Blood pumping device and motor

Abstract

The utility model 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 a winding and an iron core arranged outside the winding in a sleeving mode, a containing cavity is formed in the winding, and a gap between the winding and the iron core forms a first circulation cavity; a second circulation cavity is formed in the accommodating cavity and / or a gap between the winding and the iron core forms the second circulation cavity, and the second circulation cavity and the first circulation cavity are mutually independent and communicated; 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 into 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. Existing ventricular assist devices utilize the principle of cardiac blood pumping, pump the blood in the heart out through a pumping mechanism, and divert the blood to the aorta outside the heart to flow to the whole body.

[0003] Existing ventricular assist devices include 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 a vein such as the femoral vein by the pushing of the catheter.

[0004] 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 Utility Model

[0005] The embodiments of this application provide a blood pumping device and a motor, which can improve the effective heat dissipation of the blood pumping device and the motor.

[0006] The embodiments of this application provide a blood pumping device. The blood pumping device is used 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 a winding and an iron core sleeved outside the winding. An accommodation cavity is arranged inside the winding. The gap between the winding and the iron core forms a first flow cavity. A second flow cavity is arranged inside the accommodation cavity and / or the gap between the winding and the iron core further forms a second flow cavity. The second flow cavity is independent of and communicated with the first flow cavity; the first pipeline is communicated with the first flow cavity; the second pipeline is communicated 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 for transporting perfusion liquid into the motor, and the return pipeline is used for discharging the perfusion liquid in the motor.

[0007] According to the embodiment of the first aspect of this application, the motor further includes a rotor assembly. At least part of the rotor assembly is located inside the accommodation cavity. The gap between the winding and the rotor assembly forms the second flow cavity.

[0008] According to an embodiment of the first aspect of the present application, the motor further includes: a proximal bearing seat connected to the proximal end of the stator assembly, and the outer peripheral surface of the proximal bearing seat includes a first stepped surface and a second stepped surface arranged in a first direction; a distal bearing seat connected to the distal end of the stator assembly, and the outer peripheral surface of the distal bearing seat includes a third stepped surface and a fourth stepped surface arranged in the first direction, the circumferential surface on the side of the winding away from the iron core is lapped on the third stepped surface and the second stepped surface, and the circumferential surface on the side of the iron core facing the winding is lapped on the fourth stepped surface and the first stepped surface; wherein, the first direction is the connecting line direction of the proximal end and the distal end of the motor.

[0009] According to an embodiment of the first aspect of the present application, a first communication groove penetrating in the first direction is provided on the first stepped surface, and the first communication groove communicates with a first pipeline; a second communication groove penetrating in the first direction is provided on the fourth stepped surface, and the second communication groove communicates with a second flow cavity.

[0010] According to an embodiment of the first aspect of the present application, a communication hole communicating the first pipeline and the first communication groove is provided on the proximal bearing seat, and one opening of the communication hole is located on the end surface of the proximal bearing seat facing away from the distal bearing seat, and the other opening of the communication hole communicates with the first communication groove.

[0011] According to an embodiment of the first aspect of the present application, the rotor assembly includes a rotating shaft and a permanent magnet sleeved on the rotating shaft, the rotating shaft extends in the first direction, the permanent magnet and at least part of the rotating shaft are located in the accommodating cavity, and the winding is sleeved on the permanent magnet; the motor further includes: a distal bearing sleeved on the rotating shaft; a distal cover, the distal cover is connected to the distal end of the stator assembly, and a first through hole penetrating the distal cover in the first direction is provided on the distal cover, at least part 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; 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 communicates with the first flow cavity and the second flow cavity.

[0012] According to an embodiment of the first aspect of the present application, the motor further includes: a proximal bearing sleeved on the rotating shaft, the proximal bearing communicates the second flow cavity and a second pipeline, the rotating shaft is rotationally 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 pipeline.

[0013] According to an embodiment of the first aspect of the present application, a partition is provided between the winding and the iron core, so that the gaps between the winding and the iron core respectively form a first flow cavity and a second flow cavity.

[0014] 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.

[0015] A second aspect of the present application provides a motor, comprising a stator assembly. The stator assembly includes a winding and a core sleeved outside the winding. An accommodation cavity is provided in the winding, and a first flow cavity is formed by the gap between the winding and the core. A second flow cavity is provided in the accommodation cavity or the gap between the winding and the core further forms a second flow cavity. The first flow cavity communicates with the second flow cavity. One of the first flow cavity and the second flow cavity is used to communicate with a perfusion pipeline, and the other is used to communicate with a reflux pipeline. The perfusion pipeline is used to convey a perfusion fluid into the motor, and the reflux pipeline is used to discharge the perfusion fluid in the motor.

[0016] It can be understood that the motor provided in the second aspect of the present application can be any of the motors in the blood pumping device provided in the first aspect of the present application, and will not be described repeatedly herein. This motor can be used in various application scenarios such as pumping blood, pumping tissue fluid, and pumping digestive fluid.

