Blood pump

Abstract

The invention provides a blood pump which comprises a rotor assembly, a stator assembly and a shell, the rotor assembly and the stator assembly are axially arranged in the shell in a spaced mode in the fluid flowing direction, and the rotor assembly can rotate around the axis of the rotor assembly under the action of a magnetic field generated by the stator assembly so as to drive fluid to flow through the rotor assembly. An overflowing channel is formed in the rotor assembly, the overflowing channel is provided with a liquid outlet and a liquid inlet, and the liquid outlet is located in the side, facing the stator assembly, of the rotor assembly. Blood is guided to the near end of the rotor assembly through the flow passing channel in the rotor assembly, the blood flowing speed in the area between the near end of the rotor assembly and the stator assembly is guaranteed, the blood coagulation phenomenon caused by the fact that the flowing speed of blood in the blood pump is reduced can be avoided, and the rotating stability of the rotor assembly is guaranteed; therefore, the operation stability of the blood pump and the safety of medical operation are ensured.

Description

Technical Field

[0001] The present invention relates to the field of medical supplies, in particular to a blood pump. Background Art

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

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

[0004] However, existing blood pumps often experience slow blood flow areas during medical procedures, which can lead to thrombosis. This increases the rotor's rotational resistance and results in poor operational stability. Therefore, providing a stable blood pump has become a pressing technical challenge in the field. Summary of the Invention

[0005] The present invention aims to solve one of the technical problems in the related art to a certain extent. To this end, the present invention provides a blood pump that can ensure the blood flow rate at various locations inside the blood pump, avoid particle accumulation, and ensure the stability of the blood pump operation.

[0006] To achieve the above-mentioned objectives, the present invention provides a blood pump, comprising a rotor assembly, a stator assembly and a housing. The rotor assembly and the stator assembly are axially spaced apart in the housing along the direction of fluid flow. The rotor assembly is capable of rotating around its own axis under the action of the magnetic field generated by the stator assembly to drive fluid flow through the rotor assembly. A flow channel is formed in the rotor assembly, the flow channel having a liquid outlet and a liquid inlet, and the liquid outlet is located on the side of the rotor assembly facing the stator assembly.

[0007] Optionally, the flow passage includes a central flow channel, the central flow channel is arranged axially along the rotor assembly, and 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 the branch channel is formed on the outer surface of the rotor assembly, and the other end of the branch channel is connected to the central channel.

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

[0010] Optionally, the flow diverter 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 member, which is located between the rotor assembly and the stator assembly; the flow guide member has a plurality of flow guide fins, and the plurality of flow guide fins face one side of the rotor assembly.

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

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

[0015] Optionally, a guide space is provided between the liquid outlet of the flow channel and the surface of the stator assembly facing the rotor assembly, and a plurality of guide fins surround the guide space.

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

[0017] Optionally, the guide member includes a positioning plate and a plurality of guide fins located on the positioning plate, and the positioning plate is also provided with a first annular protrusion around it, and the surface of the first annular protrusion facing away from the guide fins is flush with the surface of the positioning plate facing away from the guide fins; a second annular protrusion is also formed on the inner wall of the stator housing facing the fluid inlet end, and the positioning plate is correspondingly arranged 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 an 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 the branch channel is formed on the outer surface of the rotor assembly, and the other end of the branch channel is communicated with the central channel.

[0020] As an optional embodiment of the present invention, the flow divider is arranged along the circumferential direction of the axis of the rotor assembly.

[0021] In the blood pump provided by the present invention, 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 shell, so as to realize the function of driving blood flow. In addition, an overflow channel is formed in the rotor assembly, and the liquid outlet of the overflow channel is located at the proximal end of the rotor assembly, so that part of the blood entering the shell can flow into the overflow channel and flow out from the fluid outlet at the proximal end of the overflow channel, thereby flushing the area between the proximal end of the rotor assembly and the stator assembly, thereby accelerating the blood flow rate in this area.

