Pump body and intrusive catheter pump system

Abstract

The invention discloses a pump body and an intrusive catheter pump system. The pump body comprises a guide pipe; the rotating shaft comprises a first section and a second section which are connected, the first section is arranged in the guide pipe, the second section extends out of the guide pipe along an outlet of the guide pipe, the rotating shaft can rotate relative to the guide pipe, a gap is formed between the rotating shaft and the outlet of the guide pipe, and the inner side and the outer side of the guide pipe are communicated through the gap; the impeller is connected with the second section and is spaced from the guide pipe; the rotating shaft can drive the impeller to rotate; the pressure component is connected with the second section, the pressure component is located between the guide pipe and the impeller and corresponds to the gap, the rotating shaft can drive the pressure component to rotate, and the pressure component generates centrifugal force. According to the pump body and the intrusive catheter pump system provided by the embodiment of the invention, the condition that blood flows backwards into the catheter can be effectively reduced.

Description

Technical Field

[0001] This application belongs to the technical field of medical devices, and particularly relates to a pump body and an interventional catheter pump system. Background Art

[0002] The interventional catheter pump system mainly includes an interventional component and a pump body that are connected. The interventional component is percutaneously inserted into the artery and pushed into the left ventricle of the patient. The pump body is used to pump the blood in the left ventricle to the aorta to maintain the intraoperative hemodynamic level of the patient. Existing catheter pumps can be divided into two categories: one is that an in-vivo motor directly drives the impeller through a connecting shaft, and the other is that an external motor drives the impeller through a flexible shaft. For both types of catheter pumps driven in these ways, wear, vibration, and heat generation will occur due to the high-speed rotation of the bearings and transmission shafts. To reduce these adverse factors, physiological fluids, such as normal saline or glucose solution, are usually poured between the transmission shaft and the catheter.

[0003] Generally, a connector is provided on the external part of the catheter for connecting a perfusion device to send the liquid from the outside to the catheter pump through the catheter. A blood channel and a perfusion liquid channel capable of transporting, for example, normal saline or glucose solution are formed in the pump body, and the outlet of the blood channel is communicated with the outlet of the perfusion liquid channel. However, during the process of the impeller pumping blood, the pressure outside the outlet of the perfusion liquid channel will also increase, resulting in the pressure outside the outlet of the perfusion liquid channel being easily greater than the pressure inside the perfusion liquid channel, causing blood to backflow into the perfusion liquid channel and affecting the safety of the patient. Summary of the Invention

[0004] The embodiments of this application provide a pump body and an interventional catheter pump system, which can effectively reduce the backflow of blood into the catheter.

[0005] On the one hand, the embodiments of this application provide a pump body, wherein the pump body includes:

[0006] A catheter;

[0007] A rotating shaft, including a first section and a second section that are connected. The first section is disposed inside the catheter, and the second section extends out of the catheter along the outlet of the catheter to the outside of the catheter. The rotating shaft can rotate relative to the catheter, and a gap is provided between the rotating shaft and the outlet of the catheter, and the inside and outside of the catheter are communicated through the gap;

[0008] An impeller, connected to the second section and spaced from the catheter, and the rotating shaft can drive the impeller to rotate;

[0009] A pressure member, connected to the second section, and the pressure member is located between the catheter and the impeller and corresponds to the gap. The rotating shaft can drive the pressure member to rotate and the pressure member generates centrifugal force.

[0010] The pump body as described above, wherein the pressure member is fixedly connected to the impeller.

[0011] The pump body as described above, wherein the pressure member is a centrifugal blade; a plurality of the centrifugal blades are provided, and the centrifugal blades are arranged at intervals along the circumference of the impeller.

[0012] The pump body as described above, wherein the centrifugal blade is a radial blade, the inlet angle of the radial blade is 30° to 50°, and the outlet angle of the radial blade is 90°.

[0013] The pump body as described above, wherein the centrifugal blade is a backward curved blade, the inlet angle of the backward curved blade is 20° to 30°, the outlet angle of the backward curved blade is less than 90°, and the outlet angle of the backward curved blade is greater than the inlet angle of the backward curved blade.

[0014] The pump body as described above, wherein the outlet angle of the backward curved blade is 25° to 45°.

[0015] The pump body as described above, wherein the centrifugal blade is a forward curved blade, the inlet angle of the forward curved blade is 40° to 70°, and the outlet angle of the forward curved blade is greater than 90°.

[0016] The pump body as described above, wherein the outlet angle of the forward curved blade is 150° to 180°.

