow channel 191, and the other end is connected to one end of the second flow guide diversion channel 1922b. The other end of the second flow guide diversion channel 1922b has a liquid inlet 101 on the surface of the rotor housing 160.

[0153] For ease of understanding, such as Figure 6 , Figure 9 The diagram shows the internal fluid flow path of the blood pump when the rotor assembly has both a first flow channel 1921 and a second flow channel 1922. Blood flows into the first housing 310 from the fluid inlet 302 (e.g., Figure 9 As shown, when a hub flow channel 191b is formed in the impeller hub 180, some blood flows directly into the central flow channel 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 flow channel 191 through the first branch channel 1921. The blood flowing into the second housing 320 flows out of the blood pump through the second fluid outlet 323 after flowing through the second flow channel, and another part of the blood flows into the central flow channel 191 through the second branch channel 1922. The blood in the central flow channel 191 finally flows out through the liquid outlet 102 and is discharged out of the blood pump through the second fluid outlet 323.

[0154] 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 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.

[0155] As an optional embodiment of this utility model, the impeller 110 is bonded to the rotor housing 160.

[0156] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the rotor assembly 100 also includes an impeller hub 180, an impeller 110 is sleeved on one end of the central shaft 150 facing the fluid inlet 302, and the impeller 110 is fixedly connected to the rotor housing 160. The impeller hub 180 is fixedly connected to the end of the impeller 110 facing the fluid inlet 302, and the first internal magnetic bearing 130 is disposed inside the impeller hub 180.

[0157] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 7 , Figure 8 As shown, the central flow channel 191 includes a central hole 191a and a hub flow channel 191b located inside the impeller hub 180. The central flow channel 191 passes through the central shaft 150 along the axial direction, and the hub flow channel 191b passes through the impeller hub 180 along the axial direction.

[0158] 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.

[0159] As an optional embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 7 , Figure 8 As shown, the first internal magnetic bearing 130 is mounted on the central shaft 150.

[0160] As a preferred embodiment of this utility model, such as Figure 1 , Figure 2 , Figure 4 , Figure 5 , Figure 7 , Figure 8 As shown, the rotor assembly 100 also includes a displacement sensor module 170, and an induction coil 370 is also provided on the inner wall of the housing 300. The induction coil 370 is arranged around the rotor assembly 100, and the axial position of the induction coil 370 partially coincides with the axial position of the displacement sensor module 170.

[0161] 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.

[0162] 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 As shown, the central shaft 150 also includes a first positioning section L3 and a second positioning section L4. The second inner magnetic bearing 120 is sleeved on the first positioning section L3. The second positioning section L4 is connected to one side of the first positioning section L3 away from the stage L1. The displacement sensor module 170 and the impeller 110 are both sleeved on the second positioning section L4, and the position of the displacement sensor module 170 corresponds to the position of the connection between the first positioning section L3 and the second positioning section L4. The diameter of the second positioning section L4 is smaller than the diameter of the first positioning section L3.

[0163] 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 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.

[0164] As an optional embodiment of this utility model, such as Figure 10 As shown, the rotor housing 160 also has a sensing cavity 163, in which the displacement sensor module 170 is housed.

[0165] As an optional embodiment of this utility model, such as Figure 10As 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.

[0166] As an optional embodiment of this utility model, such as Figure 14 , Figure 15 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 second inner magnetic bearing 120 and the two sides of the power magnetic ring 201, and the mating surfaces of the housing parts 160a are bonded together.

[0167] As an optional embodiment of this utility model, such as Figure 2 , Figure 8 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 first inner magnetic bearing 130 is sleeved on the third positioning section L5.

[0168] For ease of understanding, the following provides the assembly process of the blood pump provided in this embodiment of the present invention:

[0169] First, such as Figures 15 to 16 As shown, the modules (second inner magnetic bearing 120, 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.

[0170] Then, as Figures 16 to 17As 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 first internal magnetic bearing 130 (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).

[0171] Next, as Figures 17 to 18 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;

[0172] Finally, as Figures 18 to 19 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.

[0173] In the blood pump provided in this embodiment of the present invention, the rotor assembly 100 is located between the fluid inlet 302 and the stator assembly 200, and can rotate under the action of the magnetic field generated by the stator assembly 200. Through the blades 112, blood flows from the fluid inlet 302 toward the stator assembly 200 into the housing 300 and out through the fluid outlet, thereby achieving the function of driving blood flow. Furthermore, a flow channel 190 is formed in the rotor assembly 100, and the outlet 102 of the flow channel 190 is located near the proximal end of the rotor assembly 100. This allows some of the blood entering the housing 300 to flow into the flow channel 190 and gush out through the fluid outlet near the proximal end of the flow channel 190, thereby flushing the area between the proximal end of the rotor assembly 100 and the stator assembly 200, accelerating the blood flow rate in that area.

[0174] This embodiment of the invention utilizes the flow channel 190 in the rotor assembly 100 to guide blood to the proximal end of the rotor assembly 100, ensuring the blood flow velocity in the area between the proximal end of the rotor assembly 100 and the stator assembly 200. This effectively avoids blood clotting caused by a decrease in blood flow velocity in the blood pump, ensuring the smooth rotation of the rotor assembly 100, thereby ensuring the stability of the blood pump operation and the safety of medical procedures.

[0175] 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 device includes a rotor assembly, a stator assembly, and a housing. Along the fluid flow direction, the rotor assembly and the stator assembly are axially spaced apart in the housing. The rotor assembly can rotate around its own axis under the action of the magnetic field generated by the stator assembly to drive fluid flow. A flow channel is formed in the rotor assembly. The flow channel has a liquid outlet and a liquid inlet, and the liquid outlet is located on the side of the rotor assembly facing the stator assembly.

2. The blood pump of claim 1, wherein, The flow channel includes a central flow channel, which is arranged axially along the rotor assembly, and the two ends of the central flow channel are respectively connected to the liquid inlet and the liquid outlet.

3. The blood pump of claim 2, wherein, The flow passage further includes at least one branch channel, one end of which is formed on the outer surface of the rotor assembly, and the other end of which is connected to the central flow channel.

4. The blood pump of claim 3, wherein, The flow channel is arranged circumferentially along the axis of the rotor assembly.

5. The blood pump of claim 3, wherein, The flow channel is located between the blades of the rotor assembly and the stator assembly.

6. The blood pump of claim 3, wherein, The angle between the axis of the branch channel and the axis of the central channel is 10° to 80°.

7. The blood pump of claim 1, wherein, The blood pump also includes a flow guide located between the rotor assembly and the stator assembly; the flow guide has a plurality of flow guide fins facing one side of the rotor assembly.

8. The blood pump of claim 7, wherein, The guide fins are arranged circumferentially around the axis of the rotor assembly. The height of the guide fins along the axis of the rotor assembly gradually decreases in the direction toward the side wall of the housing. The thickness of the guide fins first gradually increases and then gradually decreases in the extension direction of the guide fins. The angle between each point of the guide fins and the radial direction of the rotor assembly gradually increases in the direction toward the side wall of the housing.

9. The blood pump of claim 7 or 8, characterized in that The flow guide is integrally formed with the stator assembly or fixedly installed on the stator assembly.

10. The blood pump of claim 8, wherein, The rotor assembly also has a flow guide hole at one end facing the stator assembly, and the diameter of the flow guide hole gradually increases along the direction towards the stator assembly; the flow guide hole is connected to the flow channel, and the portion of the flow guide fin facing the rotor assembly is located in the flow guide hole.

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