Blood pumping device and motor

Abstract

The invention discloses a blood pumping device and a motor, the blood pumping device is used for conveying blood, the blood pumping device comprises the motor, a first pipeline and a second pipeline, the motor comprises a stator assembly, the stator assembly comprises an iron core, the iron core defines a containing cavity, and a first circulation cavity is formed in the iron core; a second circulation cavity communicated with the first circulation cavity is formed in the iron core and / or the accommodating cavity; the first pipeline is communicated with the first circulation cavity; one of the first pipeline and the second pipeline is a perfusion pipeline, the other one of the first pipeline and the second pipeline is a backflow pipeline, the perfusion pipeline is used for conveying perfusion liquid to the motor, and the backflow pipeline is used for discharging the perfusion liquid in the motor.

Description

Technical Field

[0001] This application belongs to the technical field of medical devices, and particularly relates to a blood pumping device and a motor. Background Art

[0002] During cardiac surgery, due to the patient's own diseases or surgical needs, the patient's heart function weakens and the blood pumping ability is insufficient. At this time, an active interventional medical device such as a ventricular assist device needs to be inserted into the heart to assist the heart in pumping blood. The existing ventricular assist device utilizes the principle of cardiac blood pumping, pumps the blood in the heart out through a pumping mechanism, and diverts the blood to the aorta outside the heart to flow to the whole body.

[0003] 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 of the catheter (the end far from the operator or physician). The blood pumping device can be inserted through the femoral artery, axillary artery or carotid artery by the pushing of 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, realizing the blood pumping function of the ventricular assist device. Similarly, the blood pumping device can also be inserted through veins such as the femoral vein by the pushing of the catheter. When the blood pumping device is operating, it will generate heat, and if the heat of the blood pumping device is too high, it will cause damage to the patient. Summary of the Invention

[0004] The embodiments of this application provide a blood pumping device, which can improve the effective heat dissipation of the blood pumping device and the motor.

[0005] The embodiments of this application provide a blood pumping device for transporting blood. The blood pumping device includes a motor, a first pipeline and a second pipeline. The motor includes a stator assembly. The stator assembly includes an iron core. The iron core encloses to form a receiving cavity. A first flow cavity is arranged in the iron core. A second flow cavity communicating with the first flow cavity is arranged in and / or in the receiving cavity of the iron core; the first pipeline communicates with the first flow cavity; the second pipeline communicates with the second flow cavity. One of the first pipeline and the second pipeline is an infusion pipeline, and the other is a return pipeline. The infusion pipeline is used to transport infusion fluid to the motor, and the return pipeline is used to discharge the infusion fluid in the motor.

[0006] The first flow cavity is a strip-shaped cavity extending along a first direction, where the first direction is the direction from the distal end to the proximal end of the motor.

[0007] According to the implementation scheme of the first aspect of the present application, the iron core includes an inner iron core and an outer iron core sleeved outside the inner iron core, and the outer circumferential surface of the inner iron core is in contact with the inner circumferential surface of the outer iron core: a groove is provided on the circumferential surface of the inner iron core facing the outer iron core, and the gap between the groove and the outer iron core forms a first flow cavity; or, a groove is provided on the circumferential surface of the outer iron core facing the inner iron core, and the gap between the groove and the inner iron core forms the first flow cavity; or, grooves are provided on the circumferential surface of the inner iron core facing the outer iron core and the circumferential surface of the outer iron core facing the inner iron core, and a first flow cavity is formed between the groove on the inner iron core and the groove on the outer iron core.

[0008] According to an embodiment of the first aspect of the present application, the first flow chamber extends spirally in the iron core along a first direction.

[0009] According to an implementation scheme of the first aspect of the present application, the motor further includes a rotor assembly, the rotor assembly includes a rotating shaft and a magnet, the rotating shaft extends along a first direction, at least a portion of the rotating shaft is located in the accommodating cavity, the magnet is located in the accommodating cavity and is sleeved on the rotating shaft; the number of pole pairs of the magnet is P, the first circulation cavity is spirally wound around the rotating shaft and the number of windings of a single first circulation cavity is T=1 / P or T=1 / (2P).

[0010] According to an implementation scheme of the first aspect of the present application, the stator assembly also includes a winding located in the accommodating cavity, the winding is sleeved outside the magnetic steel, and the gap between the winding and the rotor assembly forms a second circulation cavity; the length of the winding in the first direction is L: when the number of turns of the first circulation cavity is T=1 / P, the pitch of the first circulation cavity is H=PL; when the number of turns of the first circulation cavity is T=1 / (2P), the pitch of the first circulation cavity is H=2PL.

[0011] According to an implementation scheme of the first aspect of the present application, the motor further includes: a distal bearing, which is sleeved on the rotating shaft, and the distal bearing connects the first circulation chamber and the second circulation chamber; a proximal bearing, which is sleeved on the rotating shaft, and the rotating shaft is rotatably connected to the stator assembly through the distal bearing and the proximal bearing, and the distal bearing is located on the side of the proximal bearing away from the first pipe; a distal cover, which is connected to the distal end of the stator assembly, and the distal cover is provided with a first through hole that penetrates the distal cover along a first direction, at least a portion of the rotating shaft extends out of the accommodating chamber from the first through hole, and the distal cover is used to seal the distal end of the accommodating chamber; a proximal cover, which is connected to the proximal end of the stator assembly, and the proximal cover is used to seal the proximal end of the accommodating chamber, and the proximal cover is provided with a second through hole that penetrates the distal cover along the first direction, and the second through hole is used to connect the second circulation chamber with the second pipe.

[0012] According to an embodiment of the first aspect of the present application, the motor further includes: a proximal bearing housing, which is connected to the proximal end of the stator assembly. The proximal bearing housing is provided with a first mounting hole penetrating through the proximal bearing housing in a first direction. Both the proximal bearing and the proximal end cover are embedded in the first mounting hole, and the proximal end cover is located at an end of the proximal bearing away from the distal bearing; a distal bearing housing, which is connected to the distal end of the stator assembly. The distal bearing housing is provided with a second mounting hole penetrating through the distal bearing housing in the first direction, and the distal bearing is embedded in the second mounting hole.

[0013] According to an embodiment of the first aspect of the present application, there is a gap between the distal end cover and the distal bearing housing in the first direction, and the gap between the distal end cover and the distal bearing housing forms a third flow cavity, and the third flow cavity communicates with the first flow cavity and the second flow cavity.

[0014] According to an embodiment of the first aspect of the present application, the first pipe is a perfusion pipe, and the second pipe is a reflux pipe.

[0015] According to an embodiment of the first aspect of the present application, the proximal bearing housing is further provided with a first communication hole, and the first communication hole communicates the first flow cavity and the first pipe.

[0016] According to an embodiment of the first aspect of the present application, one opening of the first communication hole is located on the end face of the proximal bearing housing on the side away from the distal bearing housing and communicates with the first pipe, and the other opening is located on the circumferential surface of the proximal bearing housing away from the first mounting hole and communicates with the first flow cavity.