[0017] The pump body as described above, wherein the number of the centrifugal blades is 4 to 8, and along the axial direction of the rotating shaft, the size of the centrifugal blade is 0.05 mm to 0.15 mm.

[0018] The pump body as described above, wherein along the axial direction of the conduit, the distance between the pressure member and the conduit is 0.05 mm to 0.2 mm.

[0019] On the other hand, the embodiment of the present application provides an interventional catheter pump system, wherein the interventional catheter pump system includes the pump body as described in the above aspect.

[0020] For the pump body and the interventional catheter pump system of the embodiment of the present application, by arranging a pressure member between the impeller and the conduit, when the rotating shaft drives the impeller to rotate to cause the pressure outside the outlet of the conduit to increase, the rotating shaft can drive the pressure member to generate a centrifugal force, and the centrifugal force is balanced with the increase in the pressure at the tail of the impeller (outside the outlet of the conduit) caused by the work done by the impeller, so that the pressure member plays a role in sucking at the gap between the rotating shaft and the outlet of the conduit, thereby reducing the backflow of the liquid at the tail of the impeller into the gap and the inside of the conduit. Description of the Drawings

[0021] To more clearly illustrate the technical solutions of the embodiments of the present application, the following will briefly introduce the drawings required for use in the embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0022] Figure 1 Structural schematic diagram of the pump body of the embodiment of the present application;

[0023] Figure 2 Structural schematic diagram of the impeller of the pump body of the embodiment of the present application;

[0024] Figure 3 Structural schematic diagram of the centrifugal blade of the embodiment of the present application being a radial blade;

[0025] Figure 4 Structural schematic diagram of the centrifugal blade of the embodiment of the present application being a backward-curved blade;

[0026] Figure 5 Structural schematic diagram of the centrifugal blade of the embodiment of the present application being a forward-curved blade.

[0027] Explanation of the reference numerals in the drawings:

[0028] 1. Conduit; 11. Outlet; M. Extension pipe; 21. Rotating shaft; 211. First section; 212. Second section; 22. Bearing housing end cover; 23. Bearing; 3. Impeller; 4. Pressure member; 41. Centrifugal blade; β1. Inlet angle; β2. Outlet angle;

[0029] 5. Perfusion liquid channel; 51. First sub-channel; 52. Second sub-channel; 53. Third sub-channel; 54. Fourth sub-channel; 6. Flow-through space;

[0030] 7. First pipe body; 8. Second pipe body; 91. Liquid inlet channel; 92. Liquid discharge channel. Detailed implementation manners

[0031] 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 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, rather than limiting the present application. For those skilled in the art, the present application can be implemented without some of these specific details. It should be noted that unless otherwise specified, the technical terms or scientific terms used in the embodiments of the present application should be the ordinary meanings understood by those skilled in the art to which the embodiments of the present application belong. For example, the "distal end" refers to the end away from the operator or physician, and the "proximal end" refers to the end close to the operator or physician. The following description of the embodiments is only to provide a better understanding of the present application by showing examples of the present application.

[0032] As Figure 1 shown, an embodiment of the present application provides a pump body, wherein the pump body includes a catheter 1, a rotating assembly 2, an impeller 3, and a pressure member 4.

[0033] The catheter 1 includes a hollow tubular structure and an outlet 11.

[0034] The rotating shaft 21 includes a first section 211 and a second section 212 connected to each other. Specifically, the first section 211 and the second section 212 are integrally formed. The first section 211 is disposed inside the catheter 1, and the second section 212 extends to the outside of the catheter 1 along the outlet 11 of the catheter 1. The rotating shaft 21 can rotate relative to the catheter 1, and there is a gap between the rotating shaft 21 and the outlet 11 of the catheter 1. The inside and outside of the catheter 1 are communicated through the gap.

[0035] It can be understood that a perfusion fluid channel 5 for the perfusion fluid to flow is included between the catheter 1 and the first section 211. It should be noted that the specific structure of the perfusion fluid channel can be designed according to the structure provided inside the catheter 1 as long as the effect of allowing the perfusion fluid to flow through can be achieved.

