Blood pumping device, motor, and ventricular assist device

Abstract

Disclosed in the present application are a blood pumping device, a motor, and a ventricular assist device. The blood pumping device is used for pumping blood. The blood pumping device comprises a motor, a first pipe and a second pipe; the motor comprises a stator assembly, the stator assembly comprising a core, and the core enclosing to form an accommodating cavity; a first circulation cavity is formed in the core, and a second circulation cavity communicated with the first circulation cavity is formed in the core and / or in the accommodating cavity; the first pipe is communicated with the first circulation cavity, and the second pipe is communicated with the second circulation cavity; one of the first pipe and the second pipe serves as a perfusion pipe, and the other one serves as a backflow pipe; and the perfusion pipe is used for conveying a perfusate to the motor, and the backflow pipe is used for discharging the perfusate in the motor.

Description

Blood pumping device, motor and ventricular assist device

[0001] Cross-reference to related applications

[0002] This application claims priority to Chinese Patent Application No. 202410661543.1, filed on May 24, 2024, entitled “Blood pumping device and motor”, the entire contents of which are incorporated herein by reference. TECHNICAL FIELD

[0003] The present application belongs to the technical field of medical devices, and in particular relates to a blood pumping device, a motor and a ventricular assist device. BACKGROUND

[0004] In cardiac surgery, due to the patient's own disease or the need for surgery, the patient's heart function is weakened, and the blood pumping capacity is insufficient. At this time, it is necessary to insert a ventricular assist device and other active intervention medical devices into the heart to assist the heart in pumping blood. The existing ventricular assist device uses the principle of heart pumping to pump blood out of the heart through a pumping mechanism and guide the blood to the aorta outside the heart to flow to the whole body.

[0005] In some scenarios, the existing ventricular assist device includes a catheter and a blood pumping device, the blood pumping device is arranged at the distal end (the end away from the operator or the physician) of the catheter, and the blood pumping device can be pushed through the femoral artery or axillary artery or carotid artery intervention through the catheter. At this time, the suction window of the ventricular assist device is located in the left ventricle, and the outflow window is located in the aorta. When the blood pumping device is started, the blood in the left ventricle is pumped into the aorta through the suction window and the outflow window, thereby realizing the blood pumping function of the ventricular assist device. Similarly, the blood pumping device can also be pushed through the femoral vein and other veins through the catheter. When the blood pumping device is running, heat will be generated, and if the heat of the blood pumping device is too high, it will cause damage to the patient. SUMMARY

[0006] The embodiments of the present application provide a blood pumping device, which can improve the effective heat dissipation of the blood pumping device and the motor.

[0007] In a first aspect, the embodiments of the present application provide a blood pumping device for transporting blood, comprising a motor, a first pipeline and a second pipeline, the motor comprising a stator assembly, the stator assembly comprising a core, the core enclosing a receiving cavity, the core being provided with a first flow-through cavity, and the core and / or the receiving cavity being provided with a second flow-through cavity in communication with the first flow-through cavity; the first pipeline being in communication with the first flow-through cavity; the second pipeline being in communication with the second flow-through cavity, one of the first pipeline and the second pipeline being a perfusion pipeline, and the other being a reflux pipeline, the perfusion pipeline being used for transporting perfusion fluid to the motor, and the reflux pipeline being used for discharging the perfusion fluid in the motor.

[0008] According to an embodiment of the first aspect of the present application, the first flow cavity is a strip-shaped cavity extending along the first direction, wherein the first direction is a direction in which the distal end of the motor points to the proximal end.

[0009] According to an embodiment of the first aspect of the present application, the core comprises an inner core and an outer core sleeved outside the inner core, and the outer peripheral surface of the inner core is fitted with the inner peripheral surface of the outer core: a groove is arranged on the outer peripheral surface of the inner core, and the first flow cavity is formed between the groove and the outer core; or, a groove is arranged on the inner peripheral surface of the outer core, and the first flow cavity is formed between the groove and the inner core; or, grooves are arranged on the outer peripheral surface of the inner core and the inner peripheral surface of the outer core, and the first flow cavity is formed between the grooves on the inner core and the outer core.

[0010] According to an embodiment of the first aspect of the present application, the first flow cavity spirally extends in the core along the first direction.

[0011] According to an embodiment of the first aspect of the present application, the motor further comprises a rotor assembly, the rotor assembly comprising a rotating shaft and a magnetic steel, the rotating shaft extending along the first direction, at least part of the rotating shaft being located in the accommodating cavity, and the magnetic steel being located in the accommodating cavity and sleeved on the rotating shaft; the magnetic steel has a pole pair number P, and the first flow cavity spirally surrounds the rotating shaft, and the number of surrounding turns T of a single first flow cavity is T=1 / P or T=1 / (2P).

[0012] According to an embodiment of the first aspect of the present application, the stator assembly further comprises a winding located in the accommodating cavity, the winding being sleeved outside the magnetic steel, and a gap between the winding and the rotor assembly forming a second flow cavity; the length of the winding in the first direction is L: when the number of surrounding turns T of the first flow cavity is T=1 / P, the pitch H of the first flow cavity is PL; when the number of surrounding turns T of the first flow cavity is T=1 / (2P), the pitch H of the first flow cavity is 2PL.

[0013] According to an embodiment of the first aspect of the present application, the motor further comprises: a distal end bearing sleeved on the rotating shaft, the distal end bearing communicating the first flow cavity and the second flow cavity; a proximal end bearing sleeved on the rotating shaft, the rotating shaft being rotatably connected to the stator assembly through the distal end bearing and the proximal end bearing, the distal end bearing being located on the side of the proximal end bearing away from the first pipe; a distal end cover connected to the distal end of the stator assembly, the distal end cover being provided with a first through hole penetrating the distal end cover along the first direction, at least part of the rotating shaft extending out of the accommodating cavity from the first through hole, the distal end cover being used for sealing the distal end of the accommodating cavity, a third flow cavity being formed between the distal end cover and the distal end bearing, the third flow cavity communicating the first flow cavity and the second flow cavity through the distal end bearing; and a proximal end cover connected to the proximal end of the stator assembly, the proximal end cover being used for sealing the proximal end of the accommodating cavity, the proximal end cover being provided with a second through hole penetrating the distal end cover along the first direction, the second through hole being used for communicating the second flow cavity and the second pipe.

[0014] According to an embodiment of the first aspect of the present application, the motor further comprises: a proximal bearing seat connected with the proximal end of the stator assembly, the proximal bearing seat being provided with a first mounting hole penetrating the proximal bearing seat along the first direction, the proximal bearing and the proximal cover being embedded in the first mounting hole, and the proximal cover being located at one end of the proximal bearing away from the distal bearing; and a distal bearing seat connected with the distal end of the stator assembly, the distal bearing seat being provided with a second mounting hole penetrating the distal bearing seat along the first direction, and the distal bearing being embedded in the second mounting hole.

[0015] According to an embodiment of the first aspect of the present application, the distal cover has a gap with the distal bearing seat in the first direction, and the gap between the distal cover and the distal bearing seat forms a third flow cavity, and the third flow cavity communicates with the first flow cavity and the second flow cavity.

[0016] According to an embodiment of the first aspect of the present application, the first pipeline is a perfusion pipeline, and the second pipeline is a reflux pipeline.

[0017] According to an embodiment of the first aspect of the present application, the proximal bearing seat is further provided with a first communication hole, and the first communication hole communicates the first flow cavity and the first pipeline.

[0018] According to an embodiment of the first aspect of the present application, one of the openings of the first communication hole is located on the end face of the proximal bearing seat away from the distal bearing seat and communicates with the first pipeline, and the other opening is located on the circumferential face of the proximal bearing seat away from the first mounting hole and communicates with the first flow cavity.

[0019] According to an embodiment of the first aspect of the present application, the motor further comprises a rotor assembly, the rotor assembly comprising a rotating shaft and a magnetic steel, the rotating shaft extending along the first direction, at least part of the rotating shaft being located in the accommodating cavity, and the magnetic steel being located in the accommodating cavity and sleeved on the rotating shaft; and the pitch of the first flow cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively.