[0017] According to an embodiment of the first aspect of the present application, the iron core includes an inner iron core and an outer iron core sleeved outside the inner iron core. The outer iron core and the inner iron core are arranged with a gap therebetween, and the gap between the inner iron core and the outer iron core forms a first flow cavity.

[0018] A second aspect of the present application provides a motor, including a stator assembly. The stator assembly includes an iron core. The iron core encloses to form an accommodation cavity. A first flow cavity is provided in the iron core, and a second flow cavity communicating with the first flow cavity is provided in and / or in the accommodation cavity of the iron core. One of the first flow cavity and the second flow cavity is used to communicate with a perfusion pipe, and the other is used to communicate with a reflux pipe.

[0019] It can be understood that the motor provided in the second aspect of the present application can be any one of the motors in the blood pumping device provided in the first aspect of the present application, and will not be described repeatedly here. This motor can be used in various application scenarios such as pumping blood, pumping tissue fluid, and pumping digestive fluid.

[0020] The blood pumping device according to an embodiment of the present application includes a motor, a first pipeline, and a second pipeline. The motor includes a stator assembly, and the stator assembly includes an iron core. The iron core encloses to form a receiving cavity. A first flow cavity is provided inside the iron core, and a second flow cavity communicating with the first flow cavity is provided inside and / or within the receiving cavity of the iron core. The first pipeline communicates with the first flow cavity, and the second pipeline communicates with the second flow cavity. One of the first pipeline and the second pipeline is an infusion pipeline, and the other is a return pipeline. The infusion pipeline is used to convey infusion liquid to the motor, and the return pipeline is used to discharge the infusion liquid inside the motor. In the present application, the first pipeline and the second pipeline are internally connected to the motor. The infusion liquid flows through one of the pipelines to the motor, then flows through the first flow cavity and the second flow cavity, and takes 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 reducing the damage to the patient caused by the blood pumping device. By providing a first flow cavity communicating with the first pipeline inside the iron core, there is no need to additionally provide a pipeline outside the motor, reducing the outer diameter of the motor, and thus reducing the intervention difficulty. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] 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 below. For those of ordinary skill in the art, other drawings can also be obtained based on these drawings without creative efforts.

[0022] Figure 1 Structural schematic diagram of a ventricular assist device including a blood pumping device according to some embodiments of the present application;

[0023] Figure 2 Showing an example of Figure 1 Longitudinal sectional structural schematic diagram of the ventricular assist device in

[0024] Figure 3 Structural schematic diagram showing an example of an inner iron core and a proximal bearing seat;

[0025] Figure 4 Showing an example of Figure 3 Perspective structural schematic diagram of the inner iron core and the proximal bearing seat in

[0026] Figure 5 Showing an example of Figure 2 Cross-sectional structural schematic diagram of the ventricular assist device in at the A-A position;

[0027] Figure 6 Showing another example of Figure 2 Cross-sectional structural schematic diagram of the ventricular assist device in at the A-A position;

[0028] Figure 7 Showing yet another example of Figure 2Schematic cross-sectional structure diagram of the ventricular assist device at the A-A position; Figure 8 Schematic structure diagram showing an example of a proximal cap;

[0029] Figure 9 Schematic structure diagram showing an example of an outer iron core and a distal cap;

[0030] Figure 10 Schematic structure diagram showing an example of a distal bearing housing;

[0031] Figure 11 Schematic structure diagram showing another example of an inner iron core and a proximal bearing housing;

[0032] Figure 12 Schematic showing an example of Figure 11 Cross-sectional structure diagram of the inner iron core and the proximal bearing housing in

[0033] Figure 13 Schematic structure diagram showing an example of a second conduit.

[0034] Reference numerals:

[0035] 10. Motor; 11. Stator assembly; 111. Iron core; 1111. Accommodation cavity; 1112. First flow cavity; 1113. Second flow cavity; 112. Inner iron core; 1121. First step surface; 1122. Second step surface; 113. Outer iron core; 114. Groove; 115. Winding; 12. Rotor assembly; 121. Rotating shaft; 122. Permanent magnet; 13. Distal bearing; 14. Proximal bearing; 15. Distal cap; 151. First through hole; 16. Proximal cap; 161. Second through hole; 17. Proximal bearing housing; 171. First mounting hole; 172. First communication hole; 173. Third step surface; 174. Fourth step surface; 18. Distal bearing housing; 181. Second mounting hole; 182. Fifth step surface; 183. Sixth step surface; 19. Third flow cavity;

[0036] 20. Second conduit; 21. Notch;

[0037] 30. Intervention catheter;

[0038] 40. Outflow channel; 41. Outflow window; 42. Impeller;

[0039] x. First direction. Detailed implementation manners

[0040] The features and exemplary embodiments of various aspects of the present application will be described in detail below. To make the objectives, technical solutions, and advantages of the present application clearer and more understandable, the present application will be further described in detail below in conjunction with the accompanying drawings and specific embodiments. It should be understood that the specific embodiments described herein are only intended to explain the present application and not to limit the present application. For those skilled in the art, the present application can be implemented without some of these specific details. The following description of the embodiments is only intended to provide a better understanding of the present application by showing examples of the present application.

[0041] It should be noted that, in this document, relational terms such as "first" and "second" are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any actual relationship or order between these entities or operations. Moreover, the term "comprising", "including" or any other variation thereof is intended to cover a non-exclusive inclusion, such that a process, method, article or device comprising a series of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article or device. Without further limitation, an element defined by the statement "comprising..." does not exclude the presence of additional identical elements in the process, method, article or device comprising the element.

[0042] To solve the technical problems involved in the background art, the applicant proposes a blood pumping device, which includes a motor, a first pipe and a second pipe. The motor includes a stator assembly, and the stator assembly includes an iron core. The iron core encloses to form a receiving cavity, and a first flow cavity is provided in the iron core. A second flow cavity communicating with the first flow cavity is provided in the iron core and / or in the receiving cavity; the first pipe communicates with the first flow cavity; the second pipe communicates with the second flow cavity. One of the first pipe and the second pipe is an infusion pipe, and the other is a return pipe. The infusion pipe is used to convey perfusion fluid to the motor, and the return pipe is used to discharge the perfusion fluid in the motor.

[0043] The blood pumping device provided by the present application internally communicates with the motor through the first pipe and the second pipe. The perfusion fluid flows through one of the pipes to the motor, then flows through the first flow cavity and the second flow cavity and takes away the heat generated by the motor, and then flows out from the other pipe, 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 a first flow cavity communicating with the first pipe in the iron core, there is no need to additionally provide a pipeline outside the motor, reducing the outer diameter of the motor, and thus reducing the intervention difficulty.

[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 fluids such as blood, tissue fluid, digestive fluid, etc. For the convenience of understanding and description, the following will continue to describe by taking the application scenario where the motor is applied in the blood pumping device as an example.