[0017] The blood pumping device according to an embodiment of the present application, wherein the blood pumping device is used to convey 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 a winding and a core sleeved outside the winding. An accommodation cavity is provided in the winding, and a first flow cavity is formed by the gap between the winding and the core. A second flow cavity is provided in the accommodation cavity or the gap between the winding and the core further forms a second flow cavity. The second flow cavity communicates with the first flow cavity; 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 a perfusion pipeline, and the other is a reflux pipeline. The perfusion pipeline is used to convey a perfusion fluid into the motor, and the reflux pipeline is used to discharge the perfusion fluid in the motor. In the present application, the first pipeline and the second pipeline are connected to the inside of the motor. The perfusion fluid flows into the motor through one of the pipelines, 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 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 pipeline between the winding and the core, there is no need to provide an additional pipeline outside the motor, reducing the outer diameter of the motor and thus reducing the intervention difficulty. Description of the Drawings

[0018] 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.

[0019] Figure 1 Structural schematic diagram of a ventricular assist device including a blood pumping device according to some embodiments of the present application;

[0020] Figure 2 Showing an example of Figure 1 Longitudinal sectional structural schematic diagram of the ventricular assist device in

[0021] Figure 3 Shows a schematic structural diagram of an exemplary distal bearing housing;

[0022] Figure 4 Shows a schematic structural diagram of an exemplary proximal bearing housing;

[0023] Figure 5 Shows an exemplary Figure 2 Cross-sectional structural diagram of the ventricular assist device in the A-A position;

[0024] Figure 6 Shows another exemplary Figure 2 Cross-sectional structural diagram of the ventricular assist device in the A-A position;

[0025] Figure 7 Shows a schematic structural diagram of an exemplary distal cap;

[0026] Figure 8 Shows a schematic structural diagram of an exemplary proximal cap;

[0027] Figure 9 Shows a schematic structural diagram of an exemplary second pipe;

[0028] Figure 10 Shows a schematic structural diagram of an exemplary iron core.

[0029] Reference numerals:

[0030] 10. Motor; 11. Stator assembly; 111. Winding; 112. Iron core; 1121. Eighth stepped surface; 1122. Ninth stepped surface; 113. Accommodation cavity; 114. First flow cavity; 115. Second flow cavity; 116. Partition; 12. Proximal bearing housing; 121. First stepped surface; 1211. First communication groove; 122. Second stepped surface; 123. Communication hole; 124. First mounting hole; 125. Seventh stepped surface; 126. Wire groove; 13. Distal bearing housing; 131. Third stepped surface; 132. Fourth stepped surface; 1321. Second communication groove; 133. Second mounting hole; 1331. Fifth stepped surface; 1332. Sixth stepped surface; 14. Rotor assembly; 141. Rotating shaft; 142. Permanent magnet; 15. Distal bearing; 16. Proximal bearing; 17. Distal cap; 171. First through hole; 18. Third flow cavity; 19. Proximal cap; 191. Second through hole;

[0031] 20. First pipe;

[0032] 30. Second pipe; 31. Notch;

[0033] 40. Outflow channel; 41. Outflow window; 42. Impeller;

[0034] 50. Intervention catheter;

[0035] x, First direction. Detailed implementation manners

[0036] 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, the present application will be further described in detail below with reference to the accompanying drawings and specific embodiments. It should be understood that the specific embodiments described herein are only intended to explain the present application, rather than limiting 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.

[0037] 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 variant thereof is intended to cover non-exclusive inclusion, so that a process, method, article or device comprising a series of elements not only includes those elements, but also includes other elements not expressly listed, or further includes elements inherent to such process, method, article or device. Without further limitation, an element defined by the statement "comprising..." does not exclude the existence of additional identical elements in the process, method, article or device comprising the element.

[0038] To solve the technical problems proposed in the background art, the applicant proposes 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 a winding and an iron core sleeved outside the winding. An accommodation cavity is provided in the winding. A first flow cavity is formed in the gap between the winding and the iron core. A second flow cavity is provided in the accommodation cavity and / or a second flow cavity is further formed in the gap between the winding and the iron core. The second flow cavity is independent of and communicated with the first flow cavity; the first pipeline is communicated with the first flow cavity; the second pipeline is communicated with the second flow cavity. One of the first pipeline and the second pipeline is an irrigation pipeline, and the other is a return pipeline. The irrigation pipeline is used to transport irrigation liquid into the motor, and the return pipeline is used to discharge the irrigation liquid in the motor.

[0039] The blood pumping device provided by the present application is internally connected to the motor through the first pipeline and the second pipeline. The perfusion fluid 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 the motor and reducing the damage caused to the patient by the blood pumping device. By arranging the first flow cavity communicating with the first pipeline between the iron core and the winding, there is no need to arrange an additional pipeline outside the motor, reducing the outer diameter of the motor and thus reducing the intervention difficulty.

[0040] 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, and digestive fluid. For the convenience of understanding and description, the following will continue to take the application scenario where the motor is applied in the blood pumping device as an example for description.

[0041] 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 diagram of the ventricular assist device in. Combining Figure 1 and Figure 2 It can be seen 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 50. The intervention catheter 50 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 are pushed through the patient's blood vessels by the intervention catheter 50 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.