[0036] The impeller 3 is connected to the second section 212 and is spaced from the catheter 1. An overflow space 6 is formed on the circumferential side of the part of the second section 212 not connected to the impeller 3 and the circumferential side of the impeller 3; optionally, an extension tube M is further included, and at least a part of the second section 212 and at least a part of the impeller 3 are disposed inside the extension tube M. An overflow space 6 is formed between the part of the second section 212 disposed inside the extension tube M and the extension tube M and between the part of the impeller 3 disposed inside the extension tube M and the extension tube M; the overflow space 6 is communicated with the gap, and the overflow space 6 is the pipeline channel for the pump body to pump blood. The motor of the interventional catheter pump can be disposed either inside the catheter 1 or drive the impeller through a flexible shaft. The rotating shaft 21 can drive the impeller 3 to rotate and pump blood into the aorta of the patient.

[0037] The pressure member 4 is connected to the second section 212, and the pressure member 4 is located between the conduit 1 and the impeller 3 and corresponds to the gap. The rotating shaft 21 can drive the pressure member 4 to rotate and generate centrifugal force, which balances the pressure increase at the tail of the impeller 3 (outside the outlet 11 of the conduit 1) caused by the work done by the impeller 3. Thus, the pressure member 4 plays a role in sucking at the gap between the rotating shaft 21 and the outlet of the conduit 1, thereby reducing the backflow of the liquid at the tail of the impeller 3 into the gap and the inside of the conduit 1.

[0038] As Figure 1 shown, for the pump body provided in the present application, the conduit 1 further includes a bearing housing end cover 22 and a bearing 23.

[0039] The bearing housing end cover 22 is positioned at the end of the conduit 1, and the second section 212 extends from the outlet 11 of the bearing housing end cover 22 to the outside of the conduit 1. The rotating shaft 21 can rotate relative to the conduit 1, and there is a gap between the rotating shaft 21 and the outlet of the conduit 1. The inside and outside of the conduit 1 are communicated through the gap.

[0040] The first section 211 of the rotating shaft 21 is rotationally connected to the bearing 23 to reduce the frictional force received during the rotation of the rotating shaft 21, reduce the wear of the rotating shaft 21 and the bearing housing end cover 22, and ensure the service life and use safety of both. Since the rotating shaft 21 needs to extend out of the conduit 1 to be connected to the impeller 3, a certain gap needs to be left between the bearing housing end cover 22 and the rotating shaft to prevent friction between the rotating shaft 21 and the bearing housing end cover 22 during rotation.

[0041] Optionally, the perfusion liquid channel 5 includes a first sub-channel 51, a second sub-channel 52, a third sub-channel 53, and a fourth sub-channel 54.

[0042] The first sub-channel 51 is formed between the bearing housing end cover 22 and the conduit 1, and can be an annular channel or a strip channel, and the first sub-channel 51 is communicated with the outside of the conduit 1; for the perfusion liquid outside the conduit 1 to enter the inside of the conduit 1;

[0043] The second sub-channel 52 is formed inside the bearing housing end cover 22 and extends along the radial direction of the rotating shaft 21. The second sub-channel 52 is communicated with the first sub-channel 51, and the perfusion liquid will enter the second sub-channel 52 after flowing through the first sub-channel 51;

[0044] The third sub-channel 53 is formed between the bearing housing end cover 22 and the rotating shaft 21, and the third sub-channel 53 is respectively communicated with the outside of the catheter 1 and the second sub-channel 52; by providing the third sub-channel 53, a part of the perfusion liquid can flow back to the outside of the catheter 1; since relative friction will be generated between the rotating shaft 21 and the mating components during rotation, more or less wear particles will be generated and heat will be generated. By providing the third sub-channel 53, when the perfusion liquid flows back to the outside of the catheter 1 through the third sub-channel 53, the wear particles can be carried out to the outside of the catheter 1 and the rotating shaft 21 can be cooled;

[0045] The fourth sub-channel 54 is formed between the bearing housing end cover 22 and the rotating shaft 21, and the fourth sub-channel 54 is respectively communicated with the second sub-channel 52 and the gap. By providing the fourth sub-channel 54, a part of the perfusion liquid can flow into the communication area 12 through the fourth sub-channel 54 and the gap.

[0046] It can be understood that the perfusion liquid supply channel is formed by the first sub-channel 51 and the second sub-channel 52, the recovery channel is formed by the third sub-channel 53, and the drainage channel to the human body is formed by the fourth sub-channel 54. It should be noted that the perfusion liquid channel 5 can have a variety of different installation positions, and the specific structure is designed according to the space inside the catheter 1. The present application is not limited thereto.