[0045] Before describing the specific structure of the blood pumping device, the ventricular assist device including the blood pumping device will be briefly described with reference to the accompanying drawings to facilitate understanding of the working environment of the blood pumping device. Figure 1 It is a schematic structural diagram of a ventricular assist device including a blood pumping device according to some embodiments of the present application. Figure 2 Shows an example of Figure 1 The longitudinal sectional structural schematic diagram of the ventricular assist device in, where the first pipeline is not drawn. Combining Figure 1 and Figure 2 It can be known that the present application provides a ventricular assist device including a blood pumping device. The ventricular assist device includes a blood pumping device (not labeled), an outflow channel 40, and an intervention catheter 30. 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 includes a motor 10. An inhalation window (not drawn) and an outflow window 41 are provided on the outflow channel 40. During use, the blood pumping device and the outflow channel 40 rely on the push of the intervention catheter 30 to pass through the patient's blood vessels until the blood pumping device and the outflow channel 40 are located at the designated positions in the patient's blood circulation system. At this time, the outflow window 41 and the inhalation window are located at different positions in the blood circulation system. When the motor 10 in the blood pumping device is started, the motor 10 drives the blood to enter the outflow channel 40 from the inhalation window and flow out from 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 are inserted into 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 devices such as a liquid storage tank (not drawn), a power supply device, and a control switch. At least part of the first pipeline and the second pipeline 20 are located in the intervention catheter 30. The liquid storage tank transports and discharges the perfusion liquid into the motor through the pipeline. The perfusion liquid flows through the motor 10 and takes away the heat generated during the operation of the motor 10. Among them, the perfusion liquid includes physiological saline and anticoagulant, and the anticoagulant can be heparin. The anticoagulant in the perfusion liquid reduces the probability of blood coagulation, and further reduces the probability of the blood pumping function failure of the motor 10 caused by blood coagulation.

[0047] It can be understood that in the present application, the proximal end refers to the end facing 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 will be introduced below with reference to the accompanying drawings. It should be noted here that the drawings extend along the connection line between the proximal end and the distal end of the motor, and the direction from the distal end to the proximal end is the first direction, denoted as x. In the drawings, for the convenience of drawing, the dimensions in the drawings are not necessarily proportional to the actual dimensions.

[0049] Combined with Figure 1 and Figure 2 it can be seen that the present application provides a blood pumping device for transporting blood. The blood pumping device includes a motor 10, a first pipeline (not shown), and a second pipeline 20. The motor 10 includes a stator assembly 11. The stator assembly 11 includes an iron core 111. The iron core 111 encloses to form a receiving cavity 1111. A first flow cavity 1112 is provided in the iron core 111. A second flow cavity 1113 communicating with the first flow cavity 1112 is provided in and / or within the receiving cavity 1111 of the iron core 111. It can be understood that providing the first flow cavity 1112 in the iron core 111 means that a cavity or a gap is formed in the solid structure of the iron core 111 to form the first flow cavity 1112. The first pipeline communicates with the first flow cavity 1112; the second pipeline 20 communicates with the second flow cavity 1113. One of the first pipeline and the second pipeline 20 is a perfusion pipeline, and the other is a return pipeline. Among them, the perfusion pipeline is used to transport perfusion fluid to the motor 10, and the return pipeline is used to discharge the perfusion fluid in the motor 10.

[0050] In some implementation manners, the wall surface of the first flow cavity 1112 has high smoothness and low roughness, and the wall surface of the first flow cavity 1112 is treated with a hydrophilic coating.

[0051] It can be understood that the layout manner of the second flow cavity 1113 in and / or within the receiving cavity 1111 of the iron core 111 in the present application will be described in detail below and will not be elaborated here.

[0052] In some embodiments, the first flow cavity 1112 and the second flow cavity 1113 are directly or indirectly connected. Indirect connection means that the first flow cavity 1112 and the second flow cavity 1113 are connected through at least one other cavity, gap, or spatial structure. This embodiment describes the application scenario where the first flow cavity 1112 and the second flow cavity 1113 are indirectly connected.

[0053] The blood pumping device provided in this embodiment is connected to the motor 10 through the first pipeline and the second pipeline 20. The perfusion fluid flows through one of the pipelines to the motor 10, then passes through the first flow chamber 1112 and the second flow chamber 1113 and takes 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 chamber 1112 communicating with the first pipeline inside the iron core 111, there is no need to provide an additional pipeline outside the motor, reducing the outer diameter of the motor 10, and thus reducing the intervention difficulty.

[0054] After describing the overall structure of the blood pumping device, several implementation manners of the first flow chamber in the blood pumping device will be described below with reference to the drawings. In some embodiments, the first flow chamber 1112 is a strip-shaped chamber extending along the first direction x. The first direction x is the direction from the distal end to the proximal end of the motor 10.

[0055] It can be understood that in this application, the first flow chamber 1112 being a strip-shaped chamber extending along the first direction x does not mean that the first flow chamber 1112 is a linear cavity, and the center line of the linear cavity is a straight line parallel to the first direction x. Instead, it means that the first flow chamber 1112 has opposite ends, and one end faces the proximal side and the other end faces the distal side, but the trajectory of the extension of one end of the first flow chamber 112 to the other end is not specifically limited.

[0056] Combined with Figure 2 It can be seen that in some embodiments, the iron core 111 includes an inner iron core 112 and an outer iron core 113 sleeved outside the inner iron core 112. The outer peripheral surface of the inner iron core 112 is in contact with the inner peripheral surface of the outer iron core 113. The gap between the inner iron core 112 and the outer iron core 113 forms the first flow chamber 1112, and the inner iron core 112 encloses to form an accommodation chamber 1111.

[0057] In some embodiments, the inner iron core 112 and the outer iron core 113 can be cylinders, or can be polygonal cylinder structures such as square cylinders. In this embodiment, the inner iron core 112 and the outer iron core 113 are both cylinders as an example for illustration.

[0058] It should be noted that since both the inner iron core 112 and the outer iron core 113 are axisymmetric figures, both the inner iron core 112 and the outer iron core 113 have a central axis, and the direction in which the central axis extends is consistent with the direction of the line connecting the proximal end and the distal end of the motor, that is, the direction x in the figure. The inner iron core 112 and the outer iron core 113 are of a cylindrical structure, and thus have two circumferential surfaces. The circumferential surface of the outer wall of the cylinder is the outer circumferential surface, and the circumferential surface of the inner wall of the cylinder is the inner circumferential surface. In addition, the axial direction of the inner iron core 112 refers to the direction in which the central axis extends. The circumferential direction of the inner iron core 112 refers to the circumferential direction around the cylinder. The radial direction refers to the direction passing through the central axis in the radial plane, and usually also refers to the straight-line direction along the diameter or radius, or the straight-line direction perpendicular to the central axis. The radial dimension generally refers to the radius or diameter of an axisymmetric part. It can be understood that in this application, the axial, circumferential, radial, and circumferential surfaces of other components can refer to the relevant descriptions of the aforementioned inner iron core 112.

[0059] Figure 3 Schematic structural diagram showing an exemplary inner iron core and proximal bearing housing; Figure 4 Showing an exemplary Figure 3 Perspective structural diagram of the inner iron core and proximal bearing housing in; Figure 5 Showing an exemplary Figure 2 Cross-sectional structural diagram of the ventricular assist device in the A-A position in; Figure 6 Showing another exemplary Figure 2 Cross-sectional structural diagram of the ventricular assist device in the A-A position in; Figure 7 Showing yet another exemplary Figure 2 Cross-sectional structural diagram of the ventricular assist device in the A-A position in. Figures 5 to 7 In, for the convenience of showing the structure of the flow cavity, the dimensions of the structures in the figure are not necessarily in proportion to the structures in other drawings.