[0020] According to an embodiment of the first aspect of the present application, the stator assembly further comprises a winding located in the accommodating cavity, the winding being sleeved outside the magnetic steel, and the gap between the winding and the rotor assembly forming a second flow cavity; in a state where the length of the magnetic steel along the first direction is equal to the length of the winding along the first direction, the pitch of the first flow cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively; and in a state where the length of the magnetic steel along the first direction is less than the length of the winding along the first direction, the pitch of the first flow cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively, and the pitch of the first flow cavity is positively correlated with the length of the winding along the first direction.

[0021] According to an embodiment of the first aspect of the present application, the iron core comprises an inner iron core and an outer iron core sleeved outside the inner iron core, the outer iron core being arranged with a gap from the inner iron core, and the gap between the inner iron core and the outer iron core forming the first flow cavity.

[0022] The second aspect of the present application provides an electric machine, comprising a stator assembly, the stator assembly comprising a core, the core enclosing a receiving cavity, the core being provided with a first flow cavity, and the core and / or the receiving cavity being provided with a second flow cavity in communication with the first flow cavity, one of the first flow cavity and the second flow cavity being used for communication with a perfusion pipeline, and the other being used for communication with a reflux pipeline.

[0023] It can be understood that the electric machine provided by the second aspect of the present application can be any one of the electric machines provided by the first aspect of the present application, and will not be described repeatedly herein. The electric machine can be used for pumping blood, pumping tissue fluid, and pumping digestive juice, etc. in various application scenarios.

[0024] In a third aspect, the embodiments of the present application provide a ventricular assist device, comprising the blood pumping device, an outflow channel, and an interventional catheter, the interventional catheter being connected to the proximal end of the blood pumping device, the outflow channel being connected to the distal end of the blood pumping device, and the outflow channel being provided with an inhalation window and an outflow window.

[0025] The blood pumping device provided by the embodiments of the present application comprises an electric machine, a first pipeline, and a second pipeline. The electric machine comprises a stator assembly, the stator assembly comprising a core, the core enclosing a receiving cavity, the core being provided with a first flow cavity, and the core and / or the receiving cavity being provided with a second flow cavity in communication with the first flow cavity. The first pipeline is in communication with the first flow cavity. The second pipeline is in communication with the second flow cavity. One of the first pipeline and the second pipeline is a perfusion pipeline, and the other is a reflux pipeline. The perfusion pipeline is used for delivering perfusion liquid to the electric machine, and the reflux pipeline is used for discharging the perfusion liquid in the electric machine. In the present application, the first pipeline and the second pipeline are in communication with the inside of the electric machine. After the perfusion liquid flows to the electric machine through one of the pipelines, the perfusion liquid flows through the first flow cavity and the second flow cavity and carries away the heat generated by the electric machine, and then flows out from the other pipeline, thereby improving the effective heat dissipation of the blood pumping device and reducing the damage of the blood pumping device to the patient. By providing the first flow cavity in communication with the first pipeline in the core, a pipeline needs not to be additionally arranged outside the electric machine, the outer diameter of the electric machine is reduced, and the difficulty of intervention is reduced. BRIEF DESCRIPTION OF DRAWINGS

[0026] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required to be used in the embodiments of the present application will be briefly introduced. For those skilled in the art, other drawings can also be obtained without creative labor on the basis of these drawings.

[0027] FIG. 1 is a structural schematic diagram of a ventricular assist device comprising a blood pumping device according to some embodiments of the present application;

[0028] FIG. 2 shows a longitudinal cross-sectional structural schematic diagram of the ventricular assist device in FIG. 1 according to an example;

[0029] Fig. 3 shows a structural schematic view of an inner core and a proximal bearing seat according to an example;

[0030] Fig. 4 shows a perspective structural schematic view of the inner core and the proximal bearing seat in Fig. 3 according to an example;

[0031] Fig. 5 shows a cross-sectional structural schematic view of the ventricular assist device in Fig. 2 at the A-A position according to an example;

[0032] Fig. 6 shows a cross-sectional structural schematic view of the ventricular assist device in Fig. 2 at the A-A position according to another example;

[0033] Fig. 7 shows a cross-sectional structural schematic view of the ventricular assist device in Fig. 2 at the A-A position according to yet another example;

[0034] Fig. 8 shows a structural schematic view of a proximal end cap according to an example;

[0035] Fig. 9 shows a structural schematic view of an outer core and a distal end cap according to an example;

[0036] Fig. 10 shows a structural schematic view of a distal bearing seat according to an example;

[0037] Fig. 11 shows a structural schematic view of an inner core and a proximal bearing seat according to another example;

[0038] Fig. 12 shows a cross-sectional structural schematic view of the inner core and the proximal bearing seat in Fig. 11 according to an example;

[0039] Fig. 13 shows a structural schematic view of a second conduit according to an example. DETAILED DESCRIPTION

[0040] The features and exemplary embodiments of various aspects of the present application will be described in detail below with reference to the drawings. The following detailed description is merely intended to explain the present application, and is not intended to limit the present application. The present application can be practiced without some of the specific details set forth below. The following description of the embodiments is merely provided to give a better understanding of the present application by showing examples of the present application.

[0041] It is to be noted that the relative terms such as first and second etc. are used herein only to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the terms "comprise", "contain" or any other variant thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements not only includes those elements, but also includes other elements not explicitly listed or inherent to such a process, method, article or device. Without more limitations, the elements defined by the statement "comprise" do not exclude the presence of other identical elements in the process, method, article or device including the elements.

[0042] To solve the technical problems involved in the background art, the applicant proposes a blood pumping device, comprising a motor, a first pipeline and a second pipeline, the motor comprising a stator assembly, the stator assembly comprising a core, the core enclosing a receiving cavity, the core being provided with a first flow-through cavity, and the core and / or the receiving cavity being provided with a second flow-through cavity in communication with the first flow-through cavity; the first pipeline being in communication with the first flow-through cavity; the second pipeline being in communication with the second flow-through cavity, one of the first pipeline and the second pipeline being a perfusion pipeline and the other being a reflux pipeline, the perfusion pipeline being used to deliver perfusion fluid to the motor, and the reflux pipeline being used to discharge the perfusion fluid in the motor.

[0043] The blood pumping device provided by the present application is in communication with the interior of the motor through the first pipeline and the second pipeline, and the perfusion fluid flows to the motor through one of the pipelines, then flows through the first flow-through cavity and the second flow-through cavity and carries away the heat generated by the motor, and then flows out from the other pipeline, thereby improving the effective heat dissipation of the blood pumping device and the motor and reducing the damage to the patient caused by the blood pumping device. By providing the first flow-through cavity in communication with the first pipeline in the core, no additional pipeline is needed outside the motor, the outer diameter of the motor is reduced, and the difficulty of intervention is reduced.

[0044] It can be understood that the motor in the present application can be applied to application scenarios such as blood pumping devices, tissue fluid pumping devices, digestive fluid pumping devices, etc. to achieve the purpose of pumping blood, tissue fluid, digestive fluid and other fluids. In order to facilitate understanding and description, the following will continue to take the application scenario of the motor applied in the blood pumping device as an example for description.

[0045] Before describing the specific structure of the blood pumping device, a ventricular assist device comprising the blood pumping device is briefly described in conjunction with the drawings so as to understand the working environment of the blood pumping device. Fig. 1 is a structural schematic diagram of a ventricular assist device comprising a blood pumping device according to some embodiments of the present application. Fig. 2 shows a longitudinal sectional structural schematic diagram of the ventricular assist device in Fig. 1 according to an example, wherein the first conduit is not shown. As can be seen from Figs. 1 and 2, the present application provides a ventricular assist device comprising a blood pumping device (not shown), an outflow channel 40 and an intervention catheter 30, wherein the intervention catheter 30 is connected to the proximal end of the blood pumping device, and the outflow channel 40 is connected to the distal end of the blood pumping device. The blood pumping device comprises a motor 10, and the outflow channel 40 is provided with an intake window (not shown) and an outflow window 41. The blood pumping device and the outflow channel 40 are pushed by the intervention catheter 30 to intervene in the blood vessels of a patient during use, until the blood pumping device and the outflow channel 40 are located at a designated position of the blood circulation system of the patient. At this time, the outflow window 41 and the intake window are located at different positions of the blood circulation system. When the motor 10 in the blood pumping device is started, the motor 10 drives blood to flow from the intake window into the outflow channel 40 and then out of the outflow window 41, thereby realizing the blood pumping function of the ventricular assist device.

