Pumping catheter and ventricular assist system

Abstract

The utility model relates to a blood pumping catheter and a ventricular assist system.The blood pumping catheter comprises a perfusion cavity, a perfusion pipeline, an elastic element and a first flow adjusting component, the far end of the perfusion pipeline is connected to the perfusion cavity, the elastic element and the first flow adjusting component are both installed on the perfusion pipeline, and the first flow adjusting component is located between the elastic element and the perfusion cavity; the first preset value is larger than or equal to zero, and the first flow adjusting component is in a cut-off state under the condition that the difference value between the near-end-side pressure of the first flow adjusting component and the far-end-side pressure of the first flow adjusting component is smaller than the first preset value. According to the embodiment of the invention, the blood loss of a patient can be reduced, and the risk of thrombus formation and blockage in the perfusion device and the blood pumping catheter is reduced, so that the operation stability and the operation life of the perfusion pipeline on the near end side of the perfusion device and the blood pumping catheter can be relatively improved.

Description

Technical Field

[0001] The present application relates to the technical field of medical devices, and particularly to a blood pumping catheter and a ventricular assist system. Background Art

[0002] A ventricular assist system is an assist system that can pump blood from the ventricle to other parts of the body. The ventricular assist system is often used for patients with heart weakness or heart failure and can partially or mostly replace the blood pumping function of the ventricle.

[0003] In the related art, a ventricular assist system generally includes a blood pumping catheter and a perfusion device. Among them, a power assembly and an impeller are provided at the distal end of the blood pumping catheter. The power assembly is used to drive the impeller to rotate, so that blood can flow at an accelerated speed in the pumping direction, improving the blood flow rate. The blood pumping catheter generally further includes a perfusion cavity and a perfusion pipeline communicating with the perfusion cavity. The impeller is located outside the perfusion cavity, and at least part of the power assembly is installed in the perfusion cavity. The perfusion device is used to deliver perfusion fluid to the perfusion cavity through the perfusion pipeline to absorb the heat generated by the power assembly during operation and reduce the risk of discomfort to the patient caused by overheating of the power assembly.

[0004] Currently, some perfusion pipelines are provided with elastic elements. During the process of the internal pressure at the position of the elastic element in the perfusion pipeline changing, the elastic element will have elastic fluctuations. The blood pressure in the patient's body generally fluctuates periodically between diastolic pressure and systolic pressure. During each process of the patient's blood fluctuating from diastolic pressure to systolic pressure, the blood pressure in the patient's body increases, and the increased pressure of the blood in the patient's body will be transmitted to the elastic element through the perfusion cavity and the perfusion pipeline, causing the elastic element to contract. Therefore, the blood in the patient's body easily flows through the perfusion pipeline to the perfusion device. During the process of the blood pressure in the patient's body fluctuating periodically between diastolic pressure and systolic pressure, affected by the elastic fluctuations of the elastic element, the blood in the patient's body easily flows through the perfusion pipeline to the perfusion device step by step, which will lead to blood loss of the patient. Summary of the Utility Model

[0005] The embodiments of the present application provide a blood pumping catheter and a ventricular assist system, which can greatly reduce the risk of blood flowing back along the perfusion pipeline to the proximal side of the first flow regulating component and the perfusion device, and can reduce the blood loss of the patient.

[0006] In a first aspect, an embodiment of the present application provides a blood pumping catheter, which includes: a perfusion cavity for intervening in a patient's body; a perfusion pipeline, the distal end of the perfusion pipeline is connected to the perfusion cavity, and the proximal end of the perfusion pipeline is used to be connected to the liquid outlet of a perfusion device; an elastic element installed on the perfusion pipeline; a first flow rate regulating component installed on the perfusion pipeline and located between the elastic element and the perfusion cavity. When the difference between the pressure on the proximal side of the first flow rate regulating component and the pressure on the distal side of the first flow rate regulating component is greater than or equal to a first preset value, the first flow rate regulating component is in a conducting state, and the first preset value is greater than or equal to zero; when the difference between the pressure on the proximal side of the first flow rate regulating component and the pressure on the distal side of the first flow rate regulating component is less than the first preset value, the first flow rate regulating component is in a cut-off state.

[0007] In some embodiments, the elastic element includes: a first filtering component having a first filter element for filtering impurities and bubbles mixed in the perfusion liquid flowing through the first filter element; and / or a pressure storage component having a pressure storage cavity. During the process of the increase in the pressure of the perfusion liquid at the installation position of the pressure storage component, the pressure storage cavity is used to suck the perfusion liquid from the perfusion pipeline and store the pressure; during the process of the decrease in the pressure of the perfusion liquid at the installation position of the pressure storage component, the pressure storage cavity is used to press the perfusion liquid into the perfusion pipeline and release the pressure.

[0008] In some embodiments, the elastic element includes a first filtering component and a pressure storage component, and the pressure storage component is located on the proximal side of the first filtering component.

[0009] In some embodiments, the blood pumping catheter further includes a second filtering component located on the distal side of the first flow rate regulating component. The second filtering component has a second filter element for filtering impurities and bubbles mixed in the perfusion liquid flowing through the second filter element.

[0010] In some embodiments, the first flow rate regulating component includes a first one-way valve, and the opening direction of the first one-way valve faces the perfusion cavity.

[0011] In some embodiments, the first one-way valve includes: a valve body having an internal flow channel for the circulation of the perfusion liquid; a valve core movably installed in the internal flow channel. When the difference between the pressure on the proximal side of the internal flow channel and the pressure on the distal side of the internal flow channel is less than the opening pressure of the first one-way valve, the valve core can tightly abut and block the inner wall or the end of the internal flow channel, and the contact surface between the valve core and the internal flow channel is in the same plane or the radius of the contact surface between the valve core and the internal flow channel gradually becomes smaller in the direction from the distal side to the proximal side of the internal flow channel.

[0012] In some embodiments, the blood pumping catheter further includes a drainage pipeline, the distal end of the drainage pipeline is connected to the perfusion cavity, and the proximal end of the drainage pipeline is used to be connected to the liquid return port of the perfusion device.

[0013] In some embodiments, the blood pumping catheter further includes a second flow regulating component installed in the drainage pipeline. When the pressure on the distal side of the second flow regulating component is less than or equal to a second preset value, the second flow regulating component is in a cut-off state; when the pressure on the distal side of the second flow regulating component is greater than the second preset value, the second flow regulating component is in an open state.

[0014] In some embodiments, the second flow regulating component includes a second check valve, and the opening direction of the second check valve is away from the perfusion cavity.

[0015] In some embodiments, the second preset value is between 11 kPa and 30 kPa; alternatively, the second preset value is greater than or equal to the systolic blood pressure of the patient.

[0016] In some embodiments, when the pressure on the distal side of the second flow regulating component is greater than the second preset value and less than a third preset value, the flow resistance of the waste liquid flowing through the second flow regulating component is a first resistance value; when the pressure on the distal side of the second flow regulating component is greater than or equal to the third preset value, the flow resistance of the waste liquid flowing through the second flow regulating component is a second resistance value, the third preset value is greater than the second preset value, and the first resistance value is greater than the second resistance value.

[0017] In some embodiments, the second flow regulating component includes: a multi-way regulating valve including a first port and more than two second ports, the first port is connected to the perfusion cavity through a corresponding drainage pipeline, and the plurality of second ports are respectively communicated with the first port through corresponding flow channels; a first valve group including more than one second check valve, one end of the second check valve is connected to the liquid return port through a corresponding drainage pipeline, the other end of the second check valve is connected to a part of the second ports in one-to-one correspondence, and the opening direction of the second check valve is away from the perfusion cavity; a second valve group including more than one third check valve, one end of the third check valve is connected to the liquid return port through a corresponding drainage pipeline, the other end of the third check valve is connected to another part of the second ports in one-to-one correspondence, the opening direction of the third check valve is away from the perfusion cavity, the opening pressure of the second check valve is greater than the opening pressure of the third check valve, when the pressure on the distal side of the first port is less than the third preset value, the second port corresponding to the second check valve is in a conducting state, and the second port corresponding to the third check valve is in a cut-off state; when the pressure on the distal side of the first port is greater than or equal to the third preset value, the second port corresponding to the third check valve is in a conducting state, and the second port corresponding to the second check valve is in a cut-off state.