[0022] The present invention utilizes the flow channel in the rotor assembly to guide blood to the proximal end of the rotor assembly, thereby ensuring the blood flow velocity in the area between the proximal end of the rotor assembly and the stator assembly. This can effectively avoid coagulation caused by the reduced blood flow velocity in the blood pump, ensure the smooth rotation of the rotor assembly, and further ensure the stability of the blood pump operation and the safety of medical operations. BRIEF DESCRIPTION OF THE DRAWINGS

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

[0024] Figure 1 is a schematic cross-sectional structural diagram of a blood pump provided by an embodiment of the present invention;

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

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

[0027] Figure 4 is a schematic cross-sectional structural diagram of a blood pump provided by an embodiment of the present invention;

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

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

[0030] Figure 7 is a schematic cross-sectional structural diagram of a blood pump provided by an embodiment of the present invention;

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

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

[0033] Figure 10 is a schematic cross-sectional structural diagram of a rotor housing in a blood pump provided by an embodiment of the present invention;

[0034] Figure 11 This is a schematic structural diagram of a flow guide panel in a blood pump provided by an embodiment of the present invention;

[0035] Figure 12 is a front view of a guide panel in a blood pump provided by an embodiment of the present invention;

[0036] Figure 13 is a side view of a guide panel in a blood pump provided by an embodiment of the present invention;

[0037] Figure 14 is a schematic diagram of an exploded structure of a blood pump provided by an embodiment of the present invention;

[0038] Figures 15 to 19 1 is a schematic diagram of the assembly sequence of a blood pump provided by an embodiment of the present invention.

[0039] Description of Reference Numerals

[0040] 100: Rotor assembly 101: Liquid inlet

[0041] 102: Liquid outlet 103: Diversion hole

[0042] 110: Impeller 111: Fixed cylinder

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

[0044] 130: First internal magnetic bearing 150: Central axis

[0045] L1: Platform stage L2: Power stage

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

[0047] L5: third positioning section 160: rotor housing

[0048] 160a: Housing body 161: Bearing accommodating cavity

[0049] 162: Power chamber 163: Induction chamber

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

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

[0052] 168: Boss part 170: Displacement sensor module

[0053] 180: Impeller hub 190: Flow channel

[0054] 191: Central channel 191a: Central hole

[0055] 191b: Hub runner 192: Diverter 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 diversion channel

[0059] 200: stator assembly 201: power magnetic ring

[0060] 210: guide piece 211: guide fin

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

[0062] 214: guide space 220: winding

[0063] 230: Circuit board 240: Insulation ring

[0064] 300: Shell 301: Guide shell

[0065] 302: Fluid inlet 310: First housing

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

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

[0068] 320: Second housing 321: Second guide tube

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

[0070] 324: Annular guide platform 325: Lead-out hole

[0071] 326: First conductor slot 330: Stator housing

[0072] 331: Second annular protrusion 332: Second wire 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 fixing ring 381: Lead-out groove

[0077] 400: Catheter DETAILED DESCRIPTION

[0078] The following describes embodiments of the present invention in detail, examples of which are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described in the embodiments are intended to explain the present invention and are not to be construed as limiting the present invention.

[0079] References in this specification to "one embodiment," "an example," or "an example" mean that a particular feature, structure, or characteristic described in connection with the embodiment itself can be included in at least one embodiment disclosed herein. The appearances of the phrase "in one embodiment" in various places in the specification are not necessarily all referring to the same embodiment.

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

[0081] In order to reduce the frictional resistance encountered by the rotor, the rotor needs to be in a completely suspended state, that is, the front and rear ends of the rotor are not in contact with the relevant structures of the shell. However, in this case, there is a suspension gap between the downstream end of the rotor and the shell. Some blood will flow into this suspension gap and cannot be quickly discharged from the shell, thereby forming a dead zone in the suspension gap where blood flows slowly. Blood is prone to coagulation and formation of thrombus in the dead zone, which increases the rotor rotation resistance and poor stability of the blood pump operation.

[0082] In order to solve the above technical problems, the present invention 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 direction of fluid flow, the rotor assembly 100 and the stator assembly 200 are axially spaced apart 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 the fluid flow through the rotor assembly 100. A flow channel 190 is formed in the rotor assembly 100. The flow channel 190 has a liquid outlet 102 and a liquid inlet 101, and the liquid outlet 102 is located at one end of the rotor assembly 100 facing the stator assembly 200.

[0083] In the blood pump provided by the present invention, the rotor assembly 100 can rotate under the action of the magnetic field generated by the stator assembly 200 and drive blood to flow into and out of the housing 300 to achieve the function of driving blood flow. In addition, a flow channel 190 is formed in the rotor assembly 100, and the liquid outlet 102 of the flow channel 190 is located at the proximal end of the rotor assembly 100 (such as Figure 2 、 Figure 5 、 Figure 8 As shown, the proximal end refers to the end of the rotor assembly 100 close to the stator assembly 200 in the x1 direction, and the distal end refers to the end of the rotor assembly 100 away from the stator assembly 200 in the x2 direction). 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 interior of a blood pump in some embodiments of the present invention, where arrows in the figure indicate the direction of blood flow. Part of the blood entering the housing 300 can flow into the flow channel 190 and flow 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, thereby accelerating the blood flow rate in this area.