[0046] When the blood pumping device, the intervention catheter 30 and the outflow channel 40 intervene in the patient's body, the end of the intervention catheter 30 away from the motor 10 extends out of the patient's body and is connected to a liquid storage tank (not shown), a power supply device, a control switch and the like. At least part of the first conduit and the second conduit 20 are located in the intervention catheter 30. The liquid storage tank transports and discharges perfusion liquid into the interior of the motor through the conduit. The perfusion liquid flows through the motor 10 and carries away the heat generated by the motor 10 during operation. The perfusion liquid comprises physiological saline and an anticoagulant, and the anticoagulant can be heparin. The anticoagulant in the perfusion liquid reduces the probability of blood coagulation, thereby reducing the probability of failure of the blood pumping function of the motor 10 due to blood coagulation.

[0047] It can be understood that, in the present application, the proximal end refers to the end towards the operator or physician, and the distal end refers to the end away from the operator or physician. The proximal end of the motor 10 faces the intervention catheter 30, and the distal end of the motor 10 faces the outflow channel 40.

[0048] After describing the structure of the ventricular assist device, the blood pumping device provided by the embodiments of the present application is introduced below in conjunction with the drawings. In the description, the line extending along the proximal end and the distal end of the motor in the drawings is denoted as x, and the direction from the distal end to the proximal end is the first direction.

[0049] As shown in FIGS. 1 and 2, the blood pumping device for delivering blood includes a motor 10, a first pipeline (not shown) and a second pipeline 20. The motor 10 includes a stator assembly 11, which includes an iron core 111 enclosing a receiving cavity 1111. The iron core 111 is provided with a first flow-through cavity 1112 and a second flow-through cavity 1113 in communication with the first flow-through cavity 1112. It can be understood that the first flow-through cavity 1112 is formed by a cavity or a gap in the solid structure of the iron core 111. The first pipeline is in communication with the first flow-through cavity 1112, and the second pipeline 20 is in communication with the second flow-through cavity 1113. One of the first pipeline and the second pipeline 20 is a perfusion pipeline, and the other is a reflux pipeline. The perfusion pipeline is used to deliver perfusion fluid to the motor 10, and the reflux pipeline is used to discharge the perfusion fluid in the motor 10.

[0050] In some implementations, the wall surface of the first flow-through cavity 1112 has high smoothness and low roughness, and the wall surface of the first flow-through cavity 1112 is subjected to hydrophilic coating treatment.

[0051] It can be understood that the layout of the second flow-through cavity 1113 in the iron core 111 and / or the receiving cavity 1111 will be described in detail below, and will not be described here.

[0052] In some embodiments, the first flow-through cavity 1112 and the second flow-through cavity 1113 are directly or indirectly in communication. Indirect communication means that the first flow-through cavity 1112 and the second flow-through cavity 1113 are in communication through at least one other cavity, gap or space structure. This embodiment is described in the application scenario of indirect communication between the first flow-through cavity 1112 and the second flow-through cavity 1113.

[0053] The blood pumping device provided in this embodiment is in communication with the motor 10 through the first pipeline and the second pipeline 20. After the perfusion fluid flows to the motor 10 through one of the pipelines, it flows through the first flow-through cavity 1112 and the second flow-through cavity 1113 and carries away the heat generated by the motor 10, and then flows out from the other pipeline, thereby improving the effective heat dissipation of the blood pumping device and reducing the damage to the patient caused by the blood pumping device. By providing the first flow-through cavity 1112 in communication with the first pipeline in the iron core 111, it is not necessary to additionally provide a pipeline outside the motor, thereby reducing the outer diameter of the motor 10 and the difficulty of intervention.

[0054] In some embodiments of the present application, the first pipeline and the second pipeline can be a hole structure, a pipeline structure or other structures that can allow fluid to pass through.

[0055] In some embodiments of the present application, the first conduit and the second conduit can be located at one end or both ends of the stator assembly. In some implementations, the first conduit and the second conduit are located at the distal end of the stator assembly, which is more reasonable in layout and easier to control the insertion size of the motor assembly. In alternative implementations, the first conduit is located at the proximal end of the stator assembly, and the second conduit is located at the distal end of the stator assembly, for example, the gap between the second mounting hole and the rotating shaft mentioned below.

[0056] After describing the overall structure of the blood pumping device, several implementations of the first flow-through cavity in the blood pumping device are described below in conjunction with the drawings. In some embodiments, the first flow-through cavity 1112 is a strip-shaped cavity extending along the first direction x. The first direction x is the direction from the distal end of the motor 10 to the proximal end.

[0057] It can be understood that the first flow-through cavity 1112 in the present application is a strip-shaped cavity extending along the first direction x, which does not mean that the first flow-through cavity 1112 is a straight linear cavity, and the center line of the straight linear cavity is a straight line parallel to the first direction x. Rather, the first flow-through cavity 1112 has two opposite ends, one end facing the proximal side and the other end facing the distal side, but the trajectory of one end of the first flow-through cavity 112 extending to the other end is not specifically limited.

[0058] As shown in FIG. 2, in some embodiments, the core 111 includes an inner core 112 and an outer core 113 sleeved outside the inner core 112, and the outer peripheral surface of the inner core 112 is fitted with the inner peripheral surface of the outer core 113. The gap between the inner core 112 and the outer core 113 forms the first flow-through cavity 1112, and the inner core 112 forms the accommodation cavity 1111. The gap between the inner core 112 and the outer core 113 is formed due to local recess.

[0059] In some embodiments, the inner core 112 and the outer core 113 can be a cylinder, or a polygonal cylindrical structure such as a square cylinder. The present embodiment takes the inner core 112 and the outer core 113 as a cylinder as an example.

[0060] As shown in the drawings, the inner core 112 and the outer core 113 are both axisymmetric figures, and each has a central axis extending in the direction consistent with the line connecting the proximal end and the distal end of the motor, i.e., the direction x in the drawings. The inner core 112 and the outer core 113 are cylindrical structures, and thus have two circumferential surfaces, one being the outer circumferential surface of the cylindrical outer wall and the other being the inner circumferential surface of the cylindrical inner wall. In addition, the axial direction of the inner core 112 refers to the direction in which the central axis extends. The circumferential direction of the inner core 112 refers to the circumferential direction of the cylindrical outer wall. The radial direction refers to the direction in the radial plane through the central axis, and is usually referred to as the linear direction along the diameter or radius, or the linear direction perpendicular to the central axis. The radial dimension generally refers to the radius or diameter of the axisymmetric part. It can be understood that, in the present application, the axial direction, the circumferential direction, the radial direction, and the circumferential surface of other components can be understood with reference to the foregoing descriptions of the inner core 112.

[0061] FIG. 3 shows a schematic structural view of an example of the inner core and the proximal bearing seat; FIG. 4 shows a perspective schematic structural view of the inner core and the proximal bearing seat in FIG. 3; FIG. 5 shows a schematic structural view of a cross section of the ventricular assist device in FIG. 2 at the A-A position; FIG. 6 shows a schematic structural view of a cross section of another example of the ventricular assist device in FIG. 2 at the A-A position; and FIG. 7 shows a schematic structural view of a cross section of yet another example of the ventricular assist device in FIG. 2 at the A-A position. In FIGS. 5 to 7, the sizes of the structures in the drawings are not necessarily proportional to the structures in other drawings for the convenience of displaying the structure of the flow-through cavity.

[0062] As shown in FIGS. 2 to 5, in some embodiments, the outer core 113 is sleeved on the outer surface of the inner core 112, and the inner circumferential surface of the outer core 113 is attached to the outer circumferential surface of the inner core 112. The inner core 112 is provided with a groove 114a recessed into the accommodation cavity 1111 toward the circumferential surface of the outer core 113, and the gap between the groove 114a and the outer core 113 forms the first flow-through cavity 1112. The attachment of the inner circumferential surface of the outer core 113 to the outer circumferential surface of the inner core 112 means that the attachment is made except for the groove 114a, and not the complete attachment of the entire inner circumferential surface and the entire outer circumferential surface.

[0063] In some implementations, the wall surface of the groove 114a has high smoothness and low roughness, and is provided with a hydrophilic coating.