[0042] When the blood pumping device, the interventional catheter 50, and the outflow channel 40 are inserted into the patient's body, the end of the interventional catheter 50 facing away from the motor 10 extends out of the patient's body and is connected to devices such as a liquid storage tank (not shown), a power supply device, and a control switch. At least part of the first pipeline 20 and the second pipeline 30 are located inside the interventional catheter 50. The liquid storage tank conveys 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 normal saline and an 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.

[0043] It can be understood that in this 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 interventional catheter 50, and the distal end of the motor 10 faces the outflow channel 40.

[0044] 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. Here, it is noted that the direction extending along the connection line between the proximal end and the distal end of the stator assembly in the accompanying drawings and pointing from the distal end to the proximal end is the first direction. It can be understood that the first direction can also be expressed as the axial direction of the rotating shaft, denoted as x. In the accompanying drawings, for the convenience of drawing, the dimensions in the drawings do not necessarily have a proportional relationship with the actual dimensions.

[0045] Combined 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 20, and a second pipeline 30. The motor 10 includes a stator assembly 11. The stator assembly 11 includes a winding 111 and an iron core 112 sleeved outside the winding 111. An accommodation cavity 113 is provided inside the winding 111. A first flow cavity 114 is formed in the gap between the winding 111 and the iron core 112. A second flow cavity 115 is provided in the accommodation cavity 113 and / or a second flow cavity 115 is further formed in the gap between the winding 111 and the iron core 112. The second flow cavity 115 is independent of and communicated with the first flow cavity 114. The first pipeline 20 is communicated with the first flow cavity 114, and the second pipeline 30 is communicated with the second flow cavity 115. One of the first pipeline 20 and the second pipeline 30 is a perfusion pipeline, and the other is a reflux pipeline. Among them, the perfusion pipeline is used to convey the perfusion liquid into the motor 10, and the reflux pipeline is used to discharge the perfusion liquid in the motor 10.

[0046] In some implementation manners, the wall surface of the first flow cavity 114 has a high surface finish and a low roughness, and the wall surface of the first flow cavity 114 is treated with a hydrophilic coating.

[0047] In some of these embodiments, both the winding 111 and the iron core 112 are cylindrical structures. The winding 111 and the iron core 112 can be circular cylinders, or can be polygonal cylindrical structures such as square cylinders. In this embodiment, it is exemplified that both the winding 111 and the iron core 112 are circular cylinders. The accommodation cavity 113 is formed by surrounding and enclosing the winding 111.

[0048] In some of these embodiments, the first flow cavity 114 and the second flow cavity 115 are directly connected or indirectly connected. Indirect connection means that the first flow cavity 114 and the second flow cavity 115 are connected through at least one other cavity, gap or spatial structure. This embodiment describes the application scenario where the first flow cavity 114 and the second flow cavity 115 are indirectly connected.

[0049] The blood pumping device provided in this embodiment is connected to the motor 10 through the first pipeline 20 and the second pipeline 30. The perfusion liquid flows through one of the pipelines to the motor 10, then flows through the first flow cavity 114 and the second flow cavity 115 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 the motor 10 and reducing the damage to the patient caused by the blood pumping device. By providing the first flow cavity 114 communicating with the first pipeline 20 between the iron core 112 and the winding 111, there is no need to additionally arrange a pipeline outside the motor 10, the outer diameter of the motor 10 is reduced, and thus the intervention difficulty is reduced.

[0050] Figure 3 Shows a schematic structural diagram of an exemplary distal bearing seat; Figure 4 Shows a schematic structural diagram of an exemplary proximal bearing seat.

[0051] After describing the overall structure of the blood pumping device, the specific structure of the first flow cavity in the blood pumping device will be described below with reference to the drawings. Combining Figures 2 to 4It can be seen that in some embodiments, the motor 10 further includes a proximal bearing seat 12 and a distal bearing seat 13, the proximal bearing seat 12 is connected to the proximal end of the stator assembly 11, the outer peripheral surface of the proximal bearing seat 12 includes a first step surface 121 and a second step surface 122 arranged along the first direction x, the first step surface 121 is located on the side of the second step surface away from the distal bearing seat 13, and the radial dimension of the first step surface 121 is greater than the radial dimension of the second step surface. The distal bearing seat 13 and the proximal bearing seat 12 are spaced apart along the first direction x, the distal bearing seat 13 is connected to the distal end of the stator assembly 11, and the outer peripheral surface of the distal bearing seat 13 includes a third step surface 131 and a fourth step surface 132 arranged along the first direction x, and the fourth step surface 132 is located on the side of the third step surface 131 away from the proximal bearing seat 12. The radial dimension of the fourth step surface 132 is equal to the radial dimension of the first step surface 121, and the radial dimension of the third step surface 131 is equal to the radial dimension of the second step surface 122. The circumferential surface of the winding 111 facing away from the core 112 overlaps the third step surface 131 and the second step surface 122 , and the circumferential surface of the core 112 facing the winding overlaps the fourth step surface 132 and the first step surface 121 .