[0084] In the present invention, the flow channel 190 in the rotor assembly 100 is used to guide blood to the proximal end of the rotor assembly 100, thereby ensuring the blood flow speed in the area between the proximal end of the rotor assembly 100 and the stator assembly 200. This can effectively avoid coagulation caused by the reduction of blood flow speed in the blood pump, ensure the smooth rotation of the rotor assembly 100, and further ensure the stability of the blood pump operation and the safety of medical operations.

[0085] As an optional embodiment of the present invention, the blood pump also 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 arranged on the inner wall of the shell, and the first inner magnetic bearing is arranged 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 the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the blood pump also includes a first magnetic bearing assembly, which includes a first inner magnetic bearing 130 and a first outer magnetic bearing 360 that interact with each other. The first outer magnetic bearing 360 is arranged on the inner wall of the shell 300, and the first inner magnetic bearing 130 is arranged on the rotor assembly 100.

[0087] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the blood pump also includes a second magnetic bearing assembly, which includes a second inner magnetic bearing 120 and a second outer magnetic bearing 350 that interact with each other. The second outer magnetic bearing 350 is arranged on the inner wall of the shell 300, and the second inner magnetic bearing 120 is arranged on the rotor assembly 100.

[0088] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 、 Figure 13 As shown, the housing 300 has a fluid inlet 302 at one end, 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 (eg, a first fluid outlet 313 and a second fluid outlet 323 ).

[0089] As an optional embodiment of the present invention, 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 axially along the rotor assembly 100 , and two ends of the central flow channel 191 are respectively connected to the liquid inlet 101 and the liquid outlet 102 .

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

[0091] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 7 、 Figure 8 As shown, the central flow channel 191 penetrates the rotor assembly 100 along the axial direction.

[0092] As an optional embodiment of the present invention, the flow divider 192 is arranged along the circumferential direction of the axis of the rotor assembly 100 .

[0093] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the flow diverter 192 is located between the blades 112 of the rotor assembly 100 and the stator assembly 200 .

[0094] As an optional embodiment of the present invention, 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 flow channel 191 , that is, there is an angle between the branch channel 192 and the axial direction, so that blood around the rotor assembly 100 flows from the branch channel 192 into the central flow channel 191 .

[0095] As an optional embodiment of the present invention, 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 the present invention, Figure 1 、 Figure 4 、 Figure 7 、 Figure 14 As shown, the blood pump further 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 one side of the rotor assembly 100 .

[0097] In an embodiment of the present invention, a guide fin 211 is further provided at the proximal end of the blood flow path, with multiple guide fins 211 facing one side of the rotor assembly 100, thereby guiding the blood flowing out of the liquid outlet 102 to flow quickly toward 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 the reduction of blood flow speed and the generation of coagulation, and ensuring the smooth rotation of the rotor assembly 100.

[0098] As a preferred embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 、 Figure 14 As shown, the guide fins 211 are circumferentially arranged around the axis of the rotor assembly 100 .

[0099] In an embodiment of the present invention, a plurality of guide fins 211 are distributed and extend in a divergent manner in all directions, thereby guiding the blood flowing out of the liquid outlet 102 to flow quickly to the fluid outlets in the surrounding areas, further ensuring the blood flow speed in the area between the rotor assembly 100 and the stator assembly 200, avoiding the blood flow rate reduction and coagulation, and ensuring the smooth rotation of the rotor assembly 100.

[0100] As a preferred embodiment of the present invention, 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 direction toward the housing 300, that is, the guide fins 211 are high in the central area and low in the edge area, thereby ensuring that the blood is quickly diverted when the blood flows toward the stator assembly 200, avoiding turbulence between the rotor assembly 100 and the stator assembly 200, and ensuring the smoothness of blood flow.

[0101] As a preferred embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the rotor assembly 100 further has a guide hole 103 at one end facing the stator assembly 200 . The diameter of the guide hole 103 gradually increases in the direction toward the stator assembly 200 . The guide hole 103 is connected to the flow channel 190 . The guide fin 211 is partially located in the guide hole 103 on the side facing the fluid inlet 302 .

[0102] In an embodiment of the present invention, the top of the guide fin 211 is inserted into the guide hole 103 toward the fluid inlet 302, so that when the blood flows into the guide hole 103, the blood is pre-diverted through 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 the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the guide hole 103 is conical in shape.

[0104] As an optional embodiment of the present invention, 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 the present invention, Figure 11 、 Figure 12As shown, the angle between each guide fin 211 and the radial direction of the rotor assembly 100 gradually increases toward 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 path between each pair of adjacent guide fins 211 is spiral in shape. This adapts to the flow direction of blood in the rotating flow channel 190, avoids excessive impact on the blood flow, and thus improves the safety of medical procedures.