[0018] In some embodiments, the difference between the third preset value and the second preset value is between 1 kPa and 20 kPa.

[0019] In some embodiments, the flow area of the first flow regulating component is smaller than the flow area of the perfusion pipeline; and / or, the blood pumping catheter further includes: a working device for intervening in the patient's body; a power assembly connected to the working device to drive the working device to complete corresponding actions, with part of the power assembly located in the perfusion cavity, or the perfusion cavity is formed by enclosing part of the power assembly.

[0020] In a second aspect, an embodiment of the present application provides a ventricular assist system, including the above-mentioned blood pumping catheter, and further including a perfusion device. The perfusion device includes: a perfusion structure having a liquid outlet connected to the proximal end of the perfusion pipeline for pressing perfusion liquid into the perfusion pipeline; a suction structure having a liquid return port connected to the proximal end of the drainage pipeline for sucking waste liquid in the drainage pipeline; a linkage structure connected to the perfusion structure and the suction structure so that while the perfusion structure presses perfusion liquid into the perfusion pipeline, the suction structure can suck the waste liquid in the drainage pipeline.

[0021] In some embodiments, the linkage structure includes a first linkage member and a second linkage member capable of synchronous movement; the perfusion structure includes a first pumping and pressing member and a second pumping and pressing member. Both the first pumping and pressing member and the second pumping and pressing member can suck the perfusion liquid to be perfused and transport the sucked perfusion liquid to the liquid outlet. The first pumping and pressing member and the second pumping and pressing member are connected by the first linkage member so that while one of the first pumping and pressing member and the second pumping and pressing member transports the sucked perfusion liquid to the liquid outlet, the other can suck the perfusion liquid to be perfused; the suction structure includes a third pumping and pressing member and a fourth pumping and pressing member. Both the third pumping and pressing member and the fourth pumping and pressing member can suck the waste liquid in the drainage pipeline through the liquid return port and discharge the sucked waste liquid. The third pumping and pressing member and the fourth pumping and pressing member are connected by the second linkage member so that while one of the third pumping and pressing member and the fourth pumping and pressing member discharges the sucked waste liquid, the other can suck the waste liquid in the drainage pipeline.

[0022] The blood pumping catheter and ventricular assist system according to the embodiments of the present application include a perfusion cavity, a perfusion pipeline, an elastic element, and a first flow regulating component. The distal end of the perfusion pipeline is connected to the perfusion cavity, and the proximal end of the perfusion pipeline is used to connect to the liquid outlet of the perfusion device. The elastic element and the first flow regulating component are both installed on the perfusion pipeline, and the first flow regulating component is located between the elastic element and the perfusion cavity. When the difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component is greater than or equal to a first preset value, the first flow regulating component is in a conducting state, and the first preset value is greater than or equal to zero; when the difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component is less than the first preset value, the first flow regulating component is in a cut-off state. When the difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component is greater than or equal to the first preset value, and the first preset value is greater than or equal to zero, it indicates that the perfusion liquid pressure on the proximal side of the first flow regulating component is not less than the perfusion liquid pressure on the distal side of the first flow regulating component. The first flow regulating component is adjusted to a conducting state, and the perfusion liquid flowing out of the liquid outlet of the perfusion device can smoothly flow to the perfusion cavity through the perfusion pipeline after flowing through the elastic element and the first flow regulating component; during each process of the patient's blood fluctuating from diastolic pressure to systolic pressure, the blood pressure in the patient's body increases, and the increased pressure of the blood in the patient's body will be transmitted to the distal side of the first flow regulating component through the perfusion cavity and the perfusion pipeline, which easily causes the pressure on the distal side of the first flow regulating component to be greater than the pressure on the proximal side of the first flow regulating component. When the difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component is less than the first preset value, and the first preset value is greater than or equal to zero, the first flow regulating component is adjusted to a cut-off state, which can avoid the blood in the patient's body flowing to the perfusion device through the perfusion cavity and the perfusion pipeline due to the perfusion liquid pressure on the distal side of the first flow regulating component being greater than the perfusion liquid pressure on the proximal side of the first flow regulating component, reduce the blood loss of the patient, and reduce the risk of thrombosis formation and blockage in the perfusion device and the blood pumping catheter, thereby relatively improving the operation stability and service life of the perfusion pipeline on the proximal side of the perfusion device and the blood pumping catheter; in addition, while the perfusion liquid plays a role in dissipating heat from the components in the perfusion cavity and reducing the risk of patient discomfort caused by overheating of the components in the perfusion cavity, it can also wash away the wear particles generated during the operation of the components in the perfusion cavity, avoid excessive wear of the components in the perfusion cavity, and play a certain lubricating role for the components in the perfusion cavity. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following will briefly introduce the drawings required to be used in the embodiments of the present application. For those of ordinary skill in the art, other drawings can also be obtained based on these drawings without creative efforts.

[0024] Figure 1 Schematic structural diagram of a blood pumping catheter provided for some embodiments of the present application;

[0025] Figure 2 Schematic structural diagram of a blood pumping catheter provided for some other embodiments of the present application;

[0026] Figure 3 Schematic structural diagram of a blood pumping catheter provided for some further embodiments of the present application;

[0027] Figure 4 Schematic structural diagram of a blood pumping catheter provided for some other embodiments of the present application;

[0028] Figure 5 Schematic structural diagram of a ventricular assist system provided for some embodiments of the present application;

[0029] Figure 6 Schematic internal structural diagram of a perfusion device provided for some embodiments of the present application.

[0030] In the figure: 1, perfusion pipeline; 2, liquid discharge pipeline; 3, first one-way valve; 4, perfusion cavity; 5, output shaft; 6, working instrument; 7, second filtering component; 8, pressure storage component; 9, first filtering component; 10, second one-way valve; 11, third one-way valve; 12, multi-way regulating valve; 13, pressure sensor; 14, liquid outlet; 15, liquid return port; 16, first accommodating member; 17, second accommodating member; 18, first cylinder block; 19, first sub-cavity; 20, first piston; 21, first linkage member; 22, second piston; 23, second sub-cavity; 24, second cylinder block; 25, third linkage member; 26, third cylinder block; 27, third sub-cavity; 28, third piston; 29, fourth piston; 30, fourth sub-cavity; 31, fourth cylinder block; 32, first pipeline; 33, first valve; 34, second pipeline; 35, second valve; 36, third pipeline; 37, third valve; 38, fourth valve; 39, fourth pipeline; 40, fifth pipeline; 41, fifth valve; 42, sixth pipeline; 43, sixth valve; 44, seventh pipeline; 45, seventh valve; 46, eighth pipeline; 47, eighth valve; 48, second linkage member; 49, perfusion device; 50, perfusion structure; 51, suction structure; 52, linkage structure. Detailed implementation manners

[0031] The features and exemplary embodiments of various aspects of the present application will be described in detail below. In order 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.

[0032] 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 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.