[0052] The first direction x is the connection direction of the proximal end and the distal end of the motor 10. The two ends of the winding 111 in the first direction x are respectively sealed and connected to the overlap of the second step surface 122 and the third step surface 131, and the two ends of the iron core 112 in the first direction x are respectively sealed and connected to the overlap of the first step surface 121 and the fourth step surface 132, so that the perfusion liquid in the first flow cavity 114 will not leak from the overlap position of the winding 111, the iron core 112 and the proximal bearing seat 12, the distal bearing seat 13 to the accommodating cavity 113 or the outside of the motor 10.

[0053] It is explained here that the winding 111, the core 112, the proximal bearing seat 12 and the distal bearing seat 13 are all axisymmetric figures. The axial direction of the axisymmetric figure refers to the direction in which the central axis extends, that is, the direction x in the figure. The circumferential direction refers to the circumferential direction of the periphery of the axisymmetric figure. 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 the axisymmetric part. It can be understood that in this application, the axial, circumferential, radial and circumferential surfaces of other components can refer to the above-mentioned related descriptions. It is worth noting that some components are cylindrical structures, then these components 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.

[0054] The multiple step surfaces provided on the outer circumferential surface of the proximal bearing seat 12 refer to the circumferential surface of the proximal bearing seat 12 on the side away from the axis, which is provided with multiple bosses with different radial sizes, the outer circumferential surface of the boss is defined as the step surface, and the radial size refers to the diameter of the boss. The multiple step surfaces on the outer circumferential surface of the distal bearing seat 13 are similar.

[0055] The blood pumping device provided in this embodiment overlaps the iron core 112 with the first step surface 121 and the fourth step surface 132, overlaps the second step surface 122 and the third step surface 131 with the winding 111, and the radial dimensions of the first step surface 121 and the fourth step surface 132 are larger than the radial dimensions of the second step surface 122 and the third step surface 131, so that there is a gap between the winding 111 and the iron core 112 and a first flow cavity 114 is formed.

[0056] In some embodiments, the gap between the winding 111 and the iron core 112 forms the first flow cavity 114. It can also be understood that the first flow cavity 114 is an annular cavity between the winding 111 and the iron core 112.

[0057] In some embodiments, the first step surface 121 is provided with a first connecting groove 1211 extending along the first direction x, and the first connecting groove 1211 is directly or indirectly connected to the first pipe 20. The fourth step surface 132 is provided with a second connecting groove 1321 extending along the first direction x, and the second connecting groove 1321 is directly or indirectly connected to the second flow chamber 115.

[0058] In some embodiments, a plurality of first communication grooves 1211 are disposed on the first step surface 121, and the plurality of first communication grooves 1211 are disposed around the axis of the proximal bearing seat 12. A plurality of second communication grooves 1321 are disposed on the fourth step surface 132, and the plurality of second communication grooves 1321 are disposed around the axis of the distal bearing seat 13.

[0059] The blood pumping device provided in this embodiment has two ends of the iron core 112 respectively in contact with the first step surface 121 and the fourth step surface 132. By providing a first connecting groove 1211 on the first step surface 121 and a second connecting groove 1321 on the fourth step surface 132, the first connecting groove 1211 connects the first pipeline 20 and the first circulation cavity 114, and the second connecting groove 1321 connects the second circulation cavity 115 and the first circulation cavity 114.

[0060] In some of the embodiments, a connecting hole 123 connecting the first pipe 20 and the first connecting groove 1211 is provided on the proximal bearing seat 12, one of the openings of the connecting hole 123 is located on the end surface of the proximal bearing seat 12 facing away from the distal bearing seat 13, and the other opening of the connecting hole 123 is located on the first step surface 121 and connected to the first connecting groove 1211.

[0061] Among them, the opening of the communication hole 123 on the end face is axially aligned and sealed with the first pipeline 20. The connection between the communication hole 123 and the first pipeline 20 can adopt welding, gluing or other sealing methods.

[0062] In the blood pumping device provided in this embodiment, the first pipeline 20 and the first communication groove 1211 are communicated through the communication hole 123, and the communication hole 123 and the first flow cavity 114 are communicated through the first communication groove 1211, so as to realize the communication between the first flow cavity 114 and the first pipeline 20.

[0063] After describing the implementation manner of the first flow cavity in the blood pumping device, several implementation manners of the second flow cavity in the blood pumping device will be described below in conjunction with the accompanying drawings. Figure 2 As can be seen, in some embodiments, the motor 10 further includes a rotor assembly 14. The rotor assembly 14 includes a rotating shaft 141 and a magnetic steel 142 sleeved on the rotating shaft 141. The rotating shaft 141 extends along the first direction x. The magnetic steel 142 and at least a part of the rotating shaft 141 are located in the accommodation cavity 113. The winding 111 is sleeved on the magnetic steel 142, and the gap between the winding 111 and the rotor assembly 14 forms the second flow cavity 115.

[0064] In some embodiments, the accommodation cavity 113 is formed by surrounding the winding 111. The accommodation cavity 113 is used to accommodate components such as the magnetic steel 142 and bearings. The cavity remaining after removing the occupancy of components such as the magnetic steel 142 and bearings in the accommodation cavity 113 is the second flow cavity 115.