[0106] The embodiment of the present invention does not specifically limit the spiral direction of the guide fin 211, and it can be consistent with the rotation direction of the rotor assembly 100. For example, as an optional embodiment of the present invention, Figure 11 、 Figure 12 As shown, the plurality of guide fins 211 extend in a counterclockwise direction toward the side wall of the housing 300 .

[0107] Alternatively, as another optional embodiment of the present invention, the plurality of guide fins 211 may also extend in a clockwise direction toward the side wall of the housing 300 .

[0108] As an optional embodiment of the present invention, 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 the present invention, Figure 12 As shown, a guide space 214 is provided between the liquid outlet 102 of the flow channel 190 and the surface of the stator assembly 200 facing the rotor assembly 100, and a plurality of guide fins 211 surround the guide space 214. That is, in an embodiment of the present invention, the plurality of guide fins 211 do not touch each other in the center of the guide plate, but leave a guide space 214 in the center for blood to flow in, thereby avoiding the generation of a blood flow dead zone at the intersection of adjacent guide fins 211, further preventing blood coagulation inside the blood pump, and improving the safety of medical operations.

[0110] As a preferred embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 、 Figure 14 As shown, the stator assembly 200 includes a plurality of windings 220, and a power magnetic ring 201 is provided on the rotor assembly 100. The plurality of windings 220 are circumferentially distributed around the axis. The plurality of windings 220 are used to generate a magnetic field when energized to drive the power magnetic ring 201 to drive the rotor assembly 100 to rotate. The flow guide 210 separates the fluid environment in which the rotor is located from the plurality of windings 220.

[0111] In an embodiment of the present invention, the stator assembly 200 and the power magnetic ring 201 provided on the rotor assembly 100 are arranged at intervals along the axial direction, that is, the motor structure formed by the stator assembly 200 and the power magnetic ring 201 in the embodiment of the present invention 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 motor transmission efficiency and improve the blood transfusion capacity of the blood pump.

[0112] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 、 Figure 14 As shown, the shell 300 includes a flow guide shell 301 and a stator shell 330. The flow guide shell 301 and the stator shell 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 shell 330. The flow guide member 210 closes the opening of the stator shell 330 on the side facing the fluid inlet 302.

[0113] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the guide member 210 includes a positioning plate 212 and a plurality of guide fins 211 located on the positioning plate 212. The positioning plate 212 is also provided with a first annular protrusion 213 around it. The surface of the first annular protrusion 213 facing away from the guide fins 211 is flush with the surface of the positioning plate 212 facing away from the 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 arranged 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 the plurality of windings 220 . The circuit board 230 is used to supply power to the plurality of windings 220 so that the windings 220 generate a magnetic field.

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

[0116] As an optional embodiment of the present invention, the housing 300 further includes a contraction housing 340, and the blood pump further includes a conduit 400, the diameter of the conduit 400 being smaller than the diameter of the stator housing 330, and the contraction housing 340 being transitionally connected between the conduit 400 and the end of the stator housing 330 facing away from the fluid inlet 302.

[0117] As an optional embodiment of the present invention, the guide housing 301 includes a first housing 310 and a second housing 320. The first housing 310 includes a first guide tube 311 and a plurality of first connecting bars 312. The second housing 320 includes a second guide tube 321 and a plurality of second connecting bars 322. The first guide tube 311, the second guide tube 321, and the stator housing 330 are coaxially arranged. One end of the first guide tube 311 has a fluid inlet 302. The plurality of first connecting bars 312 are connected between the other end of the first guide tube 311 and an end of the second guide tube 321 facing the fluid inlet 302. The plurality of second connecting bars 322 are connected between an end of the second guide tube 321 facing away from the fluid inlet 302 and an end of the stator housing 330 facing the fluid inlet 302.

[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 the present invention, Figure 14 As shown, the first guide tube 311 and the plurality of first connecting bars 312 are formed as one body.

[0121] As an optional embodiment of the present invention, the first connecting bar 312 is connected to the second housing 320 by welding.

[0122] As an optional embodiment of the present invention, Figure 14 As shown, the second guide tube 321 and the plurality of second connecting bars 322 are formed as one body.

[0123] As an optional embodiment of the present invention, the second connecting bar 322 is welded to the stator housing 330 .