[0033] Currently, a ventricular assist system generally includes a blood pumping catheter and a perfusion device. Among them, a power assembly and an impeller are provided at the distal end of the blood pumping catheter. The power assembly includes an output shaft, and the impeller is connected to a part of the power assembly located in the perfusion cavity through the output shaft. The power assembly is used to transmit torque to the output shaft to drive the impeller to rotate through the output shaft, so that blood can flow at an accelerated rate in the pumping direction and the blood flow rate can be increased. The blood pumping catheter generally further includes a perfusion cavity and a perfusion pipeline communicating with the perfusion cavity. The impeller is located outside the perfusion cavity, and at least part of the power assembly is installed in the perfusion cavity. Specifically, for the in-vivo motor mode, the power assembly in the perfusion cavity includes the end of the output shaft away from the impeller, a bearing sleeved on the output shaft, etc.; for the ex-vivo motor mode, the power assembly in the perfusion cavity includes the end of the output shaft away from the impeller, a bearing sleeved on the output shaft, and a part of the transmission wire located inside the perfusion cavity, etc. Among them, one end of the transmission wire located in the perfusion cavity is connected to the transmission shaft, and the end of the transmission wire located outside the perfusion cavity is connected to the ex-vivo motor. The output shaft extends from inside the perfusion cavity to outside the perfusion cavity. The perfusion device is used to deliver perfusion fluid to the perfusion cavity through the perfusion pipeline to absorb the heat generated by the power assembly during operation and reduce the risk of patient discomfort caused by overheating of the power assembly. Among them, the heat generated by the power assembly during operation is generally due to mechanical friction. For example, during the operation of the bearing of the output shaft, heat will be generated due to friction between the corresponding inner ring of the bearing and the inner ring of the bearing and the bearing balls respectively.

[0034] It has been found through research that the blood pressure in a patient's body generally fluctuates periodically between diastolic blood pressure and systolic blood pressure. During each process of the patient's blood fluctuating from diastolic blood pressure to systolic blood pressure, the blood pressure in the patient's body increases, and the increased pressure of the blood in the patient's body is transmitted to the elastic element through the perfusion cavity and the perfusion pipeline, causing the elastic element to contract. Therefore, the blood in the patient's body easily flows through the perfusion pipeline to the perfusion device. During the process of the blood pressure in the patient's body fluctuating periodically between diastolic blood pressure and systolic blood pressure, affected by the elastic fluctuation of the elastic element, the blood in the patient's body easily flows through the perfusion pipeline to the perfusion device step by step, which will further lead to blood loss in the patient.

[0035] To solve the problems of the prior art, the embodiments of the present application provide a blood pumping catheter and a ventricular assist system. The following is a detailed introduction with reference to the accompanying drawings.

[0036] Figure 1 Schematic diagram of the structure of the blood pumping catheter provided by some embodiments of the present application;

[0037] Figure 5 Schematic diagram of the structure of the ventricular assist system provided by some embodiments of the present application.

[0038] Combined with Figure 1 and Figure 5It can be known that the embodiment of the present application provides a blood pumping catheter, including a perfusion cavity 4, a perfusion pipeline 1, an elastic element (not labeled), and a first flow rate regulating component (not labeled). The perfusion cavity 4 is used to intervene in a patient's body; the distal end of the perfusion pipeline 1 is connected to the perfusion cavity 4, and the proximal end of the perfusion pipeline 1 is used to connect to the liquid outlet 14 of the perfusion device 49. The elastic element is installed on the perfusion pipeline 1. Specifically, the elastic element can be a functional element in the blood pumping catheter that can achieve certain functions, such as a filtering component or a pressure storage component. It has an elastic structure inside, and this elastic structure is located on the flow path of the perfusion pipeline. The first flow rate regulating component is installed on the perfusion pipeline 1 and is located between the elastic element and the perfusion cavity 4. When the difference between the proximal side pressure and the distal side pressure of the first flow rate regulating component is greater than or equal to a first preset value, the first flow rate regulating component is in a conducting state, and the first preset value is greater than or equal to zero; when the difference between the proximal side pressure and the distal side pressure of the first flow rate regulating component is less than the first preset value, the first flow rate regulating component is in a cut-off state. 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; when components with a medium flow space inside are connected, it essentially means that the internal medium flow spaces of the corresponding components are connected. Specifically, in this embodiment, the two ends of the perfusion pipeline 1 are respectively connected to the perfusion cavity 4 and the liquid outlet 14 of the perfusion device 49, which means that the internal flow channels of the perfusion pipeline 1 are respectively connected to the perfusion cavity 4 and the liquid outlet 14. In addition, the difference between one pressure and another pressure in the present application means the value obtained by subtracting the value of one pressure from the value of the other pressure. For example, the difference between the proximal side pressure and the distal side pressure of the first flow rate regulating component can be understood as the difference between the value of the proximal side pressure of the first flow rate regulating component and the value of the distal side pressure of the first flow rate regulating component. Based on this, in some application scenarios, the difference can be greater than 0, in some other application scenarios, the difference can be equal to 0, and in some other application scenarios, the difference can be less than 0.

[0039] When the difference between the pressure on the proximal side and the pressure on the distal side of the first flow regulating component is greater than or equal to the first preset value, and the first preset value is greater than or equal to zero, it indicates that the perfusion fluid pressure on the proximal side of the first flow regulating component is not less than the perfusion fluid pressure on the distal side of the first flow regulating component. The first flow regulating component is adjusted to the conducting state, and the perfusion fluid flowing out from the liquid outlet 14 of the perfusion device 49 can smoothly flow through the perfusion pipeline 1, the elastic element, and the first flow regulating component and then flow to the perfusion cavity 4; during each process of the patient's blood fluctuating from diastolic pressure to systolic pressure, the blood pressure in the patient's body increases, and the increased pressure of the blood in the patient's body will be transmitted to the distal side of the first flow regulating component through the perfusion cavity 4 and the perfusion pipeline 1, which easily causes the pressure on the distal side of the first flow regulating component to be greater than the pressure on the proximal side of the first flow regulating component. When the difference between the pressure on the proximal side and the pressure on the distal side of the first flow regulating component is less than the first preset value, and the first preset value is greater than or equal to zero, the first flow regulating component is adjusted to the cut-off state, which can avoid the blood in the patient's body flowing through the perfusion cavity 4 and the perfusion pipeline 1 to the perfusion device 49 due to the perfusion fluid pressure on the distal side of the first flow regulating component being greater than the perfusion fluid pressure on the proximal side of the first flow regulating component, reduce the blood loss of the patient, and reduce the risk of thrombosis formation and blockage in the perfusion device 49 and the blood pump catheter, thereby relatively improving the operation stability and operation life of the perfusion pipeline 1 on the proximal side of the perfusion device 49 and the blood pump catheter; in addition, while the perfusion fluid plays a role in dissipating heat from the components in the perfusion cavity 4 and reducing the risk of patient discomfort caused by overheating of the components in the perfusion cavity 4, it can also wash away the wear particles generated during the operation of the components in the perfusion cavity 4, avoid excessive wear of the components in the perfusion cavity 4, and play a certain lubricating role for the components in the perfusion cavity 4.

[0040] In some embodiments, the proximal end of the perfusion pipeline 1 is detachably installed at the liquid outlet 14 of the perfusion device 49. When the perfusion device 49 is damaged and needs to be replaced or when the patient needs to be transferred and the perfusion device 49 needs to be replaced, medical staff can directly detach the proximal end of the perfusion pipeline 1 from the connected perfusion device 49 and reinstall it at the liquid outlet 14 of the next perfusion device 49 to be connected, which is convenient for operation. Specifically, the proximal end of the perfusion pipeline 1 can be detachably installed at the liquid outlet 14 of the perfusion device 49 through a luer connector. The structure of the luer connector is relatively mature, which is convenient for design and processing or direct purchase, and the cost is relatively low.

[0041] Such as Figure 1As shown, in some embodiments, the elastic element includes a first filtering component 9. The first filtering component 9 has a first filter element for filtering impurities and bubbles mixed in the perfusion fluid flowing through the first filter element. Bubbles entering the patient's body will form air embolisms. By providing the filtering component, the risk of impurities and bubbles flowing into the patient's body and causing discomfort to the patient can be reduced.