[0060] Combined with Figures 2 to 5 It can be seen that in some of the embodiments, the outer iron core 113 is sleeved outside the inner iron core 112, and the inner circumferential surface of the outer iron core 113 is attached to the outer circumferential surface of the inner iron core 112. A groove 114a recessed into the accommodation cavity 1111 is provided on the circumferential surface of the inner iron core 112 facing the outer iron core 113, and a gap between the groove 114a and the outer iron core 113 forms a first flow cavity 1112.

[0061] In some of the implementation manners, the wall surface of the groove 114a has high surface finish and low roughness, and is subjected to a hydrophilic coating treatment.

[0062] Combined with Figure 2 And Figure 6It can be known that in some other embodiments, a groove 114b recessed in a direction away from the accommodation cavity 1111 is provided on the circumferential surface of the outer iron core 113 facing the inner iron core 112, and a first flow cavity 1112 is formed by the gap between the groove 114b and the inner iron core 111.

[0063] Combined Figure 2 with Figure 7 It can be known that in some other embodiments, the outer iron core 113 is sleeved outside the inner iron core 112, and the inner circumferential surface of the outer iron core 113 fits the outer circumferential surface of the inner iron core 112. Grooves 114c are provided on both the circumferential surface of the inner iron core 112 facing the outer iron core 113 and the circumferential surface of the outer iron core 113 facing the inner iron core 112, and a first flow cavity 1112 is formed between the groove 114c on the inner iron core 112 and the groove 114c on the outer iron core 113. The grooves 114c on the inner iron core 112 and the outer iron core 113 can be arranged in alignment to form a groove with a larger cross-sectional area, or the grooves 114c on the inner iron core 112 and the outer iron core 113 can be arranged in a staggered manner, so that the number of the first flow cavities 1112 is multiple. In this embodiment, only the groove 114a is opened on the inner iron core 112 as an example.

[0064] In some of these embodiments, the number of the grooves 114 can be one or more. The depth of the groove 114 is 0.05 mm - 0.5 mm. For example, the depth of the groove 114 can be any one of 0.05 mm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, and 0.5 mm. The depth of the groove 114 can refer to the dimension of the groove 114 along the radial direction.

[0065] The blood pumping device provided in this embodiment forms a first flow cavity 1112 by arranging grooves 114 on the inner iron core 112 and / or the outer iron core 113, and the perfusion liquid is conveyed along the extending direction of the grooves 114. Since the first flow cavity formed by the grooves 114 is a strip-shaped cavity, compared with an annular cavity with a larger cross-sectional area, the strip-shaped cavity has a smaller cross-sectional area, so that the perfusion liquid pressure at each part of the first flow cavity 1112 is similar, and it is not easy to have bubble residues in the first flow cavity 1112. Bubble residues in the perfusion pipeline may cause the following consequences: 1) Since bubbles are compressible, the high-pressure pulsation in the aorta will cause blood to flow back into the catheter, resulting in catheter failure (the working environment at the distal end of the perfusion device is the human aortic pressure, and the pulsating pressure changes with time. If there are bubble residues inside the perfusion device, the volume of the gas will change with the pressure, which will affect the instantaneous flow direction of the perfusion liquid at the farthest end face. When the bubble volume shrinks as the ambient pulse pressure increases, blood may flow back into the perfusion system, affecting the reliability of the blood pumping catheter. Blood is prone to form thrombus in the transmission area, especially at the bearing position, increasing the transmission friction coefficient, reducing the service life of the transmission system, and at the same time, it is easy to cause excessive temperature rise due to this); 2) If the bubbles are not completely discharged, there may be a certain probability that they will enter the blood vessel later, causing air embolism.

[0066] Combined Figures 2 to 4 It can be seen that in some of the embodiments, the first flow cavity 1112 spirally extends along a first direction x in the iron core 111, where the first direction x is the direction from the distal end to the proximal end of the motor 10. Here, the spiral extension of the first flow cavity 1112 means that the center point of the first flow cavity 1112 spirally extends along the first direction x. It is easy to understand that when the iron core 111 is composed of an inner iron core 112 and an outer iron core 113, and the inner iron core 112 and / or the outer iron core 113 are provided with grooves 114, the grooves 114 also spirally extend along the first direction x.

[0067] It can be understood that in this application, the spiral extension of the first flow cavity 1112 along the first direction x in the iron core 111 may mean that the first flow cavity 1112 has opposite ends, and the trajectory of the extension of one end of the first flow cavity 1112 to the other end in the iron core 111 spirally extends around an axis parallel to the first direction.

[0068] For the blood pumping device provided in this embodiment, compared with the scheme of opening a straight flow cavity along the first direction x, in this scheme, due to the spiral extension setting of the first flow cavity 1112, the solid thickness of the inner iron core 112 and the outer iron core 113 in the first direction x is more uniform. The first flow cavity 1112 is located at different circumferential positions of the iron core 111 during the extension along the first direction x, which will not cause the situation of unilateral thinning of the iron core 111, thereby improving the uniformity of the magnetic field distribution of the motor 10.

[0069] In some of these embodiments, the motor 10 further includes a rotor assembly 12. The rotor assembly 12 includes a rotating shaft 121 and a permanent magnet 122. The rotating shaft 121 extends along the first direction x, at least a part of the rotating shaft 121 is located in the accommodation cavity 1111, and the permanent magnet 122 is located in the accommodation cavity 1111 and sleeved on the rotating shaft 121. The number of pole pairs of the permanent magnet 122 is P. The first flow cavity 1112 spirally surrounds the rotating shaft 121, and the number of turns T of a single first flow cavity 1112 is T = 1 / P or T = 1 / (2P).

[0070] The number of pole pairs P refers to the number of pairs of magnetic poles in the permanent magnet 122. The permanent magnet 122 includes one or more N poles and S poles arranged at intervals around the rotating shaft 121. The number of N poles and S poles is equal, that is, the number of N poles is the number of pole pairs P of the permanent magnet 122. Taking the formula T = 1 / P as an example, when the number of pole pairs P is 1, the number of turns T of the first flow cavity 1112 is 1 turn. When the number of pole pairs P is 2, the number of turns T of the first flow cavity 1112 is 0.5 turn. Taking the formula T = 1 / (2P) as an example, when the number of pole pairs P is 1, the number of turns T of the first flow cavity 1112 is 0.5 turn. When the number of pole pairs P is 2, the number of turns T of the first flow cavity 1112 is 0.25 turn. When the number of the 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 along the axis of the rotating shaft 121, the angle between the connecting lines of any two adjacent first flow cavities 1112 and the axis of the rotating shaft 121 is equal. Preferably, the number of pole pairs P is 1, the number of turns T of the first flow cavity 1112 is 1 turn, and the number of the first flow cavities 1112 is 1.