[0124] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the blood pump also includes a first bearing sleeve 361, which is coaxial with the first guide tube 311 and fixedly arranged on the inner wall of the first guide tube 311. The outer wall of the 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 the present invention, Figure 1 、 Figure 4 、 Figure 7As 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 housing 300, avoiding the formation of dead zones that may cause coagulation, and improving the safety of medical operations.

[0126] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the inner wall of the first guide tube 311 is provided with an annular transition platform 314 extending around the axis, and 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 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 in the direction away from the fluid inlet 302, thereby ensuring the smoothness of the blood flow path surface inside the shell 300, avoiding the formation of dead zones that cause coagulation, and improving the safety of medical operations.

[0127] As an optional embodiment of the present invention, 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 arranged 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 the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the end of the second guide tube 321 facing the fluid inlet 302 has an annular guide platform 324, and the end of the annular guide platform 324 facing the fluid inlet 302 is located between the multiple first connecting bars 312, and the height of the surface of the annular guide platform 324 facing the fluid inlet 302 gradually decreases along the direction away from the stator assembly 200, thereby forming a smooth inclined surface at the end of the annular guide platform 324 facing the fluid inlet 302, thereby improving the smoothness of blood diversion.

[0129] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the second annular groove is connected to the end surface of the second bearing sleeve 351 facing the fluid inlet 302 , and the second external magnetic bearing 350 is in contact with the end of the annular guide platform 324 facing away from the fluid inlet 302 .

[0130] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7As 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 cause coagulation, and improving the safety of medical operations.

[0131] As an optional embodiment of the present invention, 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 the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the blood pump also includes a coil fixing ring 380, and a first coil accommodating groove is provided on the inner wall of the annular guide platform 324. The coil fixing ring 380 and the annular guide platform 324 are coaxially accommodated in the first coil accommodating groove; a second coil accommodating groove is formed on the outer wall of the coil fixing ring 380, and the induction coil 370 is wound and fixed in the second coil accommodating groove.

[0133] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the outer wall of the coil fixing ring 380 also has a lead-out groove 381 connected to the second coil accommodating groove, and the bottom of the first coil accommodating groove has a lead-out hole 325 that passes through the outer wall of the second guide tube 321. The position of the lead-out hole 325 corresponds to the position of the lead-out groove 381, and the lead-out end of the induction coil 370 passes through the lead-out groove 381 and the lead-out hole 325.

[0134] As an optional embodiment of the present invention, Figure 1 、 Figure 4 、 Figure 7 As shown, the outer wall of the second housing 320 has a first wire groove 326 extending along the axial direction, and the outer wall of the stator housing 330 has a second wire groove 332 extending along the axial direction. One end of the first wire groove 326 is connected to the lead-out hole 325, and the other end of the first wire groove 326 is connected to the second wire groove 332. The lead-out end of the induction coil 370 is set in the first wire groove 326 and the second wire groove 332.

[0135] As an optional embodiment of the present invention, the first wire groove 326 and the second wire groove 332 are both filled with filling glue, and the lead end of the induction coil 370 is fixed in the first wire groove 326 and the second wire groove 332 by the filling glue.

[0136] As an optional embodiment of the present invention, the lead end of the induction coil 370 extends through the shrink housing 340 into the conduit 400, and together with the power supply line of the stator assembly 200 (connected to the circuit board 230), passes through the conduit 400 out of the human body and is connected to an external control machine.

[0137] As an optional embodiment of the present invention, 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 from the fluid inlet 302, and part of the blood flows into the flow channel 190 from the liquid inlet 101. After flowing through the first flow channel, part of the blood flowing into the first housing 310 directly flows out of the blood pump from the first fluid outlet 313, and part of the blood continues to flow into the second housing 320 and flows out of the blood pump from the second fluid outlet 323 after flowing through the second flow channel. The blood flowing into the flow channel 190 finally flows out from the liquid outlet 102 and is discharged outside the blood pump from the second fluid outlet 323.

[0139] As a preferred embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the rotor assembly 100 includes an impeller 110, a first internal magnetic bearing 130 and a second internal magnetic bearing 120, and the blade 112 is located on the impeller 110. The impeller 110, the first internal magnetic bearing 130, the second internal magnetic bearing 120 and the power magnetic ring 201 are fixedly connected to each other. A first external magnetic bearing 360 and a second external magnetic bearing 350 are also provided on the inner wall of the shell 300. The first external magnetic bearing 360 is sleeved on the outside of the first internal magnetic bearing 130, and the second external magnetic bearing 350 is sleeved on the outside of the second internal magnetic bearing 120. There is a radial repulsion between the first external magnetic bearing 360 and the first internal magnetic bearing 130, and there is a radial repulsion between the second external magnetic bearing 350 and the second internal magnetic bearing 120.