[0042] As Figure 1 As shown, in some embodiments, the elastic element includes a pressure storage component 8. The pressure storage component 8 has a pressure storage chamber. Specifically, at least one chamber wall of the pressure storage chamber is elastic. During the process of the increase in the perfusion fluid pressure at the installation position of the pressure storage component 8, it will cause the increase in the perfusion fluid pressure in the pressure storage chamber. The elastic chamber wall of the pressure storage chamber expands outward, and the volume of the pressure storage chamber increases, so that the pressure storage chamber can suck in the perfusion fluid from the perfusion pipeline 1 and store the pressure; during the process of the decrease in the perfusion fluid pressure at the installation position of the pressure storage component 8, it will cause the decrease in the perfusion fluid pressure in the pressure storage chamber. The elastic chamber wall of the pressure storage chamber contracts inward, and the volume of the pressure storage chamber decreases, so that the pressure storage chamber can press the perfusion fluid into the perfusion pipeline 1 and release the pressure. It can be understood that the perfusion fluid pressure at the installation position of the pressure storage component 8 refers to the perfusion fluid pressure in the perfusion pipeline 1 near the pressure storage component 8. In the case where the perfusion fluid pressure output by the perfusion device 49 fluctuates, the pressure storage component 8 can play a role in leveling the peaks and filling the valleys of the perfusion fluid pressure in the perfusion pipeline 1, making the perfusion fluid pressure in the perfusion pipeline 1 relatively stable.

[0043] As Figure 1 As shown, in some embodiments, the elastic element includes a first filtering component 9 and a pressure storage component 8. The pressure storage component 8 is located on the proximal side of the first filtering component 9. The pressure storage component 8 is relatively close to the perfusion device 49 and can quickly respond to and absorb the perfusion fluid pressure fluctuations caused during the operation of the perfusion device 49.

[0044] Figure 2 It is a schematic structural diagram of a blood pumping catheter provided in some other embodiments of the present application.

[0045] As Figure 2 As shown, in some embodiments, the blood pumping catheter further includes a second filtering component 7, which is located on the distal side of the first flow regulating component. The second filtering component 7 has a second filter element for filtering impurities and bubbles mixed in the perfusion fluid flowing through the second filter element. The second filtering component 7 can filter out the tiny bubbles generated during the process of the first flow regulating component adjusting its working state to the greatest extent, thereby reducing the risk of the corresponding bubbles entering the patient's body and causing discomfort to the patient.

[0046] As Figure 1As shown, in some embodiments, the first flow regulating component includes a first one-way valve 3. The opening direction of the first one-way valve 3 faces the perfusion cavity 4, with a simple structure and relatively low cost. It should be noted that the opening direction of the one-way valve facing a certain component means that the outlet of the one-way valve is close to the corresponding component. Specifically, in the present embodiment, the opening direction of the first one-way valve 3 facing the perfusion cavity 4 means that the outlet of the first one-way valve 3 faces the perfusion cavity 4, and the perfusion fluid flowing through the first one-way valve 3 can only flow from the side far from the perfusion cavity 4 to the side close to the perfusion cavity 4. In some other embodiments, an electromagnetic valve can also be selected to replace the first one-way valve 3 to achieve the corresponding function by adjusting the valve opening of the corresponding electromagnetic valve. That is, the electromagnetic valve controls the opening and closing of the valve according to the liquid pressure on both sides of the valve body, realizing the one-way conduction performance on the perfusion path.

[0047] In some embodiments, the opening pressure of the first one-way valve 3 is less than or equal to 30 kPa. Further, the opening pressure of the first one-way valve 3 can be between 1 kPa and 13 kPa. If the opening pressure of the first one-way valve 3 is too high, the perfusion device 49 needs to provide a higher perfusion fluid pressure to make the perfusion fluid flow into the perfusion cavity 4. Therefore, by limiting the opening pressure of the first one-way valve 3, the requirement for the perfusion fluid output pressure of the perfusion device 49 can be relatively reduced, the energy consumption of the perfusion device 49 can be reduced, and the operation stability of the perfusion device 49 and the blood pumping catheter can be improved. It should be noted that the opening pressure of the one-way valve refers to the pressure difference between the inlet and the outlet during forward conduction. That is to say, in the present embodiment, the opening pressure of the first one-way valve 3 is equivalent to the first preset value. When the pressure difference between the proximal side pressure and the distal side pressure of the first one-way valve 3 is above the opening pressure of the first one-way valve 3, the first one-way valve 3 opens, and the perfusion fluid can flow from the proximal side of the first one-way valve 3 to the distal side of the first one-way valve 3.

[0048] In some embodiments, the first one-way valve 3 includes a valve body and a valve core. The valve body has an internal flow channel for the circulation of the perfusion fluid; the valve core is movably installed in the internal flow channel. Specifically, the first one-way valve 3 further includes a reset member connected to the valve core. The reset member is used to provide a reset force to the valve core in the direction pointing to the proximal side of the first one-way valve 3. The opening pressure of the first one-way valve 3 is equal to the sum of the frictional force between the valve core and the valve body and the reset force. Among them, the reset member can be an elastic member, such as a helical spring, a leaf spring or a diaphragm spring, etc. When the pressure difference between the proximal side pressure and the distal side pressure of the internal flow channel is greater than or equal to the opening pressure of the first one-way valve 3, there is a spacer area for the perfusion fluid to flow between the valve core and the internal flow channel; when the pressure difference between the proximal side pressure and the distal side pressure of the internal flow channel is less than the opening pressure of the first one-way valve 3, the valve core can be tightly pressed against and block the inner wall or the end of the internal flow channel, so that the internal flow channel is in a cut-off state. At this time, the contact surface between the valve core and the internal flow channel is in the same plane or the radius of the contact surface between the valve core and the internal flow channel gradually becomes smaller from the distal side to the proximal side of the internal flow channel. That is to say, there is no stepped mutation in the contact surface between the valve core and the internal flow channel. Therefore, during the process of the first one-way valve 3 switching to the cut-off state or the conducting state, air bubbles are not likely to appear at the contact position between the valve core and the internal flow channel, thereby reducing the risk of the corresponding air bubbles entering the patient's body and causing discomfort to the patient. It can be understood that the proximal side pressure of the internal flow channel is the same as the proximal side pressure of the first flow regulating component; the distal side pressure of the internal flow channel is the same as the distal side pressure of the first flow regulating component.

[0049] In the prior art, some power components in the perfusion chamber 4 rub against each other during operation, generating wear particles while generating heat. After the perfusion fluid enters the perfusion chamber 4 through the perfusion pipeline 1, it will exchange heat with the components in the perfusion chamber 4 to achieve the purpose of cooling. The perfusion fluid that has completed heat exchange will form waste liquid after mixing with the wear particles. Currently, the waste liquid generally drains into the patient's body through the gap between the output shaft 5 and the chamber wall of the perfusion chamber 4, which is likely to cause discomfort to the patient; in addition, since the total amount of waste liquid that the patient can absorb is limited, it is necessary to control the flow rate of the perfusion fluid within a predetermined range to control the total amount of waste liquid entering the patient's body during the operation to meet the requirements, which easily leads to an unsatisfactory heat dissipation effect of the perfusion chamber 4.

[0050] Figure 3 Structural schematic diagram of a blood pumping catheter provided in some other embodiments of the present application.

[0051] As Figures 1 to 3As shown, in some embodiments, the blood pumping catheter further includes a drainage line 2. The distal end of the drainage line 2 is connected to the perfusion chamber 4, and the proximal end of the drainage line 2 is for connecting to the return port 15 of the perfusion device 49. Most of the waste liquid can be discharged through the drainage line 2 to the return port 15 of the perfusion device 49, which can reduce the risk of discomfort to the patient caused by a large amount of waste liquid entering the patient's body. In addition, the heat dissipation effect of the perfusion chamber 4 can be improved by increasing the flow rate of the perfusion liquid in the perfusion line 1.

[0052] In some embodiments, the proximal end of the drainage line 2 is detachably installed at the return port 15 of the perfusion device 49. When the perfusion device 49 is damaged and needs to be replaced or when the patient needs to be transferred and thus the perfusion device 49 needs to be replaced, medical staff can directly detach the proximal end of the drainage line 2 from the connected perfusion device 49 and reinstall it to the return port 15 of the next perfusion device 49 to be connected, which is convenient to operate. Specifically, the proximal end of the drainage line 2 can be detachably installed at the return port 15 of the perfusion device 49 through a Luer connector. The structure of the Luer connector is relatively mature, which is convenient for design and processing or direct purchase, and the cost is relatively low.