[0064] As shown in FIGS. 2 and 6, in some other embodiments, the outer core 113 is provided with a groove 114b recessed away from the accommodation cavity 1111 toward the circumferential surface of the inner core 112, and the gap between the groove 114b and the inner core 112 forms the first flow-through cavity 1112. The gap between the groove 114b and the inner core 112 refers to the gap between the groove wall of the groove 114b and the inner core 112.

[0065] As shown in FIG. 2 and FIG. 7, in some other embodiments, the outer core 113 is sleeved on the inner core 112, and the inner circumferential surface of the outer core 113 is attached to the outer circumferential surface of the inner core 112. The circumferential surface of the inner core 112 facing the outer core 113 and the circumferential surface of the outer core 113 facing the inner core 112 are both provided with grooves 114c, and the grooves 114c on the inner core 112 and the grooves 114c on the outer core 113 form a first flow cavity 1112. The grooves 114c on the inner core 112 and the outer core 113 can be arranged in alignment to form a groove with a larger cross-sectional area, or the grooves 114c on the inner core 112 and the outer core 113 can be arranged out of alignment, so that the number of the first flow cavity 1112 is multiple. In this embodiment, the inner core 112 is taken as an example, and only the grooves 114a are opened on the inner core 112. The outer circumferential surface of the inner core 112 is the circumferential surface facing the outer core 113, and the inner circumferential surface of the outer core 113 is the circumferential surface facing the inner core 112.

[0066] In some embodiments, the number of the grooves 114 can be one or more. The depth of the groove 114 is 0.05mm-0.5mm, for example, the depth of the groove 114 can be any one of 0.05mm, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm and 0.5mm. The depth of the groove 114 can refer to the dimension of the groove 114 along the radial direction.

[0067] In one example, the grooves are arranged in multiple along the circumferential direction of the core.

[0068] The pump blood device provided by the embodiment is characterized in that the recess 114 is arranged on the inner iron core 112 and / or the outer iron core 113, the first flow cavity 1112 is formed by the recess 114, and the perfusion liquid is transported along the extension direction of the recess 114. Since the first flow cavity formed by the recess 114 is a strip-shaped cavity, compared with a ring-shaped cavity with a larger cross-sectional area, the strip-shaped cavity has a smaller cross-sectional area, so that the perfusion liquid pressure at different positions of the first flow cavity 1112 is similar, and bubbles are not easily left in the first flow cavity 1112. Bubble residues in the perfusion pipeline may have the following consequences: 1) since the bubbles are compressible, the high-pressure pulsation in the aorta can cause blood to flow back into the catheter, thereby causing the catheter to fail (wherein the working environment of the distal end of the perfusion device is the aortic pressure of the human body, the pulsatile pressure changes over time, if there are bubbles in the perfusion device, the volume of the gas will change with the change of the pressure, which will affect the instantaneous flow direction of the perfusion liquid at the farthest end, when the volume of the bubble decreases with the increase of the environmental pulse pressure, blood may flow back into the perfusion system, affecting the reliability of the blood pump catheter. Blood is easy to form thrombus in the transmission area, especially in the bearing position, which increases the transmission friction coefficient and reduces the service life of the transmission system, and is easy to cause excessive temperature rise); 2) the bubbles are not completely discharged, and there is a certain probability that they will enter the blood vessels in the future, causing gas embolism.

[0069] As shown in FIGS. 2 to 4, in some embodiments, the first flow cavity 1112 spirally extends in the first direction x in the iron core 111, wherein the first direction x is a direction in which the distal end of the motor 10 points to the proximal end. It is easy to understand that when the iron core 111 is composed of the inner iron core 112 and the outer iron core 113, and the recess 114 is arranged on the inner iron core 112 and / or the outer iron core 113, the recess 114 also spirally extends in the first direction x.

[0070] It can be understood that, in the present application, the first flow cavity 1112 spirally extends in the first direction x in the iron core 111, which can mean that the first flow cavity 1112 has two opposite ends, and the trajectory of one end of the first flow cavity 1112 extending to the other end spirally extends around an axis parallel to the first direction.

[0071] Compared with the scheme of arranging a straight flow cavity in the first direction x, in the present scheme, the first flow cavity 1112 is spirally arranged, so that the solid thickness of the inner iron core 112 and the outer iron core 113 in the first direction x is more uniform, and the first flow cavity 1112 is located at different positions of the iron core 111 in the circumferential direction when extending in the first direction x, which does not cause the iron core 111 to be thinned on one side, thereby improving the uniformity of the magnetic field distribution of the motor 10.

[0072] In some embodiments, the motor 10 further comprises a rotor assembly 12, the rotor assembly 12 comprising a rotor shaft 121 extending along the first direction x and at least partially located in the accommodating cavity 1111, and a magnetic steel 122 located in the accommodating cavity 1111 and sleeved on the rotor shaft 121. The magnetic steel 122 has a pole pair number P, and the first flow cavity 1112 spirally surrounds the rotor shaft 121 and has a number of turns T = 1 / P or T = 1 / (2P).

[0073] The pole pair number P refers to the number of pole pairs in the magnetic steel 122, and the magnetic steel 122 comprises one or more N poles and S poles arranged around the rotor shaft 121 at intervals, and the number of N poles and S poles is equal, that is, the number of N poles is the pole pair number P of the magnetic steel 122. For example, when the pole pair number P is 1, the number of turns T of the first flow cavity 1112 is 1, and when the pole pair number P is 2, the number of turns T of the first flow cavity 1112 is 0.5. For example, when the pole pair number P is 1, the number of turns T of the first flow cavity 1112 is 0.5, and when the pole pair number P is 2, the number of turns T of the first flow cavity 1112 is 0.25. When the number of first flow cavities 1112 is multiple, the number of turns T of each first flow cavity 1112 is equal, and when each first flow cavity 1112 spirally surrounds the axis of the rotor shaft 121, the angle between the connecting line of any two adjacent first flow cavities 1112 and the axis of the rotor shaft 121 is equal. Preferably, the pole pair number P is 1, the number of turns T of the first flow cavity 1112 is 1, and the number of first flow cavities 1112 is 1. The number of turns refers to the number of complete revolutions of the first flow cavity 1112 in the circumferential direction of the iron core 111 around the axis. Specifically, if the first flow cavity 1112 extends along the spiral line and rotates around the axis for n turns from one end of the iron core 111 to the other end, the number of turns is n.

[0074] In the motor 10, the tooth portion (not shown) and the slot portion (not shown) on the iron core 111 can cause uneven magnetic field distribution and generate magnetic field torque, causing the iron core to vibrate and produce noise, and reducing the efficiency of the motor 10, which is called the cogging effect. The slot portion on the iron core 111 is used to connect with the winding, and the tooth portion is used to separate adjacent slot portions. Since the pole pair number P is related to the magnetic field distribution and the rotational speed of the motor 10, the blood pumping device provided in the embodiment can, according to simulation tests and physical verification, reduce the magnetic field torque by using the perfusion fluid spirally transported in the first flow cavity 1112 to offset the cogging effect of the motor 10 and improve the efficiency of the motor 10, by making the number of turns T of the first flow cavity 1112 = 1 / P or T = 1 / (2P).

[0075] In some embodiments, the stator assembly 11 further comprises a winding 115 located in the accommodating cavity 1111, and the winding 115 is sleeved outside the magnetic steel 122. The length of the winding 115 in the first direction x is L, and when the number of turns T of the first flow cavity 1112 is 1 / P, the pitch H of the first flow cavity 1112 is PL. When the number of turns T of the first flow cavity 1112 is 1 / (2P), the pitch H of the first flow cavity 1112 is 2PL.

[0076] In some embodiments, the length of the area covered by the first flow cavity 1112 in the first direction x is greater than or equal to the length of the area covered by the magnetic steel 122 in the first direction x, and / or greater than or equal to the length of the area covered by the winding 115 in the first direction x.

[0077] The winding 115 is fixedly connected to the slot portion of the core 111, and when the winding 115 is energized, the winding 115 generates a magnetic field and interacts with the magnetic field of the magnetic steel 122, and the magnetic steel 122 rotates synchronously with the rotating shaft 121.

[0078] The pitch H of the groove 114 can be understood with reference to the pitch of the bolt, that is, the distance between adjacent threads in the axial direction of the bolt, which generally refers to the axial distance between the two points corresponding to the adjacent two teeth on the pitch diameter line on a single thread. In the present embodiment, the pitch of the groove 114 can be understood as the distance between adjacent positions in the first direction x on a single groove 114 when the number of turns of the groove 114 is greater than 1.