[0065] Figure 5 Show an example of Figure 2 The schematic cross-sectional structure diagram of the ventricular assist device in the A-A position in. In the figure, for the convenience of showing the structures of each flow cavity, the sizes of the structures in the figure are not necessarily in proportion to the structures in other accompanying drawings.

[0066] Combined with Figure 5 As can be seen, in other embodiments, a partition 116 is provided between the winding 111 and the iron core 112, so that the gaps between the winding 111 and the iron core 112 respectively form the first flow cavity 114 and the second flow cavity 115. Among them, the partition 116 divides the annular cavity formed between the winding 111 and the iron core 112 into at least two independent chambers, and at least one first flow cavity 114 and one second flow cavity 115 are included in the independent chambers.

[0067] Figure 6 Show another example of Figure 2 The schematic cross-sectional structure diagram of the ventricular assist device in the A-A position in. In the figure, for the convenience of showing the structures of each flow cavity, the sizes of the structures in the figure are not necessarily in proportion to the structures in other accompanying drawings.

[0068] Combined Figure 6 It can be seen that in some other embodiments, a second flow chamber 115 is formed by the gap between the winding 111 and the rotor assembly 14. A partition 116 is provided between the winding 111 and the iron core 112, so that the annular cavity formed between the winding 111 and the iron core 112 is at least divided into two independent chambers, and at least one first flow chamber 114 is included in the independent chambers. That is, the first flow chamber 114 in this embodiment is not an annular chamber.

[0069] Combined Figure 2 It can be seen that in some of these embodiments, the motor 10 further includes a distal bearing 15 and a proximal bearing 16, and both the distal bearing 15 and the proximal bearing 16 are sleeved on the rotating shaft 141. The distal bearing 15 communicates with the first flow chamber 114 and the second flow chamber 115, and the proximal bearing 16 communicates with the second flow chamber 115 and the second pipe 30. The rotating shaft 141 is rotatably connected to the stator assembly 11 through the distal bearing 15 and the proximal bearing 16, and the distal bearing 15 is located on the side of the proximal bearing 16 away from the first pipe 20.

[0070] In some of these embodiments, the distal bearing 15 and the proximal bearing 16 can be sliding bearings or ball bearings. In some implementation manners, the distal bearing 15 and the proximal bearing 16 are ball bearings, and gaps allowing the perfusion liquid to pass through are provided on the distal bearing 15 and the proximal bearing 16, such as the gaps between the balls. The perfusion liquid located on both sides of the bearing in the axial direction can flow through the gaps on the bearing. For example, the perfusion liquid flowing from the first flow chamber 114 into the accommodation chamber 113 flows out from the second pipe 30 after passing through the distal bearing 15 and the proximal bearing 16 in sequence, or the perfusion liquid flowing in from the second pipe 30 flows out from the first flow chamber 114 after passing through the proximal bearing 16 and the distal bearing 15 in sequence. In some alternative implementation manners, the distal bearing 15 and the proximal bearing 16 are sliding bearings, and gaps allowing the perfusion liquid to pass through are formed between the distal bearing 15 and other components (such as a bearing housing), and gaps allowing the perfusion liquid to pass through are formed between the proximal bearing 16 and other components (such as a bearing housing). In some other alternative implementation manners, one of the distal bearing 15 and the proximal bearing 16 is a ball bearing and the other is a sliding bearing, and the specific solution can be a combination of the first two implementation manners.

[0071] In the blood pumping device provided in this embodiment, when the perfusion liquid flows through the distal bearing 15 and / or the proximal bearing 16, it can carry away the particles generated during the rotation of the bearing, reduce the bearing wear, and thus improve the service life of the motor 10.

[0072] Figure 7 Shows a schematic structural diagram of an exemplary distal cap.

[0073] Combined Figure 2 and Figure 7It can be seen that in some of the embodiments, the motor 10 further includes a distal end cap 17, which is connected to the distal end of the stator assembly 11. The distal end cap 17 is provided with a first through hole 171 that penetrates the distal end cap 17 along the first direction x. At least a part of the rotating shaft 141 extends out of the accommodating cavity 113 through the first through hole 171. The distal end cap 17 is used to seal the distal end of the accommodating cavity 113. There is a gap between the distal end cap 17 and the distal bearing seat 13 in the first direction x, and the gap between the distal bearing seat 13 and the distal end cap 17 forms a third flow cavity 18. The third flow cavity 18 communicates with the first flow cavity 114 and the second flow cavity 115. The two end faces of the distal bearing 15 in the first direction x face the second flow cavity 115 and the third flow cavity 18 respectively.

[0074] The radial dimension of the first through hole 171 is slightly larger than the radial dimension of the rotating shaft 141, so that the perfusion liquid in the third flow cavity 18 can flow into and out of the flow channel 40 through the gap between the first through hole 171 on the distal end cap 17 and the rotating shaft 141, and can also flow into the second flow cavity 115 through the gap between the balls on the distal bearing 15. By setting the radial dimension of the first through hole 171, most of the perfusion liquid can be controlled to flow to the distal bearing 15, and a small part of the perfusion liquid is used to balance the pressure difference between the positions of the flow channel 40 and the third flow cavity 18, reducing the total amount of blood flowing into the motor 10 at the flow channel 40 and reducing the probability of blood clot formation in the motor 10.