[0140] In an embodiment of the present 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 solution through mechanical bearings, it can effectively reduce the rotor rotation resistance and improve the heating condition of the blood pump, thereby ensuring the safety of medical operations.

[0141] As a preferred embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the rotor assembly 100 further includes a central shaft 150 , and the impeller 110 , the first internal magnetic bearing 130 , the second internal magnetic bearing 120 and the power magnetic ring 201 are all fixedly disposed on the central shaft 150 .

[0142] In an 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, thereby ensuring the stability of the relative positions between the components, improving the overall structural strength of the rotor assembly 100, and reducing the amplitude of deformation of the rotor assembly 100 caused by the flow field during rotation, thereby improving the stability of the position of the rotor assembly 100 inside the housing 300, ensuring the stability of the operation of the blood pump, and reducing the friction and wear between the components on the rotor assembly 100, thereby extending the service life of the blood pump.

[0143] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the impeller 110 includes a fixed cylinder 111 and a plurality of blades 112 . The fixed cylinder 111 is sleeved and fixed on the central shaft 150 . The plurality of blades 112 are fixedly arranged on the outer wall of the fixed cylinder 111 , and the plurality of blades 112 are circumferentially distributed around the axis of the rotor assembly 100 .

[0144] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, impeller 110 includes a pair of blades 112 .

[0145] As an optional embodiment of the present invention, Figure 5 、 Figure 8 As shown, the flow channel 190 includes a group of first branch channels 1921 , one end of the first branch channel 1921 is connected to the central 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 the present invention, Figure 5 、 Figure 8As shown, the first branch channel 1921 includes a first inlet branch channel 1921a located in the central axis 150 and a first guide branch channel 1921b located in the fixed cylinder 111. One end of the first inlet branch channel 1921a is connected to the central flow channel 191, and the other end is connected to one end of the first guide branch channel 1921b. The other end of the first guide branch 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 the present invention, 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 at the stage L1 is larger than the diameter of the parts of the central shaft 150 on both sides of the stage L1. The power magnetic ring 201 is located on the power section L2, and the second internal magnetic bearing 120 is located on the side of the stage L1 away from the power section L2.

[0148] In an embodiment of the present invention, the central shaft 150 has a step L1 with a diameter larger than the diameters on both sides, so that the axial position of the power magnetic ring 201 can be positioned by utilizing the step between the step L1 and the power section L2, and the axial position of the second internal magnetic bearing 120 can be positioned by utilizing the step between the step L1 and the part of the central shaft 150 located on the other side of the step L1, thereby further ensuring the stability of the relative positional relationship between the components and improving the structural strength of the rotor assembly 100.

[0149] In order to further improve the structural strength of the rotor assembly 100, as a preferred embodiment of the present invention, Figure 10 As shown, the rotor assembly 100 also includes a rotor shell 160, which is sleeved on the central shaft 150, and has a bearing accommodating cavity 161 and a power accommodating cavity 162 in the rotor shell 160. The second internal magnetic bearing 120 is accommodated in the bearing accommodating cavity 161, and the power magnetic ring 201 is accommodated in the power accommodating cavity 162.

[0150] In an embodiment of the present invention, the second inner magnetic bearing 120 and the power magnetic ring 201 are respectively accommodated in the bearing accommodating cavity 161 and the power accommodating cavity 162, so that the axial position of the second inner magnetic bearing 120 and the power magnetic ring 201 is further positioned by using the rotor housing 160, thereby ensuring the stability of the relative position relationship between the components, improving the structural strength of the rotor assembly 100, and at the same time separating the blood from the second inner magnetic bearing 120 and the power magnetic ring 201, avoiding direct contact between the second inner magnetic bearing 120 and the power magnetic ring 201 and the liquid environment, thereby preventing the various components mounted on the central shaft 150 from being corroded, and ensuring the service life of the blood pump.

[0151] As an optional embodiment of the present invention, 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 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 the present invention, Figure 5 、 Figure 8 As shown, the second diversion channel 1922 includes a second inlet diversion channel 1922a located in the central axis 150 and a second guide diversion channel 1922b located in the rotor housing 160. One end of the second inlet diversion channel 1922a is connected to the central channel 191, and the other end is connected to one end of the second guide diversion channel 1922b. The other end of the second guide diversion channel 1922b has a liquid inlet 101 on the surface of the rotor housing 160.