[0079] Since the cogging effect is also related to the length of the winding 115 in the first direction x, the blood pumping device provided in the present embodiment, according to simulation tests and physical verification, uses the perfusion fluid transported by the first flow cavity 1112 to offset the cogging effect of the motor 10 and further reduce the magnetic field torque, thereby further improving the efficiency of the motor 10.

[0080] In some specific embodiments of the present application, the pitch of the first flow cavity 1112 is positively correlated with the outer diameter size of the magnetic steel 122 and the number of pole pairs of the magnetic steel 122, respectively.

[0081] The pitch of the first flow cavity 1112 refers to the distance between adjacent two same phase points in the first direction X. The pitch of the first flow cavity 1112 reflects the tightness of the first flow cavity 1112 in the first direction X. For example, a smaller pitch means that the spiral is more dense, and the fluid path is longer.

[0082] Exemplarily, the pitch of the first flow cavity 1112 is positively correlated with the outer diameter size of the magnetic steel 122 and the pole pair number of the magnetic steel 122 respectively in a proportional relationship, a linear relationship, a nonlinear relationship, a threshold relationship, or the like.

[0083] The pitch of the first flow cavity 1112 is positively correlated with the outer diameter size of the magnetic steel 122: the smaller the outer diameter of the magnetic steel 122, the smaller the pitch of the first flow cavity 1112; conversely, the larger the outer diameter of the rotor, the larger the pitch of the first flow cavity 1112.

[0084] Specifically, in the spatial distribution of the magnetic field, the pitch of the first flow cavity 1112 needs to be adjusted to adapt to the circumferential distance (half the length of the rotor structure) between the n-pole and the s-pole, in order to reduce the cogging torque. In addition, a smaller outer diameter of the magnetic steel 122 allows the radial size of the motor to be compressed, adapting to the miniaturization and integration scenarios. A smaller pitch of the first flow cavity 1112 may increase the spatial coverage of the fluid in the iron core 111, resulting in better heat dissipation. Conversely, a larger outer diameter of the rotor means that the motor has a larger volume and diameter, and the flow path of the fluid in the first flow cavity 1112 in the iron core 111 will also be correspondingly longer. In order to ensure that the fluid can flow uniformly and effectively through the entire iron core 111, avoiding the formation of fluid stagnation or eddy current in a small space, the pitch of the first flow cavity 1112 needs to be increased to adapt to the longer flow path and larger flow area, so that the fluid can form a more uniform coverage and flow on the entire iron core 111.

[0085] The pitch of the first flow cavity 1112 is positively correlated with the pole pair number of the magnetic steel 122. The more the pole pair number, the larger the pitch of the first flow cavity 1112. The pole pair number is the number of N-poles and S-poles in the motor 10.

[0086] Specifically, the pole pair number of the magnetic steel 122 affects the magnetic field distribution characteristics of the motor. The more the pole pair number, the more complex the rotating magnetic field of the motor, and at the same time, it also means that more magnetic poles are formed on the magnetic steel 122. When the pole pair number of the magnetic steel 122 changes, the electromagnetic characteristics of the motor will change, and a stronger cogging torque will be generated. In order to balance the cogging torque and ensure the smoothness and efficiency of the motor operation, the pitch of the first flow cavity 1112 also needs to be appropriately increased. Adjusting the pitch can change the size ratio of the first flow cavity 1112 in the first direction X, thereby reducing the cogging torque.

[0087] In some optional embodiments of the present application, the pitch of the first flow cavity 1112 is positively correlated with the product of the outer diameter size of the magnetic steel 122 and the pole pair number of the magnetic steel 122.

[0088] In one example, the first flow cavity 1112 has an increased pitch when the outer diameter of the magnetic steel 122 increases and the number of pole pairs of the magnetic steel 122 increases.

[0089] In another example, the first flow cavity 1112 has an increased pitch when the outer diameter of the magnetic steel 122 increases, the number of pole pairs of the magnetic steel 122 decreases, and the product of the outer diameter of the magnetic steel 122 and the number of pole pairs of the magnetic steel 122 increases.

[0090] In another example, the first flow cavity 1112 has an increased pitch when the outer diameter of the magnetic steel 122 decreases, the number of pole pairs of the magnetic steel 122 increases, and the product of the outer diameter of the magnetic steel 122 and the number of pole pairs of the magnetic steel 122 increases.

[0091] In one embodiment of the present application, the pitch of the groove 114 is positively correlated with the outer diameter of the magnetic steel 122 and the number of pole pairs of the magnetic steel 122 when the length of the magnetic steel 122 along the first direction is equal to the length of the winding 115 along the first direction; and the pitch of the groove 114 is positively correlated with the outer diameter of the magnetic steel 122 and the number of pole pairs of the magnetic steel 122 and the length of the winding 115 along the first direction when the length of the magnetic steel 122 along the first direction is less than the length of the winding 115 along the first direction.

[0092] In one example, the pitch of the groove 114 is positively correlated with the length of the winding 115 along the first direction.

[0093] The length of the stator structure 120 exceeding the length of the magnetic steel 122 can expand the effective magnetic field range, ensuring that the magnetic field generated by the magnetic steel 122 is fully cut by the coil, reducing the magnetic circuit leakage phenomenon. For example, by increasing the effective conductor length of the stator structure 120, the electromagnetic force can be enhanced under the same current, thereby improving the motor torque output.

[0094] In the above motor assembly, the winding 115 and other adjacent magnetic conductive structures that exceed the magnetic steel 122 part form a disturbance end to form a local magnetic field under the action of the current, which destroys the symmetry of the original magnetic field and may cause tooth slot torque fluctuation, which is manifested as periodic pulsation of torque output. By determining the pitch of the first flow cavity 1112 according to the outer diameter of the winding 115, the number of pole pairs of the magnetic steel 122, the length of the winding 115 along the first direction, and the length of the magnetic steel 122 along the first direction, the instability of the motor caused by the symmetry of the magnetic field can be balanced, and the smoothness of the motor operation can be improved.

[0095] In some embodiments, the inner core 112 and the outer core 113 are both cylindrical structures, and the inner diameter of the inner circumferential surface of the outer core 113 is greater than the inner diameter of the outer circumferential surface of the inner core 112, that is, the inner core 112 and the outer core 113 are arranged in a gap manner, so that there is a gap between the inner core 112 and the outer core 113 for forming the first flow cavity 1112, and the first flow cavity 1112 is an annular cavity extending along the first direction x.

[0096] The blood pumping device provided by the embodiment increases the cross-sectional area of the first flow cavity 1112 by making the first flow cavity 1112 an annular cavity extending along the first direction x, and since the first flow cavity 1112 is an annular cavity, the connection openings of the first flow cavity 1112 and the first pipeline and the second flow cavity 1113 can be designed at any position on the annular cavity according to actual needs, thereby improving the adaptability of the first flow cavity 1112 and reducing the design difficulty.

[0097] In other embodiments, the core 111 is integrally formed by powder metallurgy, 3D printing or other processes, and the first flow cavity 1112 is naturally formed inside the core 111 during the forming process, or the core 111 is prepared with the first flow cavity 1112 on the core 111 by a processing process after being integrally formed.

[0098] After describing the implementation of the first flow cavity in the blood pumping device, the following will describe several implementations of the second flow cavity in the blood pumping device in combination with the drawings. In combination with FIG. 2, in some embodiments, the winding 115 is at least partially wrapped outside the magnetic steel 122, and the gap between the winding 115 and the rotor assembly 12 forms the second flow cavity 1113.

[0099] In some embodiments, the core 111, the winding 115 and the magnetic steel 122 can be a cylinder or a polygonal cylindrical structure such as a square cylinder. The embodiment is exemplified by taking the core 111, the winding 115 and the magnetic steel 122 as cylinders. The accommodation cavity 1111 is formed by being surrounded by the core 111, and the accommodation cavity 1111 is used to accommodate components such as the winding 115, the magnetic steel 122 and the bearing. The cavity left after removing the positions of the winding 115, the magnetic steel 122 and the bearing in the accommodation cavity 1111 is the second flow cavity 1113. It is easy to understand that when the core 111 is composed of the inner core 112 and the outer core 113, the accommodation cavity 1111 is formed by being surrounded by the inner core 111.