[0047] Optionally, as Figure 1 shown, the pump body provided by the present application further includes a first pipe body 7 and a second pipe body 8. The first pipe body 7 is coaxially sleeved outside the second pipe body 8. The first pipe body 7 is connected to the end of the catheter 1, and the second pipe body 8 is connected to the end of the bearing housing end cover 22 away from the impeller 3. An inlet liquid channel 91 is formed between the first pipe body 7 and the second pipe body 8. The inlet liquid channel 91 is respectively communicated with the first sub-channel 51 and the perfusion liquid supply device to realize the supply of the perfusion liquid; a drainage liquid channel 92 is formed inside the second pipe body 8. The drainage liquid channel 92 is respectively communicated with the third sub-channel 53 and the perfusion liquid recovery device to realize the recovery of the perfusion liquid.

[0048] Optionally, the first pipe body 7 is a sheath pipe and the second pipe body 8 is a heat shrinkable pipe.

[0049] The impeller 3 and the bearing housing end cover 22 are arranged at intervals to prevent the impeller 3 and the bearing housing end cover 22 from contacting and wearing each other during the rotation of the impeller 3.

[0050] In the pump body provided by the present application, the pressure member 4 is fixedly connected to the impeller 3 to ensure that the pressure member 4 and the impeller 3 have the same rotation speed, so as to simultaneously adjust the pressures of the perfusion liquid channel 5 and the flow-through space 6 and ensure pressure balance.

[0051] Optionally, the pressure member 4 is integrally formed and connected to the side of the impeller 3 facing the bearing housing end cover 22, which has the advantage of being convenient for processing.

[0052] As Figures 2 to 5 shown, for the pump body provided by the present application, wherein the pressure member 4 is a centrifugal blade 41; a plurality of centrifugal blades 41 are provided, and the centrifugal blades 41 are arranged at intervals along the circumferential direction of the impeller 3 to ensure its suction effect. When the number of blades is insufficient, the centrifugal suction effect is poor, and it is impossible to effectively prevent the blood from flowing back into the catheter 1; when the number of blades is too large, the impeller will occupy too much space, and the perfusion fluid may not flow out normally at a low rotational speed.

[0053] As Figure 3 and Figure 5 shown, for the pump body provided by the present application, wherein the centrifugal blade 41 is a radial blade, the inlet angle β1 of the radial blade is 30° to 50°, and the outlet angle β2 of the radial blade is 90°. Optionally, when the radial blade is at the same angle as the impeller outflow angle, the pressure balance effect is the best.

[0054] Alternatively, the centrifugal blade 41 is a backward curved blade, the inlet angle β1 of the backward curved blade is 20° to 30°, the outlet angle β2 of the backward curved blade is less than 90°, and the outlet angle β2 of the backward curved blade is greater than the inlet angle β1 of the backward curved blade. Optionally, the outlet angle β2 of the backward curved blade is 25° to 45°.

[0055] Alternatively, the centrifugal blade 41 is a forward curved blade, the inlet angle β1 of the forward curved blade is 40° to 70°, and the outlet angle β2 of the forward curved blade is greater than 90°. Optionally, the outlet angle β2 of the forward curved blade is 150° to 180°.

[0056] The inlet angle β1 of the centrifugal blade 41 is the angle between the tangent line at its starting position and the circumferential direction at that position, and the outlet angle β2 of the centrifugal blade 41 is the angle between the tangent line at its tail and the circumferential direction at that position.

[0057] When the above-mentioned various types of centrifugal blades 41 are adopted and their inlet angles and outlet angles meet the above-mentioned angle requirement ranges, it can effectively ensure that the centrifugal blades 41 can generate a suction effect and prevent the blood in the overflow space 6 from flowing back into the interior of the perfusion fluid channel 5.

[0058] As Figures 3 to 5 shown, for the pump body provided by the present application, wherein the number of centrifugal blades 41 is 4 to 8. On the one hand, it can ensure the suction effect of the liquid at the gap between the outlet of the catheter 1 and the rotating shaft 21 during the rotation of the centrifugal blades 41. On the other hand, it can ensure that the space occupied by the centrifugal blades 41 will not affect the flow of the perfusion fluid, and ensure that the perfusion fluid can still flow out smoothly from the gap at a low rotational speed of the centrifugal blades 41.

[0059] Axially along the rotating shaft 21, the size of the centrifugal blade 41 is from 0.05 mm to 0.15 mm, which can minimize the impact on the assembly of the impeller 3 while ensuring the suction capacity. When the number of blades is small, the blade height can be appropriately increased.

[0060] Axially along the catheter 1, the distance between the pressure member 4 and the catheter 1 is from 0.05 mm to 0.2 mm; to ensure the smooth flow of the perfusion fluid.