[0075] In some of the embodiments, the distal end outer shape of the distal end cap 17 is a conical streamline surface. In the working state, the conical streamline surface can be used as a blood flow-through surface.

[0076] In some of the embodiments, an impeller 42 is provided in the flow channel 40 of the blood pumping device. After the rotating shaft 141 extends out of the accommodating cavity 113 through the first through hole 171, it is connected to the impeller 42. When the motor 10 is started, the rotating shaft 141 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.

[0077] In some of the embodiments, the first pipe 20 is a perfusion pipe, and the second pipe 30 is a return pipe. The perfusion liquid in the first pipe 20 flows through the first flow cavity 114, the third flow cavity 18, the distal bearing 15, the second flow cavity 115, and the proximal bearing 16 in sequence and then flows out of the motor 10 through the second pipe 30.

[0078] The blood pumping device provided in this embodiment can carry away the particles generated during the rotation of the bearings when the perfusion fluid flows through the distal bearing 15 and the proximal bearing 16, effectively reducing the particles generated during the operation of the motor 10 from entering the human body, reducing the total amount of perfusion fluid flowing into the patient, and further reducing the total amount of particles flowing into the patient, thereby improving the product safety. By making the first pipe 20 the perfusion pipe and the second pipe 30 the return pipe, the perfusion fluid will first enter the third flow chamber 18 from the first flow chamber 114, and then flow out from the second pipe 30 after flushing the bearings, so that the particle content in the perfusion fluid at the third flow chamber 18 is extremely low, reducing the total amount of particles flowing into the patient from the first through hole 171.

[0079] Combined with Figure 2 and Figure 4 it can be seen that in some embodiments, the proximal bearing seat 12 is provided with a first mounting hole 124 that penetrates the proximal bearing seat 12 along the first direction x, and the proximal bearing 16 is embedded in the first mounting hole 124. The distal bearing seat 13 is provided with a second mounting hole 133 that penetrates the distal bearing seat 13 along the first direction x, and the distal bearing 15 is embedded in the second mounting hole 133. Among them, the first mounting hole 124 communicates with the second flow chamber 115 and the second pipe 30, and the second mounting hole 133 communicates with the third flow chamber 18 and the second flow chamber 115.

[0080] It can be understood that the proximal bearing 16 being embedded in the first mounting hole 124 means that the outer peripheral surface of the proximal bearing 16 is embedded in the circumferential surface of the proximal bearing seat 12 facing the first mounting hole 124 and fixedly connected. At the same time, the inner peripheral surface of the proximal bearing 16 is sleeved on the rotating shaft 141 and fixedly connected to the rotating shaft 141. The same applies to the distal bearing 15.

[0081] Combined with Figure 2 and Figure 3 it can be seen that in some embodiments, the circumferential surface of the distal bearing seat 13 facing the second mounting hole 133 includes a fifth step surface 1331 and a sixth step surface 1332, and the fifth step surface 1331 is located on the side of the sixth step surface 1332 away from the proximal bearing seat 12. The radial dimension of the fifth step surface 1331 is larger than the radial dimension of the sixth step surface 1332, and the distal bearing 15 is embedded in the fifth step surface 1331. The perfusion fluid in the third flow chamber 18 first flows through the distal bearing 15 and then flows into the second flow chamber 115 through the second mounting hole 133 where the sixth step surface 1332 is located.

[0082] Among them, the multiple step surfaces on the circumferential surface of the distal bearing seat 13 facing the second mounting hole 133 refer to that there are multiple through holes with different radial dimensions on the circumferential surface, and the hole surface (inner circumferential surface) of the through hole is defined as the step surface, and the radial dimension refers to the aperture of the through hole.

[0083] The blood pumping device provided in this embodiment makes the radial dimension of the fifth step surface 1331 larger than that of the sixth step surface 1332. The side wall of the sixth step surface 1332 facing the fifth step surface 1331 will abut against the distal bearing 15, restricting the movement of the distal bearing 15 in the first direction x, thereby improving the connection stability between the distal bearing 15 and the distal bearing seat 13.

[0084] Combined with Figure 2 and Figure 4 It can be known that in some embodiments, a seventh step surface 125 is further provided on the circumferential surface of the proximal bearing seat 12 facing away from the first mounting hole 124. The seventh step surface 125 is located on the side of the first step surface 121 facing away from the second step surface 122, and the radial dimension of the seventh step surface 125 is larger than that of the first step surface 121. The proximal end of the iron core 112 abuts against the side wall of the seventh step surface 125 facing the first step surface 121. The intervention catheter 50 is directly or indirectly connected to the seventh step surface 125.

[0085] The blood pumping device provided in this embodiment restricts the movement of the iron core 112 in the first direction x by providing the seventh step surface 125 on the proximal bearing seat 12 and making the proximal end of the iron core 112 abut against the side wall of the first mounting hole 124 where the seventh step surface 125 is located, thereby improving the connection stability between the iron core 112 and the proximal bearing seat 12.