[0053] As Figure 3 shown, in some embodiments, the blood pumping catheter further includes a second flow rate regulating component installed on the drainage line 2. When the pressure on the distal side of the second flow rate regulating component is less than or equal to the second preset value, the second flow rate regulating component is in a cut-off state; when the pressure on the distal side of the second flow rate regulating component is greater than the second preset value, the second flow rate regulating component is in an open state. When the pressure on the distal side of the second flow rate regulating component is less than or equal to the first preset value, after the perfusion liquid flows into the perfusion chamber 4 and forms waste liquid, the pressure of the waste liquid in the perfusion chamber 4 is relatively small, and the blood outside the perfusion chamber 4 is likely to enter the perfusion chamber 4. By adjusting the second flow rate regulating component to the cut-off state, it can prevent the patient's blood from flowing to the perfusion device 49 through the drainage line 2 and the second flow rate regulating component; when the pressure on the distal side of the second flow rate regulating component is greater than the first preset value, after the perfusion liquid flows into the perfusion chamber 4 and forms waste liquid, the pressure of the waste liquid in the perfusion chamber 4 is relatively large, so that the blood in the patient's body can be blocked outside the perfusion chamber 4 to a large extent. That is to say, after the second flow rate regulating component is adjusted to the open state, the blood in the patient's body is not likely to enter the perfusion chamber 4, and the liquid flowing into the drainage line 2 is basically waste liquid, which can relatively reduce the blood loss of the patient.

[0054] As Figure 3As shown, in some embodiments, the second flow rate regulating component includes a second one-way valve 10. The opening direction of the second one-way valve 10 faces away from the perfusion cavity 4, with a simple structure and low cost. It should be noted that the opening direction of the one-way valve facing away from a certain component means that the inlet of the one-way valve is close to the corresponding component. Specifically, in the present embodiment, the opening direction of the second one-way valve 10 facing away from the perfusion cavity 4 means that the inlet of the second one-way valve 10 is close to the perfusion cavity 4, and the waste liquid flowing through the second one-way valve 10 can only flow from the side close to the perfusion cavity 4 to the side away from the perfusion cavity 4. In other embodiments, an electromagnetic valve can also be selected as the second flow rate, and the corresponding functions can be achieved by adjusting the valve opening of the corresponding electromagnetic valve. That is, the corresponding electromagnetic valve can control the opening and closing of the valve according to the liquid pressure on both sides of the valve body, realizing the one-way conduction performance on the perfusion path.

[0055] In some embodiments, the second preset value is between 11 kPa and 30 kPa. Since the second preset value is greater than 11 kPa, it is possible to avoid the blood outside the perfusion cavity 4 from entering the perfusion cavity 4 as much as possible, reducing the risk of blood loss; since the second preset value is less than 30 kPa, it is possible to avoid a large amount of waste liquid from entering the patient's body due to excessive pressure on the distal side of the second flow rate regulating component, and at the same time avoid excessive pressure of the waste liquid in the drainage pipeline 2, improving the working stability of the drainage pipeline 2.

[0056] In some embodiments, the second preset value is greater than or equal to the systolic blood pressure of the patient. That is to say, the patient's blood pressure cannot independently cause the second flow rate regulating component to open, which can greatly reduce the risk of blood loss.

[0057] In some embodiments, when the pressure on the distal side of the second flow rate regulating component is greater than the second preset value and less than the third preset value, the flow resistance of the waste liquid flowing through the second flow rate regulating component is the first resistance value; when the pressure on the distal side of the second flow rate regulating component is greater than or equal to the third preset value, the flow resistance of the waste liquid flowing through the second flow rate regulating component is the second resistance value. The third preset value is greater than the second preset value, and the first resistance value is greater than the second resistance value. That is to say, when the pressure on the distal side of the second flow rate regulating component is greater than the third preset value, the flow resistance of the waste liquid flowing through the second flow rate regulating component is relatively small, and the waste liquid in the perfusion cavity 4 can be quickly discharged through the drainage pipeline 2 and the second flow rate component, thereby preventing a large amount of waste liquid from entering the patient's body.

[0058] Figure 4 It is a schematic structural diagram of a blood pumping catheter provided in still other embodiments of the present application.

[0059] As Figure 4As shown, in some embodiments, the second flow rate regulating component includes a multi-way regulating valve 12, a first valve group, and a second valve group. The multi-way regulating valve 12 includes a first port and more than two second ports. The first port is connected to the perfusion chamber 4 through a corresponding liquid discharge pipeline 2, and the multiple second ports are respectively communicated with the first port through corresponding flow channels. The first valve group includes more than one second check valve 10. One end of the second check valve 10 is connected to the liquid return port 15 through a corresponding liquid discharge pipeline 2, and the other end of the second check valve 10 is connected to a part of the second ports in one-to-one correspondence. The opening direction of the second check valve 10 is away from the perfusion chamber 4. The second valve group includes more than one third check valve 11. One end of the third check valve 11 is connected to the liquid return port 15 through a corresponding liquid discharge pipeline 2, and the other end of the third check valve 11 is connected to another part of the second ports in one-to-one correspondence. The opening direction of the third check valve 11 is away from the perfusion chamber 4. The opening pressure of the second check valve 10 is greater than the opening pressure of the third check valve 11, so that the flow resistance of the waste liquid flowing through the second valve group is greater than the flow resistance of the waste liquid flowing through the first valve group. When the pressure on the distal side of the first port is less than the third preset value, the second port corresponding to the second check valve 10 is in a conducting state, and the second port corresponding to the third check valve 11 is in a cut-off state. When the pressure on the distal side of the first port is greater than or equal to the third preset value, the second port corresponding to the third check valve 11 is in a conducting state, and the second port corresponding to the second check valve 10 is in a cut-off state. It can be understood that the first resistance value is the sum of the flow resistances generated during the process of the waste liquid flowing through the multi-way regulating valve 12 and the second valve group, and the second resistance value is the sum of the flow resistances generated during the process of the waste liquid flowing through the multi-way regulating valve 12 and the first valve group. Specifically, in this embodiment, the number of the second ports is two, and the number of both the second check valve 10 and the third check valve 11 is one. The valve body structures included in the second flow rate regulating component are all relatively conventional, and the overall structure is simple.

[0060] As Figure 4 shown, in some embodiments, the blood pumping catheter further includes a pressure sensor 13 installed on the liquid discharge pipeline. The pressure sensor 13 is located on the distal side of the second flow rate regulating component to accurately monitor the waste liquid pressure at the corresponding position. In some of these embodiments, the pressure sensor 13 feeds back the monitored waste liquid pressure to the multi-way regulating valve 12, and the multi-way regulating valve 12 controls the conduction between the first port and the corresponding second port based on the received waste liquid pressure.

[0061] In some embodiments, the opening pressure of the second check valve 10 can be 11 kPa to 30 kPa, and the opening pressure of the third check valve 11 can be 1 kPa to 10 kPa.

[0062] In some embodiments, the difference between the third preset value and the second preset value is between 1 kPa and 20 kPa. When the difference between the third preset value and the second preset value is less than 1 kPa and the pressure on the distal side of the second flow regulating component is near the second preset value, due to factors such as blood pressure fluctuations, the periodic fluctuation range of the pressure on the distal side of the second flow regulating component is likely to be greater than the above difference. Therefore, it is necessary to frequently adjust the internal structure of the second flow regulating component to cause the second flow regulating component to frequently switch between the first resistance value and the second resistance value, which will result in poor system stability of the blood pumping catheter. Since the maximum difference between the third preset value and the second preset value is 20 kPa, it is possible to prevent a large amount of waste liquid from flowing into the patient's body due to excessive waste liquid pressure in the perfusion chamber 4, and at the same time, it is possible to avoid damage to the blood pumping catheter due to excessive waste liquid pressure on the distal side of the second flow regulating component. Further, the difference between the third preset value and the second preset value is 13 kPa.