[0153] For ease of understanding, Figure 6 、 Figure 9 The figure shows the internal fluid flow path of the blood pump when the rotor assembly has both the first branch channel 1921 and the second branch channel 1922. Blood flows from the fluid inlet 302 into the first housing 310 (as shown in FIG. Figure 9 As shown, in the case where a hub flow channel 191b is formed in the impeller hub 180, part of the blood flows directly into the central flow channel 1511 through the liquid inlet 101 at the top of the rotor assembly), and after flowing through the first flow channel, part of the blood flows directly out of the blood pump from the first fluid outlet 313, part continues to flow into the second housing 320, and part flows into the central flow channel 191 through the first branch channel 1921; part of the blood that flows into the second housing 320 flows out of the blood pump from 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 from the liquid outlet 102 and is discharged out of the blood pump from the second fluid outlet 323.

[0154] In order to further improve the structural strength of the rotor assembly 100, as a preferred embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the rotor housing 160 has a boss portion 168 at one end facing the fluid inlet 302, and the fixed cylinder 111 of the impeller 110 has a connecting groove at one end facing away from the fluid inlet 302, and the boss portion 168 is accommodated in the connecting groove, so that mechanical limiting is achieved by utilizing the snap-fit ​​relationship between the boss portion 168 and the connecting groove, thereby ensuring the concentricity between the rotor housing 160 and the impeller 110, and further ensuring the overall structural strength of the rotor assembly 100 during rotation.

[0155] As an optional embodiment of the present invention, the impeller 110 is bonded to the rotor housing 160 .

[0156] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the rotor assembly 100 also includes an impeller hub 180, the impeller 110 is sleeved on one end of the central axis 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 one end of the impeller 110 facing the fluid inlet 302, and the first internal magnetic bearing 130 is arranged inside the impeller hub 180.

[0157] As an optional embodiment of the present invention, 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, wherein 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 the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 、 Figure 10 、 Figure 11 As shown, the impeller hub 180 is of streamlined design. Specifically, the end of the impeller hub 180 facing away from the impeller 110 has a diameter-reducing section, and the diameter of the impeller hub 180 in the diameter-reducing section gradually increases in a direction approaching the impeller 110 .

[0159] As an optional embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 7 、 Figure 8 As shown, the first inner magnetic bearing 130 is sleeved on the central shaft 150 .

[0160] As a preferred embodiment of the present invention, Figure 1 、 Figure 2 、 Figure 4 、 Figure 5 、 Figure 7 、 Figure 8 As shown, the rotor assembly 100 further includes a displacement sensor module 170 , and an induction coil 370 is further 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 an 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, and the axial position of the induction coil 370 partially overlaps with the axial position of the displacement sensor module 170. Therefore, 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, and the position of the rotor assembly 100 can be feedback controlled by adjusting the force condition of the rotor assembly 100 to ensure that the rotor assembly 100 is in a fully suspended state, thereby ensuring the stability of the blood pump operation.

[0162] In order to further improve the structural strength of the rotor assembly 100, as a preferred embodiment of the present invention, 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 internal magnetic bearing 120 is sleeved on the first positioning section L3, the second positioning section L4 is connected to the 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 connection position of 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 an embodiment of the present invention, the position of the displacement sensor module 170 corresponds to the position of the connection between the first positioning segment L3 and the second positioning segment L4, so that the displacement sensor module 170 is axially positioned by utilizing the step at the connection between the first positioning segment L3 and the second positioning segment L4, thereby 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 the present invention, Figure 10 As shown, the rotor housing 160 further has a sensing accommodating cavity 163 , and the displacement sensor module 170 is accommodated in the sensing accommodating cavity 163 .

[0165] As an optional embodiment of the present invention, Figure 10 As shown, the rotor housing 160 further comprises a first stepped hole 164, a through hole 165, a second stepped hole 166, and a third stepped hole 167. The first stepped hole 164, the through hole 165, the second stepped hole 166, and the third stepped hole 167 are all coaxially arranged with the rotor housing 160. The through hole 165 extends from the power accommodating chamber 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 is connected between the bearing accommodating chamber 161 and the power accommodating chamber 162, and its diameter corresponds to the diameter of the stage L1. The second stepped hole 166 is connected between the induction accommodating chamber 163 and the bearing accommodating chamber 161, and its diameter corresponds to the diameter of the first positioning section L3. The third stepped hole 167 extends from the induction accommodating chamber 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 the present invention, Figure 14 、 Figure 15 As shown, the rotor housing 160 includes a pair of housing parts 160a, and the two housing parts 160a are respectively embraced by the two sides of the central axis 150, the displacement sensor module 170, the second inner magnetic bearing 120 and the power magnetic ring 201, and the mating surfaces of the housing parts 160a are bonded together.