[0086] In some embodiments, a wire groove 126 recessed towards the axis of the proximal bearing seat 12 is further provided on the circumferential surface of the proximal bearing seat 12 facing away from the first mounting hole 124. The wire groove 126 extends from the seventh step surface 125 to the first step surface 121 in the first direction x. The wire harness of the winding 111 extends into the intervention catheter 50 through the wire groove 126 and is connected to an external power supply device and a control device.

[0087] Figure 8 Shows a schematic structural diagram of an exemplary proximal cap.

[0088] Combined body Figure 2 and Figure 8 It can be known that in some embodiments, the motor 10 further includes a proximal cap 19. The proximal cap 19 is connected to the opening on the side of the communication hole 123 facing the first pipe 20, and the proximal cap 19 is used to seal the communication hole 123. A second through hole 191 penetrating the proximal cap 19 in the first direction x is provided on the proximal cap 19. The second through hole 191 communicates the first pipe 20 and the communication hole 123, and the first pipe 20 is connected to the second through hole 191.

[0089] In some embodiments, the materials of the proximal cover 19 and the distal cover 17 include metal and non-metal. The materials of the proximal cover 19 and the distal cover 17 can be the same or different, and the material of the proximal cover 19 and the distal cover 17 is preferably 316 stainless steel.

[0090] In some of the embodiments, the connection between the first pipe 20 and the second through hole 191 and the connection between the second pipe 30 and the first mounting hole 124 may be welded, glued or sealed in other ways.

[0091] Figure 9 A schematic diagram of the structure of a second pipeline of an example is shown.

[0092] Combination Figure 2 and Figure 9 It can be seen that in some of the embodiments, the first pipe 20 and the second pipe 30 can be straight tubes or other special-shaped tubes, and the present application does not make specific limitations on this. In addition, for the return pipe, a notch 31 is provided at the proximal end of the return pipe, and the number of the notches 31 can be at least one. When the number of notches 31 is two or more, the plurality of notches 31 are symmetrically or asymmetrically arranged along the circumferential direction. The notch 31 is used to connect with a support wire (not shown) at least partially located in the return pipe. After the support wire is embedded in the notch 31, it is connected to the return pipe by laser welding or gluing at the embedded position, thereby further improving the connection strength between the return pipe and the motor 10.

[0093] Figure 10 A schematic structural diagram of an exemplary iron core is shown.

[0094] Combination Figure 2 and Figure 10 It can be seen that in some embodiments, an eighth step surface 1121 and a ninth step surface 1122 are provided on the circumferential surface of the iron core 112 away from the axis, and the eighth step surface 1121 is located on the side of the ninth step surface 1122 away from the proximal bearing seat 12. The radial dimension of the eighth step surface 1121 is smaller than the radial dimension of the ninth step surface 1122, and the outflow channel 40 overlaps the eighth step surface 1121.

[0095] The multiple step surfaces on the circumferential surface of the core 112 away from the axis side refer to multiple bosses with different radial sizes on the circumferential surface, the outer circumferential surface of the boss is defined as the step surface, and the radial size refers to the diameter of the boss.

[0096] The blood pumping device provided in this embodiment reduces the radial dimension of the overlapping position of the outflow channel 40 and the motor 10 by making the radial dimension of the eighth step surface 1121 smaller than the radial dimension of the ninth step surface 1122 and the outflow channel 40 overlaps the eighth step surface 1121, thereby reducing the intervention size of the ventricular assist device and reducing the difficulty of intervention of the ventricular assist device.

[0097] In some of these embodiments, the motor 10 further includes a housing (not shown), the housing is sleeved outside the iron core 112, and at least a part of the housing is in contact with the ninth step surface 1122.

[0098] It can be understood that the components in contact with the human body and blood in the above blood pumping device need to be made of biocompatible materials, which can be metal or non-metal. For example, when these components are metal, they can be made of 316 stainless steel.

[0099] In some other embodiments, the iron core 112 can also be used as the outer shell of the motor 10 and 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 and intervention difficulty of the motor 10.

[0100] 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 iron core 112 and the proximal bearing seat 12 are integrally formed. For another example, the iron core 112 and the distal bearing seat 13 are integrally formed. For yet another example, the iron core 112 and the distal end cover 17 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 the present application.

[0101] In some alternative embodiments, the present application further provides a liquid pumping device for transporting body fluids other than blood. The liquid pumping device includes a motor 10, a first pipe 20, and a second pipe 30. The motor 10 includes a stator assembly 11. The stator assembly 11 includes a winding 111 and an iron core 112 sleeved outside the winding 111. An accommodation cavity 113 is provided in the winding 111. A first flow cavity 114 is formed in the gap between the winding 111 and the iron core 112. A second flow cavity 115 is provided in the accommodation cavity 113 and / or a second flow cavity 115 is further formed in the gap between the winding 111 and the iron core 112. The second flow cavity 115 is independent of and communicated with the first flow cavity 114. The first pipe 20 is communicated with the first flow cavity 114, and the second pipe 30 is communicated with the second flow cavity 115. One of the first pipe 20 and the second pipe 30 is a perfusion pipe, and the other is a reflux pipe. Wherein, the perfusion pipe is used to transport perfusion liquid into the motor 10, and the reflux pipe is used to discharge the perfusion liquid in the motor 10.