[0063] In some embodiments, the flow-through area of the first flow regulating component is smaller than the flow-through area of the perfusion pipeline 1. The flow-through area refers to the area of the fluid flow-through cross-section. In this embodiment, the flow-through area of the perfusion pipeline 1 refers to the flow-through cross-section area of the perfusion fluid flowing through the perfusion pipeline 1, and the flow-through area of the first flow regulating component refers to the flow-through cross-section area of the perfusion fluid at the position of the first flow regulating component. When the difference between the pressure on the proximal side and the pressure on the distal side of the first flow regulating component is greater than or equal to the first preset value, the first flow regulating component is in a conducting state, and the perfusion fluid on the proximal side of the first flow regulating component can smoothly flow to the distal side of the first flow regulating component and then enter the perfusion chamber 4. However, affected by factors such as the patient's blood pressure fluctuations and the elastic fluctuations of the elastic element, the blood will form turbulence or eddy currents, and there is also a risk of blood loss caused by the blood gradually conducting through the perfusion pipeline 1 to the perfusion device 49. By defining that the flow-through area of the first flow regulating component is smaller than the flow-through area of the perfusion pipeline 1, the flow velocity of the perfusion fluid at the position of the first flow regulating component is relatively fast. Affected by factors such as the patient's blood pressure fluctuations and the elastic fluctuations of the perfusion pipeline 1, although the blood will form turbulence or eddy currents, due to the relatively small flow-through area of the first flow regulating component and the relatively fast flow velocity of the perfusion fluid at the position of the first flow regulating component, the risk of blood conducting to the proximal side of the first flow regulating component can be reduced to a large extent, and the blood loss of the patient can be further reduced.

[0064] In some embodiments, the blood pumping catheter further includes a working instrument 6 and a power assembly. The working instrument 6 is used to intervene in the patient's body. The power assembly is connected to the working instrument 6 to drive the working instrument 6 to complete corresponding actions. Part of the power assembly is located in the perfusion cavity 4, or the perfusion cavity 4 is formed by enclosing part of the power assembly. Specifically, the working instrument 6 can be an impeller, and the power assembly can include an output shaft 5. One end of the output shaft 5 is rotatably connected to the inside of the perfusion cavity 4 through a corresponding bearing, and the other end of the output shaft 5 is fixedly connected to the impeller. For the external motor mode, the perfusion cavity 4 is formed by enclosing the perfusion cavity wall. The power assembly in the perfusion cavity 4 includes one end of the output shaft 5 away from the impeller, a bearing sleeved on the output shaft 5, and a transmission wire part located inside the perfusion cavity 4. The power assembly further includes an external motor located outside the patient. Among them, one end of the transmission wire located in the perfusion cavity 4 is connected to the transmission shaft, and the other end of the transmission wire located outside the perfusion cavity 4 is connected to the external motor. The external motor can drive the impeller to rotate through the transmission wire and the transmission shaft. For the internal motor mode, the power assembly includes an internal motor for intervening in the patient's body. The internal motor has a housing, and the perfusion cavity 4 is formed by enclosing the housing of the internal motor. That is to say, the perfusion cavity 4 can be the internal space of the housing of the internal motor. The power assembly in the perfusion cavity 4 includes one end of the output shaft 5 away from the impeller, a bearing sleeved on the output shaft 5, and other internal motor components in the housing. The internal motor can drive the impeller to rotate through the transmission shaft.

[0065] Figure 6 Schematic diagram of the internal structure of the perfusion device 49 provided by some embodiments of the present application.

[0066] As Figure 5 and Figure 6 shown, the embodiments of the present application further provide a ventricular assist system, including the above-mentioned blood pumping catheter, and further including a perfusion device 49. The perfusion device 49 includes a perfusion structure 50, a suction structure 51 and a linkage structure 52. The perfusion structure 50 has a liquid outlet 14, and the liquid outlet 14 is connected to the proximal end of the perfusion pipeline 1 for pressing perfusion liquid into the perfusion pipeline 1. The suction structure 51 has a liquid return port 15, and the liquid return port 15 is connected to the proximal end of the drainage pipeline 2 for sucking the waste liquid in the drainage pipeline 2. The linkage structure 52 is connected to the perfusion structure 50 and the suction structure 51, so that when the perfusion structure 50 presses perfusion liquid into the perfusion pipeline 1, the suction structure 51 can suck the waste liquid in the drainage pipeline 2. By setting the linkage structure 52, it is possible to ensure the synchronous operation of the perfusion structure 50 and the suction structure 51, so that the injection of perfusion liquid and the discharge of waste liquid in the heat dissipation cavity have a high degree of synchronization, so as to reduce the risk of waste liquid entering the patient's body and the patient's blood being discharged from the discharge pipeline. In addition, since the ventricular assist system includes the blood pumping catheter in the above embodiments, it has at least all the beneficial effects brought by the above embodiments, and will not be elaborated here one by one.

[0067] AsFigure 6 As shown, in some embodiments, the linkage structure 52 includes a first linkage member 21 and a second linkage member 48 capable of synchronous movement; the perfusion structure 50 includes a first pumping member and a second pumping member. Both the first pumping member and the second pumping member can suck the perfusion fluid to be perfused and convey the sucked perfusion fluid to the liquid outlet 14. The first pumping member and the second pumping member are connected by the first linkage member 21, so that when one of the first pumping member and the second pumping member conveys the sucked perfusion fluid to the liquid outlet 14, the other can suck the perfusion fluid to be perfused; the suction structure 51 includes a third pumping member and a fourth pumping member. Both the third pumping member and the fourth pumping member can suck the waste liquid in the drainage pipeline 2 through the liquid return port 15 and discharge the sucked waste liquid. The third pumping member and the fourth pumping member are connected by the second linkage member 48, so that when one of the third pumping member and the fourth pumping member discharges the sucked waste liquid, the other can suck the waste liquid in the drainage pipeline 2. It can realize the continuous perfusion of the perfusion fluid and the continuous suction of the waste liquid, can better maintain the coherence of the injection of the perfusion fluid and the discharge of the waste liquid, and reduce the risks of the power component being blocked by wear particles, wear particles entering the patient's body, or blood flowing out of the patient's body.

[0068] As Figure 6 As shown, in some embodiments, the perfusion structure 50 further includes a first accommodating member 16, a first pipeline assembly, a second pipeline assembly, a third pipeline assembly, and a fourth pipeline assembly. Among them, the first accommodating member 16 has a first accommodating cavity for accommodating the perfusion fluid to be perfused; the first pumping member and the second pumping member are distributed along the first direction; the first pumping member includes a first cylinder body 18 and a first piston 20 slidably connected to the first cylinder body 18. The first cylinder body 18 and the first piston 20 enclose a first sub-cavity 19. The two ends of the first pipeline assembly are respectively connected to the first accommodating member 16 and the first pumping member, so that the perfusion fluid in the first accommodating cavity flows into the first sub-cavity 19. The two ends of the second pipeline assembly are respectively connected to the first pumping member and the liquid outlet 14, so that the perfusion fluid in the first sub-cavity 19 flows to the liquid outlet 14; the second pumping member includes a second cylinder body 24 and a second piston 22 slidably connected to the second cylinder body 24. The second cylinder body 24 and the second piston 22 enclose a second sub-cavity 23. The first piston 20 is located at a position of the first sub-cavity 19 close to the second sub-cavity 23, and the second piston 22 is located at a position of the second sub-cavity 23 close to the first sub-cavity 19. The two ends of the third pipeline assembly are respectively connected to the first accommodating member 16 and the second pumping member, so that the perfusion fluid in the first accommodating cavity flows into the second sub-cavity 23. The two ends of the fourth pipeline assembly are respectively connected to the second pumping member and the liquid outlet 14, so that the perfusion fluid in the second sub-cavity 23 flows to the liquid outlet 14.