[0071] In the motor 10, the tooth portions (not shown) and slot portions (not shown) on the iron core 111 will cause uneven magnetic field distribution, generate magnetic field torque, cause vibration of the iron core and generate noise, and reduce the efficiency of the motor 10. This phenomenon is called cogging effect. Among them, the slot portions on the iron core 111 are used to connect with windings, and the tooth portions are used to separate adjacent slot portions. Since the number of pole pairs P is related to the magnetic field distribution and rotational speed of the motor 10, in the blood pumping device provided in this embodiment, according to simulation tests and physical verification, by making the number of turns T of the first flow cavity 1112 be T = 1 / P or T = 1 / (2P), the perfusion liquid spirally conveyed in the first flow cavity 1112 is used to offset the cogging effect of the motor 10, thereby reducing the magnetic field torque and improving the efficiency of the motor 10.

[0072] In some of these embodiments, the stator assembly 11 further includes a winding 115 located in the accommodation cavity 1111. The winding is sleeved outside the permanent magnet 122. The length of the winding 115 in the first direction x is L. When the number of turns T of the first flow cavity 1112 is T = 1 / P, the pitch H of the first flow cavity 1112 is H = PL. When the number of turns T of the first flow cavity 1112 is T = 1 / (2P), the pitch H of the first flow cavity 1112 is H = 2PL.

[0073] The winding 115 is fixedly connected to the slot portion of the iron core 111. When the winding 115 is energized, the winding 115 generates a magnetic field and interacts with the magnetic field of the permanent magnet 122, causing the permanent magnet 122 to rotate synchronously with the rotating shaft 121.

[0074] The pitch H of the groove 114 can be understood by referring to the pitch of a bolt, that is, the distance measured along the axis of the bolt between two adjacent threads, generally referring to the axial distance between two corresponding points on the middle diameter line of two adjacent teeth on a single thread. In this embodiment, when the number of turns of the groove 114 is greater than 1, the pitch of the groove 114 can be understood as the distance between two adjacent positions of a single groove 114 in the first direction x.

[0075] Since the cogging effect is also related to the length of the winding 115 in the first direction x, in the blood pumping device provided in this embodiment, according to simulation tests and physical verification, by making the pitch H of the first flow chamber 1112 equal to PL or H = 2PL, the perfusion fluid spirally conveyed in the first flow chamber 1112 is used to offset the cogging effect of the motor 10, thereby reducing the magnetic torque and further improving the efficiency of the motor 10.

[0076] In some of these embodiments, both the inner iron core 112 and the outer iron core 113 are cylindrical structures, and the inner diameter of the inner peripheral surface of the outer iron core 113 is greater than the outer diameter of the outer peripheral surface of the inner iron core 112. That is, the inner iron core 112 and the outer iron core 113 are arranged with a gap therebetween, such that there is a gap for forming the first flow chamber 1112 between the inner iron core 112 and the outer iron core 113, and the first flow chamber 1112 is an annular cavity extending in the first direction x.

[0077] In the blood pumping device provided in this embodiment, by making the first flow chamber 1112 an annular cavity extending in the first direction x, the cross-sectional area of the first flow chamber 1112 is increased. And since the first flow chamber 1112 is an annular cavity, the connection openings of the first flow chamber 1112 with the first pipe and the second flow chamber 1113 can be designed at any position on the annular cavity according to actual needs, thereby improving the adaptability of the first flow chamber 1112 and reducing the design difficulty.

[0078] In other embodiments, the iron core 111 is integrally formed by processes such as powder metallurgy and 3D printing. During the forming process, the first flow chamber 1112 is naturally formed inside the iron core 111, or, after the iron core 111 is integrally formed, the first flow chamber 1112 is prepared on the iron core 111 by a processing technique.

[0079] After describing the implementation manners of the first flow chamber in the blood pumping device, several implementation manners of the second flow chamber in the blood pumping device will be described below in conjunction with the drawings. In conjunction with Figure 2, in some embodiments, the winding 115 at least partially surrounds the outside of the permanent magnet 122, and the gap between the winding 115 and the rotor assembly 12 forms a second flow cavity 1113.

[0080] In some embodiments, the iron core 111, the winding 115, and the permanent magnet 122 can be cylinders, or can be polygonal cylinder structures such as square cylinders. In this embodiment, it is exemplified that the iron core 111, the winding 115, and the permanent magnet 122 are all cylinders. The accommodation cavity 1111 is formed by surrounding and enclosing the iron core 111, and the accommodation cavity 1111 is used to accommodate components such as the winding 115, the permanent magnet 122, and the bearing. After removing the occupied positions of components such as the winding 115, the permanent magnet 122, and the bearing from the accommodation cavity 1111, the remaining cavity is the second flow cavity 1113. It is easy to understand that when the iron core 111 is composed of an inner iron core 112 and an outer iron core 113, the accommodation cavity 1111 is formed by surrounding and enclosing the inner iron core 111.

[0081] In other embodiments, the second flow cavity 1113 is also located inside the iron core 111. For example, when the iron core 111 is integrally formed, both the first flow cavity 1112 and the second flow cavity 1113 are prepared by performing a processing technique on the iron core 111. Or, when the iron core 111 is composed of an inner iron core 112 and an outer iron core 113, the gap between the inner iron core 112 and the outer iron core 113 forms the first flow cavity 1112, and at the same time, there is also a second flow cavity 1113 formed by a processing technique on the inner iron core 112 and / or the outer iron core 113. The specific form of the second flow cavity 1113 located inside the iron core 111 can refer to the form of the first flow cavity 1112 formed by the groove 114, which will not be elaborated here.

[0082] In some embodiments, the motor 10 further includes a distal bearing 13 and a proximal bearing 14, and both the distal bearing 13 and the proximal bearing 14 are sleeved on the rotating shaft 121. The rotating 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.

[0083] In some of these embodiments, the distal bearing 13 and the proximal bearing 14 can be sliding bearings or ball bearings. In some of these implementations, the distal bearing 13 and the proximal bearing 14 are ball bearings, and there are gaps on the distal bearing 13 and the proximal bearing 14 through which the perfusion fluid can pass, such as the gaps between the balls. The perfusion fluid located on both sides of the bearing in the axial direction can flow through the gaps on the bearing. For example, the perfusion fluid flowing from the first flow chamber 1112 to the second flow chamber 1113 flows out of the second pipe 20 after passing through the distal bearing 13 and the proximal bearing 14 in sequence, or the perfusion fluid flowing into the second pipe 20 flows out of the first pipe through the first flow chamber 1112 after passing through the proximal bearing 14 and the distal bearing 13 in sequence. In some alternative implementations, the distal bearing 13 and the proximal bearing 14 are sliding bearings, and a gap allowing the perfusion fluid to pass is formed between the distal bearing 13 and other components (such as a bearing housing), and a gap allowing the perfusion fluid to pass is formed between the proximal bearing 14 and other components (such as a bearing housing). In some other alternative implementations, one of the distal bearing 13 and the proximal bearing 14 is a ball bearing and the other is a sliding bearing, and the specific solution can be a combination of the first two implementations.