[0102] In some of these embodiments, the body fluid includes tissue fluid, digestive fluid, etc.

[0103] 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, which will not be elaborated here too much.

[0104] In addition, the present application further provides a motor, which includes a stator assembly. The stator assembly includes a winding and an iron core sleeved outside the winding. An accommodation cavity is provided in the winding, and a first flow cavity is formed by the gap between the winding and the iron core. A second flow cavity is provided in the accommodation cavity and / or a second flow cavity is further formed by the gap between the winding and the iron core. The first flow cavity and the second flow cavity are independent of each other and communicate with each other. One of the first flow cavity and the second flow cavity is used to communicate with a perfusion pipeline, and the other is used to communicate with a reflux pipeline. The perfusion pipeline is used to convey a perfusion liquid into the motor, and the reflux pipeline is used to discharge the perfusion liquid in the motor.

[0105] It can be understood that the motor provided by the present application can be the motor in any one of the foregoing blood pumping devices and liquid pumping devices, and will not be described repeatedly here.

[0106] As described above, the foregoing are only specific embodiments 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 systems, modules, and units described above can refer to the corresponding processes in the foregoing method embodiments, and will not be elaborated here. It should be understood that the protection scope of the present application is not limited thereto. Any person skilled in the art can easily think of various equivalent modifications or substitutions within the technical scope disclosed by the present application, and these modifications or substitutions should all be covered within the protection scope of the present application.

Claims

1. A blood pumping device for conveying blood, characterized in that: include: A motor, comprising a stator assembly, wherein the stator assembly comprises a winding and an iron core sleeved outside the winding, wherein a receiving cavity is provided in the winding, a gap between the winding and the iron core forms a first flow cavity, a second flow cavity is provided in the receiving cavity and / or the gap between the winding and the iron core also forms a second flow cavity, and the second flow cavity is independent of and connected to the first flow 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 into 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, characterized in that: The motor further comprises a rotor assembly, at least a portion of which is located in the accommodating cavity, and a gap between the winding and the rotor assembly forms the second flow cavity.

3. The blood pumping device according to claim 2, characterized in that: The motor also includes: A proximal bearing seat connected to the proximal end of the stator assembly, wherein the outer peripheral surface of the proximal bearing seat comprises a first step surface and a second step surface arranged along a first direction; A distal bearing seat is connected to the distal end of the stator assembly, and the outer circumferential surface of the distal bearing seat includes a third step surface and a fourth step surface arranged along a first direction, the circumferential surface of the winding facing away from the iron core overlaps the third step surface and the second step surface, and the circumferential surface of the iron core facing the winding overlaps the fourth step surface and the first step surface; wherein the first direction is the connection direction of the proximal end and the distal end of the motor.

4. The blood pumping device according to claim 3, characterized in that: A first communicating groove is provided on the first step surface and extends along the first direction, and the first communicating groove is communicated with the first pipeline; The fourth step surface has a second communicating groove extending through the first direction, wherein the second communicating groove is connected to the second flow chamber.

5. The blood pumping device according to claim 4, characterized in that: The proximal bearing seat is provided with a connecting hole connecting the first pipeline and the first connecting groove, one of the openings of the connecting hole is located on the end surface of the proximal bearing seat away from the distal bearing seat, and the other opening of the connecting hole is connected to the first connecting groove.

6. The blood pumping device according to claim 3, characterized in that: The rotor assembly comprises a rotating shaft and a magnetic steel sleeved on the rotating shaft, the rotating shaft extends along the first direction, the magnetic steel and at least a part of the rotating shaft are located in the accommodating cavity, and the winding is sleeved on the magnetic steel; The motor also includes: A distal bearing, sleeved on the rotating shaft; A distal cover, wherein the distal cover is connected to the distal end of the stator assembly, and the distal cover is provided with a first through hole penetrating the distal cover along the first direction, and 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 gap is formed 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.

7. The blood pumping device according to claim 6, characterized in that: The motor also includes: A proximal bearing is sleeved on the rotating shaft, the proximal bearing is connected to the second flow chamber and the second pipeline, 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 pipeline.

8. The blood pumping device according to claim 1, characterized in that: A partition is provided between the winding and the iron core, so that the gap between the winding and the iron core forms the first flow cavity and the second flow cavity respectively.

9. The blood pumping device according to claim 1, characterized in that: The first pipeline is a perfusion pipeline, and the second pipeline is a return pipeline.

10. A motor, characterized in that: The invention comprises a stator assembly, wherein the stator assembly comprises a winding and an iron core sleeved outside the winding, wherein a receiving cavity is arranged inside the winding, a gap between the winding and the iron core forms a first flow cavity, a second flow cavity is arranged inside the receiving cavity and / or the gap between the winding and the iron core also forms the second flow cavity, the first flow cavity and the second flow cavity are independent of each other and are connected, one of the first flow cavity and the second flow cavity is used to be connected with a perfusion pipe, and the other is used to be connected with a return pipe, the perfusion pipe is used to transport perfusion liquid into the motor, and the return pipe is used to discharge the perfusion liquid in the motor.

Images