[0069] The liquid discharging structure further includes a second accommodating member 17, a fifth pipeline assembly, a sixth pipeline assembly, a seventh pipeline assembly, and an eighth pipeline assembly. Among them, the second accommodating member 17 has a second accommodating cavity for accommodating waste liquid; the third pumping member and the fourth pumping member are distributed along the first direction; the third pumping member includes a third cylinder body 26 and a third piston 28 slidably connected to the third cylinder body 26. A third sub-cavity 27 is formed by enclosing the third cylinder body 26 and the third piston 28. The two ends of the sixth pipeline assembly are respectively connected to the third pumping member and the liquid return port 15, so that the waste liquid at the liquid return port 15 flows into the third sub-cavity 27. The two ends of the fifth pipeline assembly are respectively connected to the second accommodating member 17 and the third pumping member, so that the waste liquid in the third sub-cavity 27 flows into the second accommodating cavity; the fourth pumping member includes a fourth cylinder body 31 and a fourth piston 29 slidably connected to the fourth cylinder body 31. A fourth sub-cavity 30 is formed by enclosing the fourth cylinder body 31 and the fourth piston 29. The third piston 28 is located at a position of the third sub-cavity 27 close to the fourth sub-cavity 30, and the fourth piston 29 is located at a position of the fourth sub-cavity 30 close to the third sub-cavity 27. The two ends of the eighth pipeline assembly are respectively connected to the fourth pumping member and the liquid return port 15, so that the waste liquid at the liquid return port 15 flows into the fourth sub-cavity 30. The two ends of the seventh pipeline assembly are respectively connected to the second accommodating member 17 and the fourth pumping member, so that the waste liquid in the fourth sub-cavity 30 flows into the second accommodating cavity.

[0070] The linkage structure 52 further includes a third linkage member 25 connected to the first linkage member 21 and the second linkage member 48, so that the first linkage member 21 and the second linkage member 48 can move synchronously. Among them, the first linkage member 21 can be a first gear shaft, the second linkage member 48 can be a second gear shaft, and the third linkage member 25 can be a driving gear that meshes with both the first gear shaft and the second gear shaft. The two ends of the first gear shaft are respectively fixed to the first piston 20 and the second piston 22, and the two ends of the second gear shaft are respectively fixed to the third piston 28 and the fourth piston 29. The first gear shaft and the second gear shaft are respectively located on both sides of the driving gear along the second direction, and the first direction intersects with the second direction.

[0071] In some embodiments, the first direction, the second direction and the axial direction of the driving gear are perpendicular to each other in pairs. That is to say, the first gear shaft and the second gear shaft can be arranged at the same height along the axial direction of the driving gear, thereby reducing the overall height of the linkage structure 52. When the driving gear rotates clockwise to move the first gear shaft away from the first sub-chamber 19, the first piston 20 and the second piston 22 slide away from the first sub-chamber 19 at the same time. The volume in the first sub-chamber 19 increases and the volume in the second sub-chamber 23 decreases. The perfusion liquid in the first accommodating chamber can flow to the first sub-chamber 19 through the first pipeline assembly, and the perfusion liquid in the second sub-chamber 23 can flow to the liquid outlet 14 through the fourth pipeline assembly, so that the pressure on the proximal side of the first flow regulating component increases to the difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component is greater than or equal to the first preset value, and the first flow regulating component is adjusted to the conducting state. The perfusion liquid flowing out of the liquid outlet 14 can flow smoothly to the perfusion chamber 4 through the perfusion pipeline 1, the elastic element and the first flow regulating component. After the perfusion liquid enters the perfusion chamber 4, it is mixed with the wear particles in the perfusion chamber 4 to form waste liquid with a certain pressure; at the same time, the second gear shaft, the third piston 28 and the fourth piston 29 slide towards the third sub-chamber 27. The volume in the third sub-chamber 27 decreases and the volume in the fourth sub-chamber 30 increases. When the pressure on the distal side of the second flow regulating component is greater than the second preset value, the second flow regulating component is in the open state. The waste liquid in the perfusion chamber 4 flows through the second flow regulating component through the drain pipeline 2 and reaches the return liquid port 15. The waste liquid at the position of the return liquid port 15 can flow to the fourth sub-chamber 30 through the eighth pipeline assembly, and the waste liquid in the third sub-chamber 27 can flow to the second accommodating chamber through the fifth pipeline assembly.

[0072] When the driving gear rotates counterclockwise to move the first gear axially towards the first sub-chamber 19, the first piston 20 and the second piston 22 slide towards the first sub-chamber 19 simultaneously. The volume in the first sub-chamber 19 decreases and the volume in the second sub-chamber 23 increases. The perfusion liquid in the first accommodating chamber can flow to the second sub-chamber 23 through the third pipeline assembly, and the perfusion liquid in the first sub-chamber 19 can flow to the liquid outlet 14 through the second pipeline assembly, so that the pressure on the proximal side of the first flow regulating component increases to a difference between the pressure on the proximal side of the first flow regulating component and the pressure on the distal side of the first flow regulating component that is greater than or equal to the first preset value. The first flow regulating component is adjusted to the conducting state. The perfusion liquid flowing out from the liquid outlet 14 can flow smoothly to the perfusion chamber 4 through the perfusion pipeline 1, the elastic element, and the first flow regulating component. After the perfusion liquid enters the perfusion chamber 4, it mixes with the wear particles in the perfusion chamber 4 to form waste liquid with a certain pressure. At the same time, the second gear shaft, the third piston 28, and the fourth piston 29 slide away from the third sub-chamber 27. The volume in the third sub-chamber 27 increases and the volume in the fourth sub-chamber 30 decreases. When the pressure on the distal side of the second flow regulating component is greater than the second preset value, the second flow regulating component is in the open state. The waste liquid in the perfusion chamber 4 flows through the second flow regulating component through the drain pipeline 2 and reaches the liquid return port 15. The waste liquid at the liquid return port 15 can flow to the third sub-chamber 27 through the sixth pipeline assembly, and the waste liquid in the fourth sub-chamber 30 can flow to the second accommodating chamber through the seventh pipeline assembly.

[0073] As Figure 5 shown, in some embodiments, the first pipeline assembly includes a first pipeline 32 and a first valve 33, the second pipeline assembly includes a second pipeline 34 and a second valve 35, the third pipeline assembly includes a third pipeline 36 and a third valve 37, and the fourth pipeline assembly includes a fourth pipeline 39 and a fourth valve 38. Among them, the first valve 33 and the third valve 37 can be one-way valves with the opening direction facing away from the first accommodating member 16, and the second valve 35 and the fourth valve 38 can be one-way valves with the opening direction facing the liquid outlet 14. The fifth pipeline assembly includes a fifth pipeline 40 and a fifth valve 41, the sixth pipeline assembly includes a sixth pipeline 42 and a sixth valve 43, the seventh pipeline assembly includes a seventh pipeline 44 and a seventh valve 45, and the eighth pipeline assembly includes an eighth pipeline 46 and an eighth valve 47. Among them, the fifth valve 41 and the seventh valve 45 can be one-way valves with the opening direction facing the second accommodating member 17, and the sixth valve 43 and the eighth valve 47 can be one-way valves with the opening direction facing away from the liquid return port 15. By setting multiple one-way valves, the reverse flow of the perfusion liquid and the waste liquid in the corresponding pipelines can be prevented, and the structure is simple and easy to implement.

[0074] In some embodiments, the opening pressure of the one-way valve included in the perfusion device 49 can be from 1 kPa to 10 kPa.

[0075] AsFigure 5 As shown, in some embodiments, for the perfusion structure 50, the first pipeline and the second pipeline can be combined into one pipeline near the part of the first sub-chamber 19 and then connected to the first sub-chamber 19. The third pipeline and the fourth pipeline can be combined into one pipeline near the part of the second sub-chamber 23 and then connected to the second sub-chamber 23. The first pipeline and the third pipeline can be combined into one pipeline near the part of the first accommodation chamber and then connected to the first accommodation chamber. The second pipeline and the fourth pipeline can be combined into one pipeline near the part of the liquid outlet 14 and then connected to the liquid outlet 14. It can be understood that for the suction structure 51, a similar arrangement method can also be adopted to achieve the purpose of simplifying the pipeline structure of the perfusion device 49.