[0061] Optionally, the outer diameter of the centrifugal blade 41 should be the same as the maximum outer diameter at the bottom of the hub of the impeller 3, and the inner diameter of the centrifugal blade 41 should also be as close as possible to the outer diameter of the rotating shaft 21. Axially along the rotating shaft 21, the distance between the pressure member 4 and the catheter 1 is the same as the size of the centrifugal blade 41 to ensure the best centrifugal suction effect.

[0062] On the other hand, the embodiment of the present application provides an interventional catheter pump system, wherein the interventional catheter pump system includes the pump body described in the above aspect.

[0063] In the interventional catheter pump system of the embodiment of the present application, through percutaneous intervention of the femoral artery / axillary artery, it crosses the aortic valve of the heart and enters the left ventricle. After reaching the working position of the left ventricle, the power source drives the rotating shaft to drive the impeller to rotate, and the impeller 3 rotates to pump blood from the left ventricle into the aorta. To solve the problems of wear, vibration and heat generation caused by the high-speed rotation of the bearings and the rotating shaft in the catheter 1, the interventional catheter pump system further includes a perfusion passage, and at least part of the perfusion fluid flows out from the gap between the rotating shaft 21 and the outlet of the catheter 1 and flows into the human body. During the process of pumping blood by the impeller, it will also increase the pressure outside the outlet 11 of the catheter 1, resulting in the blood pressure outside the outlet 11 of the catheter 1 being greater than the pressure of the perfusion fluid inside the catheter 1, causing blood to backflow into the perfusion fluid channel. By arranging the pressure member 4 at the gap between the rotating shaft 21 and the outlet of the catheter 1, when the rotating shaft 21 drives the impeller 3 to rotate, resulting in an increase in the pressure in the flow-through space 6, the rotating shaft 21 can drive the pressure member 4 to generate a suction effect on the gap between the rotating shaft 21 and the outlet of the catheter 1, so that the pressure in the gap tends to balance with the pressure in the flow-through space 6, thereby reducing the backflow of the liquid in the flow-through space 6 into the gap and the inside of the catheter 1.

[0064] Note that in this article, 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 also includes 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 said element.

Claims

1. A pump body, characterized in that, The pump body includes: A conduit; A rotating shaft, including a first section and a second section connected to each other. The first section is disposed inside the conduit, and the second section extends out of the conduit along the outlet of the conduit to the outside of the conduit. The rotating shaft can rotate relative to the conduit. A gap is provided between the rotating shaft and the outlet of the conduit, and the inside and outside of the conduit communicate with each other through the gap; An impeller, connected to the second section and spaced from the conduit. The rotating shaft can drive the impeller to rotate; A pressure member, connected to the second section, and the pressure member is located between the conduit and the impeller and corresponds to the gap. The rotating shaft can drive the pressure member to rotate and the pressure member generates centrifugal force.

2. The pump body according to claim 1, wherein The pressure member is fixedly connected to the impeller.

3. The pump body according to claim 1, wherein, The pressure member is a centrifugal blade; there are a plurality of the centrifugal blades, and the centrifugal blades are spaced along the circumferential direction of the impeller.

4. The pump body according to claim 3, wherein, The centrifugal blade is a radial blade, the inlet angle of the radial blade is 30° to 50°, and the outlet angle of the radial blade is 90°.

5. The pump body according to claim 3, characterized in that, The centrifugal blade is a backward curved blade, the inlet angle of the backward curved blade is 20° to 30°, the outlet angle of the backward curved blade is less than 90°, and the outlet angle of the backward curved blade is greater than the inlet angle of the backward curved blade.

6. The pump body according to claim 5, characterized in that, The outlet angle of the backward curved blade is 25° to 45°.

7. The pump body according to claim 3, characterized in that, The centrifugal blade is a forward curved blade, the inlet angle of the forward curved blade is 40° to 70°, and the outlet angle of the forward curved blade is greater than 90°.

8. The pump body according to claim 7, characterized in that, The outlet angle of the forward curved blade is 150° to 180°.

9. The pump body according to claim 3, characterized in that, The number of the centrifugal blades is 4 to 8, and along the axial direction of the rotating shaft, the size of the centrifugal blade is 0.05 mm to 0.15 mm.

10. The pump body according to claim 1, characterized in that, Along the axial direction of the conduit, the distance between the pressure member and the conduit is 0.05 mm to 0.2 mm.

11. An interventional catheter pump system, characterized in that, The interventional catheter pump system includes the pump body according to any one of claims 1 to 10.

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