[0100] In some embodiments, the second flow cavity 1113 is also located in the core 111. For example, when the core 111 is integrally formed, the first flow cavity 1112 and the second flow cavity 1113 are both formed by machining the core 111. Alternatively, when the core 111 is composed of an inner core 112 and an outer core 113, the gap between the inner core 112 and the outer core 113 forms the first flow cavity 1112, and the second flow cavity 1113 is formed by machining the inner core 112 and / or the outer core 113. The specific form of the second flow cavity 1113 in the core 111 can refer to the form of the first flow cavity 1112 formed by the groove 114, which will not be described here.

[0101] In some embodiments, the motor 10 further comprises a distal bearing 13 and a proximal bearing 14, both of which are sleeved on the shaft 121. The shaft 121 is rotatably connected to the stator assembly 11 through the distal bearing 13 and the proximal bearing 14, and the distal bearing 13 is located on the side of the proximal bearing 14 away from the first pipe. The first flow cavity 1112 and the second flow cavity 1113 are directly or indirectly communicated through the distal bearing 13, and the second flow cavity 1113 and the second pipe 20 are directly or indirectly communicated through the proximal bearing 14.

[0102] In some embodiments, the distal bearing 13 and the proximal bearing 14 can be sliding bearings or ball bearings. In some implementations, the distal bearing 13 and the proximal bearing 14 are ball bearings, and gaps allowing the perfusion fluid to pass through are provided on the distal bearing 13 and the proximal bearing 14, such as the gaps between the balls. The perfusion fluid flowing from the first flow cavity 1112 to the second flow cavity 1113 can pass through the gaps on the distal bearing 13 and the proximal bearing 14 in sequence and then flow out of the second pipe 20, or the perfusion fluid flowing into the second pipe 20 can pass through the gaps on the proximal bearing 14 and the distal bearing 13 in sequence and then flow out of the first pipe through the first flow cavity 1112. In alternative implementations, the distal bearing 13 and the proximal bearing 14 are sliding bearings, and gaps allowing the perfusion fluid to pass through are formed between the distal bearing 13 and other components (such as a bearing seat) and between the proximal bearing 14 and other components (such as a bearing seat). In alternative implementations, one of the distal bearing 13 and the proximal bearing 14 is a ball bearing, and the other is a sliding bearing, which can be a combination of the first two implementations.

[0103] The blood pumping device provided in the embodiments can carry away the particles generated when the bearings rotate when the perfusion fluid flows through the distal bearing 13 and / or the proximal bearing 14, reducing the pollution of the blood caused by the particles entering the blood.

[0104] FIG. 8 shows a structural schematic diagram of an example proximal end cover; and FIG. 9 shows a structural schematic diagram of an example outer iron core and distal end cover.

[0105] As shown in FIGS. 2, 8 and 9, in some embodiments, the motor 10 further comprises a distal end cover 15 connected to the distal end of the stator assembly 11 and a proximal end cover 16 connected to the proximal end of the stator assembly 11. The distal end cover 15 is provided with a first through hole 151 extending through the distal end cover 15 along the first direction x, and the at least part of the rotating shaft 121 extends out of the first through hole 151 into the accommodation cavity 1111. The proximal end cover 16 is provided with a second through hole 161 extending through the proximal end cover 16 along the first direction x, and the second through hole 161 is used to directly or indirectly connect the second flow passage 1113 and the second pipeline 20. The distal end cover 15 is used to seal the distal end of the accommodation cavity 1111, and the proximal end cover 16 is used to seal the proximal end of the accommodation cavity 1111.

[0106] In some embodiments, the distal end of the distal end cover 15 is in a conical streamline shape, which can serve as a blood flow surface in the working state.

[0107] In some examples, the inner circumferential surface of the distal end cover 15 is in a conical streamline shape, which facilitates the fluid in the first flow passage 1112 to flow into the first through hole 151 and balance the fluid pressure outside the accommodation cavity 1111.

[0108] In some embodiments, the outflow passage 40 in the central chamber auxiliary device is provided with an impeller 42, and the rotating shaft 121 is connected to the impeller 42 after extending out of the first through hole 151 into the accommodation cavity 1111. When the motor 10 is started, the rotating shaft 121 drives the impeller 42 to rotate, and the impeller 42 pumps blood from the suction window to the outflow window 41 and realizes the blood pumping function.

[0109] In some embodiments, the materials of the proximal end cover 16 and the distal end cover 15 include metal and non-metal, and the materials of the proximal end cover 16 and the distal end cover 15 can be the same or different. For example, the materials of the proximal end cover 16 and the distal end cover 15 are both 316 stainless steel.

[0110] FIG. 10 shows a structural schematic diagram of an example distal end bearing seat; and FIG. 11 shows a structural schematic diagram of another example inner iron core and proximal end bearing seat.

[0111] As shown in FIGS. 2, 10 and 11, in some embodiments, the motor 10 further comprises a proximal bearing seat 17 and a distal bearing seat 18. The proximal bearing seat 17 is connected to the proximal end of the stator assembly 11, and the proximal bearing seat 17 is provided with a first mounting hole 171 penetrating the proximal bearing seat 17 along the first direction X of the rotating shaft 121. The proximal bearing 14 and the proximal cover 16 are both embedded in the first mounting hole 171, and the proximal cover 16 is located at the end of the proximal bearing 14 away from the distal bearing 13. The distal bearing seat 18 is connected to the distal end of the stator assembly 11, and the distal bearing seat 18 is provided with a second mounting hole 181 penetrating the distal bearing seat 18 along the first direction X of the rotating shaft 121. The distal bearing 13 is sleeved on the rotating shaft 121 and embedded in the second mounting hole 181.

[0112] It can be understood that the embedding of the proximal bearing 14 in the first mounting hole 171 means that the outer circumferential surface of the proximal bearing 14 is embedded on the circumferential surface of the proximal bearing seat 17 on the side facing the first mounting hole 171 and is fixedly connected. Meanwhile, the inner circumferential surface of the proximal bearing 14 is sleeved on the rotating shaft 121 and is fixedly connected with the rotating shaft 121. The same applies to the distal bearing 13.

[0113] In some embodiments, the distal cover 15 and the distal bearing seat 18 form a gap in the first direction X, and the gap between the distal cover 15 and the distal bearing seat 18 forms a third flow cavity 19. The third flow cavity 19 communicates the first flow cavity 1112 and the second flow cavity 1113 through the distal bearing 13. The two end surfaces of the distal bearing 13 in the first direction X are respectively directed towards the second flow cavity 1113 and the third flow cavity 19.

[0114] The radial dimension of the first through hole 151 is slightly larger than the radial dimension of the rotating shaft 121, and a gap is formed between the first through hole 151 and the rotating shaft 121. This allows the perfusion liquid in the third flow cavity 19 to flow into and out of the passage 40 through the gap between the first through hole 151 and the rotating shaft 121 on the distal cover 15, or to flow into the second flow cavity 1113 through the gap between the balls on the distal bearing 13. The radial dimension of the first through hole 151 can be used to control the flow direction of most of the perfusion liquid to the distal bearing 13, and a small part of the perfusion liquid is used to balance the pressure difference between the outflow passage 40 and the third flow cavity 19, reduce the total amount of blood flowing into the motor 10 at the outflow passage 40, and reduce the probability of blood clots in the motor 10.

[0115] In some embodiments, the first conduit is a perfusion conduit, and the second conduit 20 is a backflow conduit. The perfusion liquid of the first conduit flows through the first flow cavity 1112, the third flow cavity 19, the distal end bearing 13, the second flow cavity 1113, and the proximal end bearing 14 in sequence, and then flows out of the motor 10 through the second conduit 20.

[0116] The blood pumping device provided by the embodiment can effectively reduce the particles generated when the motor 10 is running from entering the human body, reduce the total amount of perfusion liquid flowing into the patient, and further reduce the total amount of particles flowing into the patient, thereby improving the safety of the product. By making the first conduit a perfusion conduit and the second conduit 20 a backflow conduit, the perfusion liquid first enters the third flow cavity 19 from the first flow cavity 1112, and then flushes the bearings before flowing out from the second conduit 20, so that the content of particles in the perfusion liquid at the third flow cavity 19 is extremely low, thereby reducing the total amount of particles flowing into the patient from the first through hole 151.