[0076] As described above, the above is only the specific implementation manner of the present application. Those skilled in the art can clearly understand that for the convenience and simplicity 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, which will not be repeated here. 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 by 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 catheter, characterized in that, Comprising: An infusion cavity for intervening in a patient's body; An infusion pipeline, the distal end of the infusion pipeline is connected to the infusion cavity, and the proximal end of the infusion pipeline is used to be connected to the liquid outlet of an infusion device; An elastic element installed on the infusion pipeline; A first flow rate regulating component installed on the infusion pipeline and located between the elastic element and the infusion cavity, When the difference between the pressure on the proximal side and the pressure on the distal side of the first flow rate regulating component is greater than or equal to a first preset value, the first flow rate regulating component is in a conducting state, and the first preset value is greater than or equal to zero; When the difference between the pressure on the proximal side and the pressure on the distal side of the first flow rate regulating component is less than the first preset value, the first flow rate regulating component is in a cut-off state.

2. The blood pumping catheter according to claim 1, wherein, The elastic element includes: A first filtering component, the first filtering component has a first filter element for filtering impurities and bubbles mixed in the infusion liquid flowing through the first filter element; and / or, A pressure storage component, the pressure storage component has a pressure storage cavity, during the process of the increase of the infusion liquid pressure at the installation position of the pressure storage component, the pressure storage cavity is used to suck the infusion liquid from the infusion pipeline and store pressure; during the process of the decrease of the infusion liquid pressure at the installation position of the pressure storage component, the pressure storage cavity is used to press the infusion liquid into the infusion pipeline and release pressure.

3. The blood pumping catheter according to claim 2, wherein The elastic element includes the first filtering component and the pressure storage component, and the pressure storage component is located on the proximal side of the first filtering component.

4. The blood pumping catheter according to claim 1 or 2, characterized in that, The blood pumping catheter further includes a second filtering component located on the distal side of the first flow rate regulating component, and the second filtering component has a second filter element for filtering impurities and bubbles mixed in the infusion liquid flowing through the second filter element.

5. The blood pumping catheter according to claim 1, characterized in that, The first flow rate regulating component includes a first one-way valve, and the opening direction of the first one-way valve faces the infusion cavity.

6. The blood pumping catheter according to claim 5, characterized in that, The first flow rate regulating component includes a first one-way valve, and the opening direction of the first one-way valve faces the infusion cavity. The first one-way valve includes: A valve body having an internal flow channel for the flow of the infusion liquid; A valve core movably installed in the internal flow channel; When the difference between the pressure on the proximal side and the pressure on the distal side of the internal flow channel is less than the opening pressure of the first one-way valve, the valve core can tightly press against and block the inner wall or the end of the internal flow channel, and the contact surface between the valve core and the internal flow channel is in the same plane or the radius of the contact surface between the valve core and the internal flow channel gradually becomes smaller in the direction from the distal side to the proximal side of the internal flow channel.

7. The blood pumping catheter according to claim 1, characterized in that, It further includes a drainage pipeline, the distal end of the drainage pipeline is connected to the infusion cavity, and the proximal end of the drainage pipeline is used to be connected to the liquid return port of the infusion device.

8. The blood pumping catheter according to claim 7, wherein It further includes a second flow rate regulating component installed on the drainage pipeline. When the pressure on the distal side of the second flow rate regulating component is less than or equal to a second preset value, the second flow rate regulating component is in a cut-off state; When the pressure on the distal side of the second flow regulating component is greater than the second preset value, the second flow regulating component is in an open state.

9. The blood pumping catheter according to claim 8, wherein The second flow regulating component includes a second one-way valve, and the opening direction of the second one-way valve faces away from the perfusion cavity.

10. The blood pumping catheter according to claim 8, characterized in that, The second preset value is between 11 kPa and 30 kPa; alternatively, the second preset value is greater than or equal to the systolic blood pressure of the patient.

11. The blood pumping catheter according to claim 8, characterized in that, When the pressure on the distal side of the second flow regulating component is greater than the second preset value and less than the third preset value, the flow resistance of the waste liquid flowing through the second flow regulating component is the first resistance value; When the pressure on the distal side of the second flow regulating component is greater than or equal to the third preset value, the flow resistance of the waste liquid flowing through the second flow regulating component is the second resistance value, the third preset value is greater than the second preset value, and the first resistance value is greater than the second resistance value.

12. The blood pumping catheter according to claim 11, wherein The second flow regulating component includes: A multi-way regulating valve, including a first port and more than two second ports. The first port is connected to the perfusion cavity through a corresponding drainage pipeline, and the plurality of second ports are respectively communicated with the first port through corresponding flow channels; A first valve group, including more than one second one-way valve. One end of the second one-way valve is connected to the liquid return port through a corresponding drainage pipeline, and the other end of the second one-way valve is connected to a part of the second ports in one-to-one correspondence. The opening direction of the second one-way valve faces away from the perfusion cavity; A second valve group, including more than one third one-way valve. One end of the third one-way valve is connected to the liquid return port through a corresponding drainage pipeline, and the other end of the third one-way valve is connected to another part of the second ports in one-to-one correspondence. The opening direction of the third one-way valve faces away from the perfusion cavity, and the opening pressure of the second one-way valve is greater than the opening pressure of the third one-way valve. When the pressure on the distal side of the first port is less than the third preset value, the second port corresponding to the second one-way valve is in a conducting state, and the second port corresponding to the third one-way valve is in a cut-off state; when the pressure on the distal side of the first port is greater than or equal to the third preset value, the second port corresponding to the third one-way valve is in a conducting state, and the second port corresponding to the second one-way valve is in a cut-off state.

13. The blood pumping catheter according to claim 11, wherein, The difference between the third preset value and the second preset value is between 1 kPa and 20 kPa.

14. The blood pumping catheter according to claim 1, wherein The flow area of the first flow regulating component is smaller than the flow area of the perfusion pipeline; and / or The blood pumping catheter further includes: A working instrument for intervening in the patient's body; A power assembly connected to the working instrument to drive the working instrument to complete corresponding actions. Part of the power assembly is located in the perfusion cavity, or the perfusion cavity is formed by enclosing part of the power assembly.

15. A ventricular assist system, characterized in that, Including the blood pumping catheter according to any one of claims 1 to 14, further including a perfusion device, and the perfusion device includes: A perfusion structure having a liquid outlet, and the liquid outlet is connected to the proximal end of the perfusion pipeline for pressing perfusion liquid into the perfusion pipeline; A suction structure having a liquid return port connected to the proximal end of a drainage pipeline for sucking waste liquid in the drainage pipeline; A linkage structure connected to the perfusion structure and the suction structure, such that while the perfusion structure is pressing perfusion liquid into the perfusion pipeline, the suction structure can suck the waste liquid in the drainage pipeline.

16. The ventricular assist system according to claim 15, wherein the linkage structure includes a first linkage member and a second linkage member capable of synchronous movement; the perfusion structure includes a first pumping member and a second pumping member, both of which can suck the perfusion liquid to be perfused and convey the sucked perfusion liquid to the liquid outlet. The first pumping member and the second pumping member are connected by the first linkage member, such that while one of the first pumping member and the second pumping member conveys the sucked perfusion liquid to the liquid outlet, the other can suck the perfusion liquid to be perfused; the suction structure includes a third pumping member and a fourth pumping member, both of which can suck the waste liquid in the drainage pipeline through the liquid return port and discharge the sucked waste liquid. The third pumping member and the fourth pumping member are connected by the second linkage member, such that while one of the third pumping member and the fourth pumping member discharges the sucked waste liquid, the other can suck the waste liquid in the drainage pipeline.

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