[0084] In the blood pumping device provided in this embodiment, when the perfusion fluid flows through the distal bearing 13 and / or the proximal bearing 14, it can carry away the particles generated during the rotation of the bearing, reduce the wear of the bearing, and thus increase the service life of the motor 10.

[0085] Figure 8 The structural schematic diagram of an exemplary proximal cap is shown; Figure 9 The structural schematic diagram of an exemplary outer iron core and distal cap is shown.

[0086] Combined with Figure 2 、 Figure 8 and Figure 9 It can be known that in some of these embodiments, the motor 10 further includes a distal cap 15 and a proximal cap 16. The distal cap 15 is connected to the distal end of the stator assembly 11, and the proximal cap 16 is connected to the proximal end of the stator assembly 11. The distal cap 15 is provided with a first through hole 151 penetrating the distal cap 15 in the first direction x, and at least part of the rotating shaft 121 extends out of the accommodation chamber 1111 from the first through hole 151. The proximal cap 16 is provided with a second through hole 161 penetrating the proximal cap 16 in the first direction x, and the second through hole 161 is used to directly or indirectly connect the second flow chamber 1113 and the second pipe 20. The distal cap 15 is used to seal the distal end of the accommodation chamber 1111, and the proximal cap 16 is used to seal the proximal end of the accommodation chamber 1111.

[0087] In some of these embodiments, the distal shape of the distal cap 15 is a conical streamline surface, and in the working state, the conical streamline surface can be used as a blood flow surface.

[0088] In some of these embodiments, an impeller 42 is provided in the outflow passage 40 of the blood pumping device. The rotating shaft 121 extends out of the accommodation cavity 1111 from the first through hole 151 and is connected to the impeller 42. When the motor 10 is started, the rotating shaft 121 drives the impeller 42 to rotate. When the impeller 42 rotates, it pumps blood from the suction window to the outflow window 41 and realizes the blood pumping function.

[0089] In some of these embodiments, the materials of the proximal cap 16 and the distal cap 15 include metals and non-metals, and the materials of the distal cap 15 and the proximal cap 16 may be the same or different. For example, the materials of both the distal cap 15 and the proximal cap 16 are 316 stainless steel.

[0090] Figure 10 The structural schematic diagram of an exemplary distal bearing housing is shown; Figure 11 The structural schematic diagram of another exemplary inner iron core and proximal bearing housing is shown.

[0091] Combined Figure 2 、 Figure 10 and Figure 11 It can be understood that in some of these embodiments, the motor 10 further includes a proximal bearing housing 17 and a distal bearing housing 18. The proximal bearing housing 17 is connected to the proximal end of the stator assembly 11. The proximal bearing housing 17 is provided with a first mounting hole 171 that axially penetrates the proximal bearing housing 17 along the rotating shaft 121. The proximal bearing 14 and the proximal cap 16 are both embedded in the first mounting hole 171, and the proximal cap 16 is located at one end of the proximal bearing 14 away from the distal bearing 13. The distal bearing housing 18 is connected to the distal end of the stator assembly 11. The distal bearing housing 18 is provided with a second mounting hole 181 that axially penetrates the distal bearing housing 18 along the rotating shaft 121. The distal bearing 13 is sleeved on the rotating shaft 121 and is embedded in the second mounting hole 181. The distal bearing housing 18 is connected to the distal end of the stator assembly 11. The distal bearing housing 18 is provided with a second mounting hole 181 that penetrates the distal bearing housing 18 along the first direction x, and the distal bearing 13 is embedded in the second mounting hole 181.

[0092] It can be understood that the proximal bearing 14 being embedded in the first mounting hole 171 means that the outer peripheral surface of the proximal bearing 14 is embedded in the circumferential surface of the proximal bearing housing 17 facing the first mounting hole 171 and is fixedly connected. At the same time, the inner peripheral surface of the proximal bearing 14 is sleeved on the rotating shaft 121 and is fixedly connected to the rotating shaft 121. The same applies to the distal bearing 13.

[0093] In some embodiments, a gap is formed between the distal cover 15 and the distal bearing seat 18 in the first direction x, and the gap between the distal cover 15 and the distal bearing seat 18 forms a third circulation cavity 19, and the third circulation cavity 19 is connected to the first circulation cavity 1112 and the second circulation cavity 1113 through the distal bearing 13. The two end surfaces of the distal bearing 13 in the first direction x face the second circulation cavity 1113 and the third circulation cavity 19 respectively.

[0094] The radial dimension of the first through hole 151 is slightly larger than the radial dimension of the rotating shaft 121, so that the perfusion liquid in the third circulation chamber 19 can flow into the outflow channel 40 through the gap between the first through hole 151 on the distal cover 15 and the rotating shaft 121, and can also flow into the second circulation chamber 1113 through the gap between the balls on the distal bearing 13. By setting the radial dimension of the first through hole 151, most of the perfusion liquid can be controlled to flow to the distal bearing 13, and a small part of the perfusion liquid is used to balance the pressure difference between the outflow channel 40 and the third circulation chamber 19, thereby reducing the total amount of blood flowing into the motor 10 at the outflow channel 40 and reducing the probability of blood forming thrombus in the motor 10.

[0095] In some embodiments, the first pipeline is a perfusion pipeline, and the second pipeline 20 is a return pipeline. The perfusion liquid in the first pipeline flows through the first circulation cavity 1112, the third circulation cavity 19, the distal bearing 13, the second circulation cavity 1113 and the proximal bearing 14 in sequence, and then flows out of the motor 10 through the second pipeline 20.

[0096] In the blood pumping device provided in this embodiment, when the perfusion liquid flows through the distal bearing 13 and the proximal bearing 14, it can carry away the particles generated when the bearings rotate, effectively reducing the particles generated when the motor 10 is running and entering the human body, reducing the total amount of perfusion liquid flowing into the patient's body, and then reducing the total amount of particles flowing into the patient's body, thereby improving product safety. By making the first pipe a perfusion pipe and the second pipe 20 a return pipe, the perfusion liquid will first enter the third circulation cavity 19 from the first circulation cavity 1112, and then flow out from the second pipe 20 after flushing the bearings, so that the particle content in the perfusion liquid at the third circulation cavity 19 is extremely low, reducing the total amount of particles flowing into the patient's body from the first through hole 151.

[0097] In some embodiments, the circumferential surface of the distal 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 bearing seat 12. The radial dimension of the fifth step surface 182 is smaller than the radial dimension of the sixth step surface 183, and the distal bearing 13 is embedded in the sixth step surface 183. The perfusion liquid in the third circulation cavity 19 first flows through the second mounting hole 181 where the fifth step surface 182 is located, and then flows into the second circulation cavity 1113 through the distal bearing 13.

[0098] The blood pumping device provided in this embodiment makes the radial dimension of the fifth step surface 182 smaller than that of the sixth step surface 183. The side wall of the fifth step surface 182 facing the sixth step surface 183 will abut against the distal bearing 13, restricting the movement of the distal bearing 13 in the first direction x, thereby improving the connection stability between the distal bearing 13 and the distal bearing seat 18.

[0099] Figure 12 Shows an example of Figure 11 The cross-sectional structural schematic diagram of the inner iron core and the proximal bearing seat in.