[0117] In some embodiments, the circumferential surface of the distal end bearing seat 18 facing the second mounting hole 181 includes a fifth step surface 182 and a sixth step surface 183, and the fifth step surface 182 is located on the side of the sixth step surface 183 away from the proximal end bearing seat 17. The radial dimension of the fifth step surface 182 is smaller than the radial dimension of the sixth step surface 183, and the distal end bearing 13 is embedded in the sixth step surface 183. There is a gap between the second mounting hole 181 and the shaft, and the perfusion liquid in the third flow cavity 19 first flows through the gap between the second mounting hole 181 and the shaft where the fifth step surface 182 is located, and then flows into the second flow cavity 1113 through the distal end bearing 13.

[0118] The blood pumping device provided by the embodiment makes the radial dimension of the fifth step surface 182 smaller than the radial dimension of the sixth step surface 183, so that the side wall of the fifth step surface 182 facing the sixth step surface 183 abuts against the distal end bearing 13, thereby limiting the movement of the distal end bearing 13 in the first direction x, and further improving the connection stability of the distal end bearing 13 and the distal end bearing seat 18.

[0119] FIG. 12 shows a cross-sectional structural schematic view of the inner core and the proximal end bearing seat in FIG. 11.

[0120] As shown in FIGS. 2, 11, and 12, in some embodiments, the proximal end bearing seat 17 is further provided with a first communication hole 172, and the first communication hole 172 directly or indirectly communicates the first flow cavity 1112 and the first conduit.

[0121] In some embodiments, the connection between the first conduit and the proximal end bearing seat 17, and the connection between the second conduit 20 and the proximal end cover 16 can be welded, glued, or sealed by other sealing methods.

[0122] Figure 13 shows a structural schematic diagram of an example second pipe.

[0123] As shown in Figure 13, in some embodiments, the first pipe and the second pipe 20 can be straight tubes or other special-shaped tubes, which are not limited in the present application. In addition, for the return pipe, the proximal end of the return pipe is provided with a notch 21, and the number of notches 21 can be at least one. When the number of notches 21 is more than two, the plurality of notches 21 are symmetrically or asymmetrically arranged along the circumference. The notch 21 is used to connect with the support wire (not shown) located at least partially in the return pipe. After the support wire is embedded in the notch 21, the support wire is connected with the return pipe at the embedded position by laser welding or gluing, further improving the connection strength of the return pipe and the motor 10.

[0124] In some embodiments, one of the openings of the first communication hole 172 is located on the end face of the proximal bearing seat 17 away from the distal bearing seat 18 and communicates with the first pipe, and the other opening is located on the circumferential face of the proximal bearing seat 17 away from the first mounting hole 171 and communicates with the first flow cavity 1112.

[0125] In some embodiments, the distal cover 15 and the outer iron core 113 can be separately prepared and then connected by welding, gluing or other processes, or the distal cover 15 and the outer iron core 113 can be integrally formed. The proximal bearing seat 17 and the inner iron core 112 can be separately prepared and then connected by welding, gluing or other processes, or the proximal bearing seat 17 and the inner iron core 112 can be integrally formed. When the proximal bearing seat 17 and the inner iron core 112 are separately prepared and then connected, the proximal end of the inner iron core 112 abuts against the distal end face of the proximal bearing seat 17, and then the connection position is connected by welding, gluing or other processes. The distal cover 15 and the outer iron core 113 are the same.

[0126] As shown in Figures 2 and 3, in some embodiments, the circumferential face of the inner iron core 112 towards the outer iron core 113 includes a first step face 1121 and a second step face 1122, the first step face 1121 is located at the distal end of the inner iron core 112, and the second step face 1122 is located at the proximal end of the inner iron core 112. The radial dimension of the first step face 1121 is smaller than the radial dimension of the second step face 1122. The circumferential face of the proximal bearing seat 17 away from the first mounting hole 171 includes a third step face 173 and a fourth step face 174, the third step face 173 is located at the side of the fourth step face 174 close to the inner iron core 112, the radial dimension of the third step face 173 is smaller than the radial dimension of the fourth step face 174, and the radial dimension of the third step face 173 is smaller than the radial dimension of the second step face 1122. One of the openings of the first communication hole 172 is located on the third step face 173.

[0127] The distal end cover 15 is lapped on the first step surface 1121, and the outflow channel 40 is lapped on the circumferential surface of the distal end cover 15 away from the first step surface 1121. By making the radial dimension of the first step surface 1121 smaller than the radial dimension of the second step surface 1122, the radial dimension of the lapped part of the distal end cover 15 and the inner core 112 and the lapped part of the distal end cover 15 and the outflow channel 40 is effectively reduced, thereby reducing the difficulty of intervention of the motor 10 and the blood pumping device.

[0128] In some embodiments, the radial dimension of the third step surface 173 is smaller than the radial dimension of the fourth step surface 174, and the radial dimension of the third step surface 173 is smaller than the radial dimension of the second step surface 1122, so that an annular groove is formed at the third step surface 173, which is concave inwardly along the axis of the rotating shaft 121 and surrounds the axis. The annular groove is in communication with the third flow cavity 19. When the inner core 112 is provided with the groove 114, the groove 114 extends from the first step surface 1121 to the second step surface 1122 and is in communication with the annular groove formed by the third step surface 173. The groove 114 is in communication with the third flow cavity 19 at the first step surface 1121, and the groove 114 is in communication with the first pipeline through the first communication hole 172 at the third step surface 173. By making one of the openings of the first communication hole 172 located at the third step surface 173, the perfusion solution in the first pipeline can flow into the annular groove formed by the third step surface 173 through the first communication hole 172 and continue to flow into the first flow cavity 1112 formed by the groove 114. The annular groove formed by the third step surface 173 can make it unnecessary to provide multiple first communication holes 172 to be in communication with each of the multiple first flow cavities 1112, but only need to make the multiple first flow cavities 1112 in communication with the annular groove formed by the third step surface 173. The proximal end of the outer core 113 is sleeved outside the fourth step surface 174, and the fourth step surface 174 abuts against the inner circumferential surface of the outer core 113, i.e., the fourth step surface 174 is embedded in the outer core 113. By making the fourth step surface 174 abut against the inner circumferential surface of the outer core 113, the outer core 113 seals the annular groove formed at the third step surface 173, thereby making the annular groove have only two outlets, i.e., the groove 114 and the first communication hole 172.

[0129] In some embodiments, the inner core 112 is connected with the proximal bearing seat 17, and the third fourth step surface 174 on the proximal bearing seat 17 is connected with the outer core 113. It can also be understood that the outer core 113 is connected with the inner core 112 through the proximal bearing seat 17, and the outer core 113 is sleeved outside the inner core 112, and there is a gap between the outer core 113 and the inner core 112 for forming the first flow-through cavity 1112.

[0130] In some embodiments, the motor 10 further comprises a shell (not shown) sleeved outside the core 111, and at least part of the shell is attached to the second step surface 1122.

[0131] It can be understood that the components of the above-mentioned blood pumping device that come into contact with the human body and blood need to be made of biologically safe materials, which can be metal or non-metal. For example, when these components are metal, they can be made of 316 stainless steel. In other embodiments, the core 111 can also be used as the shell of the motor 10 to directly contact the patient's tissue, so that the motor 10 does not need to be additionally provided with a shell, thereby reducing the diameter of the motor 10 and the difficulty of intervention.

[0132] It can be understood that the above-mentioned embodiments are introduced respectively, and in fact, each component can be integrally formed. For example, the inner core 112 and the proximal bearing seat 17 are integrally formed, and for another example, the outer core 113 and the distal cover 15 are integrally formed, and for another example, the inner core 112 and the outer core 113 are integrally formed, and for another example, the inner core 112 and the distal bearing seat 18 are integrally formed. The above are only some examples of integral forming, and are not all integral forming schemes. As long as the combination scheme can meet the processing requirements and performance requirements, it is within the protection scope of the present application.