[0167] As an optional embodiment of the present invention, Figure 2 、 Figure 8 As shown, the central axis 150 also includes a third positioning segment L5, which is connected to the side of the second positioning segment L4 away from the stage L1, and the diameter of the third positioning segment L5 is smaller than the diameter of the second positioning segment L4; the first internal magnetic bearing 130 is sleeved on the third positioning segment L5.

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

[0169] First, if Figures 15 and 16 As shown, the modules corresponding to the chambers in the rotor housing 160 (the second inner magnetic bearing 120, the power magnetic ring 201, and the displacement sensor module 170) are sequentially mounted on the central shaft 150, so that each module contacts the corresponding step (shoulder), and the two housing parts 160a are aligned so that they surround the central shaft 150 and both sides of each module, and the two are bonded together to form the rotor housing 160;

[0170] Then, if Figures 16 and 17 As shown, the head end of the central shaft 150 passes through the second housing 320, so that the rotor housing 160 is accommodated in the second housing 320, and the impeller 110, the first internal magnetic bearing 130 (not shown in the figure and 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 on both sides, the rotor assembly 100 cannot be easily removed from the second housing 320);

[0171] Then, if Figures 17 and 18 As shown, the first connecting bars 312 of the first housing 310 are fixedly connected to the second housing 320 to assemble and form the guide housing 301;

[0172] Finally, if Figures 18 and 19 As shown, the multiple second connecting bars 322 of the second housing 320 are fixedly connected to the stator housing 330 to install the stator assembly 200 to the proximal end of the aforementioned structure, and then the shrink housing 340, the conduit 400 and other structures are sequentially installed to the proximal end of the second housing 320 to complete the installation operation.

[0173] In the blood pump provided in an embodiment of the present invention, the rotor assembly 100 is located between the fluid inlet 302 and the stator assembly 200, and is capable of rotating under the influence of the magnetic field generated by the stator assembly 200 and driving blood through the blades 112 to flow 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. In addition, a flow channel 190 is formed in the rotor assembly 100, and the liquid outlet 102 of the flow channel 190 is located at the proximal end of the rotor assembly 100. As a result, some blood entering the housing 300 can flow into the flow channel 190 and flow out through 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, thereby accelerating the blood flow rate in this area.

[0174] The embodiment of the present invention utilizes the flow channel 190 in the rotor assembly 100 to guide blood to the proximal end of the rotor assembly 100, thereby ensuring the blood flow speed in the area between the proximal end of the rotor assembly 100 and the stator assembly 200. This can effectively avoid coagulation caused by the reduction of blood flow speed in the blood pump, ensure the smooth rotation of the rotor assembly 100, and further ensure the stability of the blood pump operation and the safety of medical operations.

[0175] The above are only specific embodiments of the present invention, but the scope of protection of the present invention is not limited thereto. Those skilled in the art should understand that the present invention includes but is not limited to the contents described in the drawings and the above specific embodiments. Any modifications that do not deviate from the functional and structural principles of the present invention are intended to be included within the scope of the claims.

Claims

1. A blood pump, characterized in that: The invention comprises a rotor assembly, a stator assembly and a housing. The rotor assembly and the stator assembly are axially spaced apart in the housing along the direction of fluid flow. The rotor assembly can rotate around its own axis under the action of the magnetic field generated by the stator assembly to drive the fluid to flow through the rotor assembly. An overflow channel is formed in the rotor assembly. The overflow 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 according to claim 1, wherein The flow passage includes a central flow channel, which is arranged axially along the rotor assembly. Two ends of the central flow channel are respectively connected to the liquid inlet and the liquid outlet.

3. The blood pump according to claim 2, characterized in that 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 communicated with the central channel.

4. The blood pump according to claim 3, characterized in that The flow dividers are arranged along the circumferential direction of the axis of the rotor assembly.

5. The blood pump according to claim 3, characterized in that The flow divider is located between the blades of the rotor assembly and the stator assembly.

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

7. The blood pump according to claim 1, characterized in that The blood pump further includes a flow guide member, which is located between the rotor assembly and the stator assembly; the flow guide member has a plurality of flow guide fins, and the plurality of flow guide fins face one side of the rotor assembly.

8. The blood pump according to claim 7, characterized in that 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 shell. 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 fin and the radial direction of the rotor assembly gradually increases in the direction toward the side wall of the shell.

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

10. The blood pump according to claim 8, characterized in that The rotor assembly further has a guide hole at one end facing the stator assembly, the diameter of which gradually increases in the direction toward the stator assembly; the guide hole is connected to the flow channel, and the guide fin is located in the guide hole on the side facing the rotor assembly.

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