[0100] Combined with Figure 2 、 Figure 11 And Figure 12 It can be known that in some embodiments, a first communication hole 172 is further provided on the proximal bearing seat 17, and the first communication hole 172 is directly or indirectly communicated with the first flow cavity 1112 and the first pipeline.

[0101] In some embodiments, the connection between the first pipeline and the proximal bearing seat 17, and the connection between the second pipeline 20 and the proximal cover 16 can adopt welding, gluing or other sealing methods.

[0102] Figure 13 Shows a structural schematic diagram of an example of the second pipeline.

[0103] Combined with Figure 13 It can be known that in some embodiments, the first pipeline and the second pipeline 20 can be straight tube-shaped pipes or other special-shaped pipes, and the present application does not make specific limitations thereto. In addition, for the return pipeline, a notch 21 is provided at the proximal end of the return pipeline, and the number of notches 21 can be at least one. When the number of notches 21 is more than two, the multiple notches 21 are arranged symmetrically or asymmetrically along the circumferential direction. The notch 21 is used to connect with a support wire (not shown) at least partially located in the return pipeline. After the support wire is embedded in the notch 21, it is connected to the return pipeline by laser welding or gluing at the embedded position, further improving the connection strength between the return pipeline and the motor 10.

[0104] In some embodiments, one opening of the first communication hole 172 is located on the end surface of the proximal bearing seat 17 facing away from the distal bearing seat 18 and is communicated with the first pipeline, and the other opening is located on the circumferential surface of the proximal bearing seat 17 facing away from the first mounting hole 171 and is communicated with the first flow cavity 1112.

[0105] In some of these embodiments, the distal end cap 15 and the outer iron core 113 can be prepared separately and then connected by processes such as welding and gluing. The distal end cap 15 and the outer iron core 113 can also be integrally formed. The proximal bearing seat 17 and the inner iron core 112 can be prepared separately and then connected by processes such as welding and gluing. The proximal bearing seat 17 and the inner iron core 112 can also be integrally formed. When the proximal bearing seat 17 and the inner iron core 112 are connected after being prepared separately, 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 processes such as welding and gluing. The same applies to the distal end cap 15 and the outer iron core 113.

[0106] Combined Figure 2 with 3 it can be seen that in some of these embodiments, the circumferential surface of the inner iron core 112 facing the outer iron core 113 includes a first stepped surface 1121 and a second stepped surface 1122. The first stepped surface 1121 is located at the distal end of the inner iron core 112, and the second stepped surface 1122 is located at the proximal end of the inner iron core 112. The radial dimension of the first stepped surface 1121 is smaller than the radial dimension of the second stepped surface 1122. The circumferential surface of the proximal bearing seat 17 facing away from the first mounting hole 171 includes a third stepped surface 173 and a fourth stepped surface 174. The third stepped surface 173 is located on the side of the fourth stepped surface 174 closer to the inner iron core 112. The radial dimension of the third stepped surface 173 is smaller than the radial dimension of the fourth stepped surface 174, and the radial dimension of the third stepped surface 173 is smaller than the radial dimension of the second stepped surface 1122. One of the openings of the first communication hole 172 is located on the third stepped surface 173.

[0107] The distal end cap 15 overlaps on the first stepped surface 1121, and the outflow channel 40 overlaps on the circumferential surface of the distal end cap 15 facing away from the first stepped surface 1121. By making the radial dimension of the first stepped surface 1121 smaller than the radial dimension of the second stepped surface 1122, the radial dimensions at the overlapping joints of the distal end cap 15 and the inner iron core 112 and at the overlapping joints of the distal end cap 15 and the outflow channel 40 are effectively reduced, thereby reducing the intervention difficulty of the motor 10 and the blood pumping device.

[0108] Among them, the multiple step surfaces on the circumferential surface of the proximal bearing seat 17 facing away from the first mounting hole 171 refer to the circumferential surface provided with multiple bosses with different radial dimensions, the outer circumferential surface of the boss is defined as the step surface, and the radial dimension refers to the diameter of the boss. The step surface on the circumferential surface of the inner core 112 facing the outer core 113 is the same. 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 in the axial direction of the rotating shaft 121 and surrounds the axis, and the annular groove is connected to the third flow cavity 19. When the inner core 112 is provided with a groove 114, the groove 114 extends from the first step surface 1121 to the second step surface 1122 and communicates with the annular groove formed by the third step surface 173. The groove 114 communicates with the third circulation cavity 19 at the first step surface 1121, and the groove 114 communicates 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 liquid 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 circulation cavity 1112 formed by the groove 114. The annular groove formed by the third step surface 173 can make it possible to provide a plurality of first communication holes 172 to communicate with each first circulation cavity 1112 when there are a plurality of first circulation cavities 1112, and it is only necessary for the plurality of first circulation cavities 1112 to communicate 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 circumference of the outer core 113, that is, the fourth step surface 174 is embedded in the outer core 113. By making the fourth step surface 174 abut against the inner circumference of the outer core 113, the outer core 113 seals the annular groove formed at the third step surface 173, so that the annular groove has only two outlets, namely, the groove 114 and the first connecting hole 172.

[0109] In some embodiments, the inner core 112 is connected to the proximal bearing seat 17, and the third and fourth step surfaces 174 on the proximal bearing seat 17 are connected to the outer core 113. It can also be understood that the outer core 113 is connected to 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 cavity 1112.

[0110] In some of the embodiments, the motor 10 further includes a housing (not shown), which is sleeved outside the iron core 111 , and at least a portion of the housing is in contact with the second step surface 1122 .

[0111] It can be understood that the components in contact with the human body and blood in the above-mentioned blood pumping device need to be made of biocompatible materials, which can be metals or non-metals. For example, when these components are made of metal, they can be made of 316 stainless steel. In some other embodiments, the iron core 111 can also be used as the outer shell of the motor 10 to directly contact the patient's tissue, so that the motor 10 does not need to be provided with an additional housing, thereby reducing the diameter of the motor 10 and the difficulty of intervention.

[0112] It can be understood that the above-described embodiments introduce each component separately. In fact, each component can be recombined and integrally formed. For example, the inner iron core 112 and the proximal bearing seat 17 are integrally formed. For another example, the outer iron core 113 and the distal cover 15 are integrally formed. For another example, the inner iron core 112 and the outer iron core 113 are integrally formed. For another example, the inner iron core 112 and the distal bearing seat 18 are integrally formed. The above are only partial examples of integral forming, 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 this application.

[0113] In some alternative embodiments, the present application further provides a liquid pumping device for pumping other body fluids except blood. The liquid pumping device includes a motor 10, a first pipe, and a second pipe 20. The motor 10 includes a stator assembly 11. The stator assembly 11 includes an iron core 111. The iron core 111 encloses a receiving cavity 1111. A first flow cavity 1112 is provided in the iron core 111. A second flow cavity 1113 communicating with the first flow cavity 1112 is provided inside the iron core 111 and / or inside the receiving cavity 1111. The first pipe communicates with the first flow cavity 1112; the second pipe 20 communicates with the second flow cavity 1113. One of the first pipe and the second pipe 20 is a perfusion pipe, and the other is a return pipe. Among them, the perfusion pipe is used to transport perfusion fluid to the motor 10, and the return pipe is used to discharge the perfusion fluid in the motor 10.