[0133] In some alternative embodiments, the present application also provides a liquid pumping device for delivering other body fluids except blood, which comprises a motor 10, a first pipeline and a second pipeline 20. The motor 10 comprises a stator assembly 11, the stator assembly 11 comprises a core 111, the core 111 encloses a containing cavity 1111, the core 111 is provided with a first flow-through cavity 1112, and the core 111 and / or the containing cavity 1111 is provided with a second flow-through cavity 1113 in communication with the first flow-through cavity 1112. The first pipeline is in communication with the first flow-through cavity 1112, and the second pipeline 20 is in communication with the second flow-through cavity 1113. One of the first pipeline and the second pipeline 20 is a perfusion pipeline, and the other is a backflow pipeline. The perfusion pipeline is used for delivering perfusion liquid to the motor 10, and the backflow pipeline is used for discharging the perfusion liquid in the motor 10.

[0134] In some embodiments, the body fluid includes tissue fluid, digestive fluid, etc.

[0135] The structure of the pump liquid device is referred to the pump blood device, and the same technical effects can be achieved, which will not be described in detail.

[0136] In addition, the application further provides an electric machine, which comprises a stator assembly, the stator assembly comprises a core, the core encloses a containing cavity, the core is provided with a first flow cavity, and the core and / or the containing cavity is provided with a second flow cavity which is communicated with the first flow cavity. One of the first flow cavity and the second flow cavity is used for being communicated with a perfusion pipeline, and the other is used for being communicated with a backflow pipeline. The perfusion pipeline is used for conveying perfusion liquid into the electric machine, and the backflow pipeline is used for discharging the perfusion liquid in the electric machine.

[0137] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will not be described repeatedly.

[0138] It can be understood that the electric machine provided by the application can be the electric machine in any one of the pump blood device and the pump liquid device, which will

Claims

1. A blood pumping device for transporting blood, wherein, The motor comprises a stator assembly, the stator assembly comprises a core, the core encloses a receiving cavity, the core is provided with a first flow cavity, and the core and / or the receiving cavity is provided with a second flow cavity in communication with the first flow cavity. A first pipeline is in communication with the first flow cavity. A second pipeline is in communication with the second flow cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, and the other is a backflow pipeline, the perfusion pipeline is used to deliver perfusion fluid to the motor, and the backflow pipeline is used to discharge the perfusion fluid in the motor. The first flow cavity is a strip-shaped cavity extending along a first direction, wherein the first direction is a direction in which a distal end of the motor points to a proximal end.

2. The blood pumping device of claim 1, wherein, The core comprises an inner core and an outer core sleeved outside the inner core, and an outer peripheral surface of the inner core is fitted with an inner peripheral surface of the outer core.

3. The blood pumping device of claim 2, wherein, The outer peripheral surface of the inner core is provided with a groove, and the first flow cavity is formed between the groove and the outer core. Or, the inner peripheral surface of the outer core is provided with a groove, and the first flow cavity is formed between the groove and the inner core. Or, the outer peripheral surface of the inner core and the inner peripheral surface of the outer core are both provided with grooves, and the first flow cavity is formed between the grooves on the inner core and the outer core. The first flow cavity spirally extends in the core along the first direction.

4. The blood pumping device of claim 2 or 3, wherein, The motor further comprises a rotor assembly, the rotor assembly comprises a rotating shaft and a magnetic steel, the rotating shaft extends along the first direction, at least part of the rotating shaft is located in the receiving cavity, and the magnetic steel is located in the receiving cavity and sleeved on the rotating shaft.

5. The blood pumping device of claim 4, wherein, The magnetic steel has a pole pair number P, the first flow cavity spirally surrounds the rotating shaft, and a single first flow cavity has a winding number T=1 / P or T=1 / (2P). The stator assembly further comprises a winding located in the receiving cavity, the winding is sleeved outside the magnetic steel, and a gap between the winding and the rotor assembly forms the second flow cavity.

6. The blood pumping device of claim 5, wherein, The length of the winding in the first direction is L: when the winding number T of the first flow cavity is 1 / P, the pitch H of the first flow cavity is PL; and when the winding number T of the first flow cavity is 1 / (2P), the pitch H of the first flow cavity is 2PL. The motor further comprises:

7. The blood pumping device of claim 5, wherein, A distal end bearing sleeved on the rotating shaft, the distal end bearing is in communication with the first flow cavity and the second flow cavity; A proximal end bearing sleeved on the rotating shaft, the rotating shaft is rotationally connected with the stator assembly through the distal end bearing and the proximal end bearing, and the distal end bearing is located on a side of the proximal end bearing away from the first pipeline; A distal end cover connected with a distal end of the stator assembly, the distal end cover is provided with a first through hole penetrating through the distal end cover along the first direction, at least part of the rotating shaft extends out of the receiving cavity from the first through hole, the distal end cover is used to seal a distal end of the receiving cavity, a third flow cavity is formed between the distal end cover and the distal end bearing, and the third flow cavity is in communication with the first flow cavity and the second flow cavity through the distal end bearing. ​ A proximal end cover is connected to the proximal end of the stator assembly, and is used to seal the proximal end of the accommodating cavity. The proximal end cover is provided with a second through hole penetrating the proximal end cover along the first direction, and the second through hole is used to communicate the second flow-through cavity and the second pipeline.

8. The blood pumping device of claim 7, wherein, The motor further comprises: A proximal end bearing seat is connected to the proximal end of the stator assembly. The proximal end bearing seat is provided with a first mounting hole penetrating the proximal end bearing seat along the first direction. The proximal end bearing and the proximal end cover are both embedded in the first mounting hole. The proximal end cover is located at the end of the proximal end bearing away from the distal end bearing. A distal end bearing seat is connected to the distal end of the stator assembly. The distal end bearing seat is provided with a second mounting hole penetrating the distal end bearing seat along the first direction. The distal end bearing is embedded in the second mounting hole.

9. The blood pumping device of claim 8, wherein, The distal end cover and the distal end bearing seat have a gap in the first direction. The gap between the distal end cover and the distal end bearing seat forms a third flow-through cavity. The third flow-through cavity communicates the first flow-through cavity and the second flow-through cavity.

10. The blood pumping device of claim 7, wherein, The first pipeline is a perfusion pipeline, and the second pipeline is a backflow pipeline.

11. The blood pumping device of claim 8, wherein, The proximal end bearing seat is further provided with a first communication hole. The first communication hole communicates the first flow-through cavity and the first pipeline.

12. The blood pumping device of claim 11, wherein, One of the openings of the first communication hole is located on the end face of the proximal end bearing seat away from the distal end bearing seat and communicates the first pipeline. The other opening is located on the circumferential face of the proximal end bearing seat away from the first mounting hole and communicates the first flow-through cavity.

13. The blood pumping device of claim 1, wherein, The motor further comprises a rotor assembly. The rotor assembly comprises a rotating shaft and a magnetic steel. The rotating shaft extends along the first direction. At least part of the rotating shaft is located in the accommodating cavity. The magnetic steel is located in the accommodating cavity and is sleeved on the rotating shaft. The pitch of the first flow-through cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively.

14. The blood pumping device of claim 13, wherein, The stator assembly further comprises a winding located in the accommodating cavity. The winding is sleeved outside the magnetic steel. The gap between the winding and the rotor assembly forms the second flow-through cavity. In the case that the length of the magnetic steel along the first direction is equal to the length of the winding along the first direction, the pitch of the first flow-through cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively. In the case that the length of the magnetic steel along the first direction is less than the length of the winding along the first direction, the pitch of the first flow-through cavity is positively correlated with the outer diameter of the magnetic steel and the pole pair number of the magnetic steel, respectively. The pitch of the first flow-through cavity is positively correlated with the length of the winding along the first direction.

15. The blood pumping device of claim 1, wherein, The iron core comprises an inner iron core and an outer iron core sleeved outside the inner iron core. The outer iron core is gap-set with the inner iron core. The gap between the inner iron core and the outer iron core forms the first flow-through cavity.

16. An electric machine, wherein, The pump blood device comprises a stator assembly, the stator assembly comprises a core, the core encloses a containing cavity, the core is provided with a first flow cavity, the core and / or the containing cavity is provided with a second flow cavity in communication with the first flow cavity, one of the first flow cavity and the second flow cavity is used for communicating with a perfusion pipeline, and the other is used for communicating with a backflow pipeline.

17. A ventricular assist device, wherein, The pump blood device, the outflow channel and the interventional catheter are provided by the application, the interventional catheter is connected with the proximal end of the pump blood device, the outflow channel is connected with the distal end of the pump blood device, and the outflow channel is provided with the suction window and the outflow window.

Images