[0114] In some of these embodiments, the body fluid includes tissue fluid, digestive fluid, etc.

[0115] The structure of the liquid pumping device refers to the blood pumping device and can produce the same technical effects as the blood pumping device, so details are not described here too much.

[0116] In addition, the present application further provides a motor. The motor includes a stator assembly. The stator assembly includes an iron core. The iron core encloses a receiving cavity. A first flow cavity is provided in the iron core. A second flow cavity communicating with the first flow cavity is provided inside the iron core and / or inside the receiving cavity. One of the first flow cavity and the second flow cavity is used to communicate with the perfusion pipe, and the other is used to communicate with the return pipe. The perfusion pipe is used to transport perfusion fluid into the motor, and the return pipe is used to discharge the perfusion fluid in the motor.

[0117] It can be understood that the motor provided in the present application can be the motor in any one of the foregoing blood pumping device and liquid pumping device, and will not be described repeatedly herein.

[0118] As described above, the foregoing is only the specific implementation manner of the present application. Those skilled in the art can clearly understand that for the convenience and brevity of description, the specific working processes of the above-described systems, modules, and units can refer to the corresponding processes in the foregoing method embodiments, and will not be elaborated herein. It should be understood that the protection scope of the present application is not limited thereto. Any person skilled in the art within the technical scope disclosed in the present application can easily think of various equivalent modifications or substitutions, and these modifications or substitutions should all be covered within the protection scope of the present application.

Claims

1. A blood pumping device for transporting blood, characterized in that, include: A motor, comprising a stator assembly, wherein the stator assembly comprises an iron core, wherein the iron core is enclosed to form a receiving cavity, wherein a first flow cavity is provided in the iron core, and wherein a second flow cavity communicating with the first flow cavity is provided in the iron core and / or in the receiving cavity; a first pipe, communicating with the first flow chamber; The second pipe is connected to the second circulation cavity, one of the first pipe and the second pipe is a perfusion pipe, and the other is a return pipe. The perfusion pipe is used to transport perfusion liquid to the motor, and the return pipe is used to discharge the perfusion liquid in the motor.

2. The blood pumping device according to claim 1, wherein The first flow cavity is a strip-shaped cavity extending along a first direction, wherein the first direction is a direction from the distal end of the motor to the proximal end.

3. The blood pumping device according to claim 2, wherein The iron core comprises an inner iron core and an outer iron core sleeved outside the inner iron core, and the outer circumference of the inner iron core is in contact with the inner circumference of the outer iron core: A groove is provided on the circumferential surface of the inner iron core facing the outer iron core, and the gap between the groove and the outer iron core forms the first flow cavity; Or, a groove is provided on the circumferential surface of the outer core facing the inner core, and a gap between the groove and the inner core forms the first flow cavity; Alternatively, grooves are provided on the circumferential surface of the inner core facing the outer core and on the circumferential surface of the outer core facing the inner core, and the first flow cavity is formed between the groove on the inner core and the groove on the outer core.

4. The blood pumping device according to claim 2 or 3, characterized in that, The first flow chamber spirally extends in the core along the first direction.

5. The blood pumping device according to claim 4, characterized in that, The motor further includes a rotor assembly, the rotor assembly including a rotating shaft and a magnetic steel, the rotating shaft extends along the first direction, at least a portion of the rotating shaft is located in the accommodating cavity, and the magnetic steel is located in the accommodating cavity and sleeved on the rotating shaft; The number of pole pairs of the magnetic steel is P, the first circulation cavity is spirally wound around the rotating shaft, and the number of turns of a single first circulation cavity is T=1 / P or T=1 / (2P).

6. The blood pumping device according to claim 5, wherein, The stator assembly further includes a winding located in the accommodating cavity, the winding is sleeved outside the magnetic steel, and the gap between the winding and the rotor assembly forms the second flow cavity; The length of the winding in the first direction is L: when the number of turns of the first circulation cavity is T=1 / P, the pitch of the first circulation cavity is H=PL; when the number of turns of the first circulation cavity is T=1 / (2P), the pitch of the first circulation cavity is H=2PL.

7. The blood pumping device according to claim 5, characterized in that, The motor also includes: A distal bearing, sleeved on the rotating shaft, the distal bearing communicating with the first circulation cavity and the second circulation cavity; A proximal bearing, sleeved on the rotating shaft, the rotating shaft is rotatably connected to the stator assembly through the distal bearing and the proximal bearing, and the distal bearing is located on a side of the proximal bearing away from the first pipe; A distal cover connected to the distal end of the stator assembly, the distal cover is provided with a first through hole penetrating the distal cover along the first direction, at least a portion of the rotating shaft extends out of the accommodating cavity from the first through hole, and the distal cover is used to seal the distal end of the accommodating cavity; A proximal 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 cover is provided with a second through hole that penetrates the distal cover along the first direction, and the second through hole is used to connect the second flow cavity with the second pipe.

8. The blood pumping device according to claim 7, characterized in that, The motor also includes: A proximal bearing seat, the proximal bearing seat is connected to the proximal end of the stator assembly, the proximal bearing seat is provided with a first mounting hole penetrating the proximal bearing seat along the first direction, the proximal bearing and the proximal cover are both embedded in the first mounting hole, and the proximal cover is located at an end of the proximal bearing away from the distal bearing; A distal bearing seat is connected to the distal end of the stator assembly, and a second mounting hole is provided on the distal bearing seat and penetrates the distal bearing seat along the first direction, and the distal bearing is embedded in the second mounting hole.

9. The blood pumping device according to claim 8, characterized in that, There is a gap between the distal cover and 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 connects the first flow cavity and the second flow cavity.

10. The blood pumping device according to claim 9, wherein, The first pipeline is a perfusion pipeline, and the second pipeline is a return pipeline.

11. The blood pumping device according to claim 8, characterized in that, The proximal bearing seat is also provided with a first communicating hole, and the first communicating hole is connected with the first circulation cavity and the first pipeline.

12. The blood pumping device according to claim 11, characterized in that, One opening of the first connecting hole is located on the end surface of the proximal bearing seat away from the distal bearing seat and is connected to the first pipeline, and the other opening is located on the circumferential surface of the proximal bearing seat away from the first mounting hole and is connected to the first circulation cavity.

13. The blood pumping device according to claim 1, characterized in that, The iron core comprises an inner iron core and an outer iron core sleeved outside the inner iron core, a gap is set between the outer iron core and the inner iron core, and the gap between the inner iron core and the outer iron core forms the first flow cavity.

14. A motor, characterized in that, The invention comprises a stator assembly, wherein the stator assembly comprises an iron core, wherein the iron core encloses a receiving cavity, wherein a first flow cavity is arranged in the iron core, and wherein a second flow cavity connected with the first flow cavity is arranged in the iron core and / or in the receiving cavity, wherein one of the first flow cavity and the second flow cavity is used to be connected with an injection pipe, and the other is used to be connected with a return pipe.

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