Pumping catheter and ventricular assist system

Abstract

The invention 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] This application relates to the field of medical device technology, and in particular to a blood pumping catheter and ventricular assist system. Background Technology

[0002] A ventricular assist system is an auxiliary system that pumps blood from the ventricles to other parts of the body. Ventricular assist systems are often used in patients with heart weakness or heart failure to partially or largely replace the pumping function of the ventricles.

[0003] In related technologies, ventricular assist systems generally include a pumping catheter and a perfusion device. The distal end of the pumping catheter is equipped with a power unit and an impeller. The power unit drives the impeller to rotate, causing blood to flow more rapidly in the pumping direction, thus increasing blood flow rate. The pumping catheter typically also includes a perfusion chamber and perfusion tubing connected to the perfusion chamber. The impeller is located outside the perfusion chamber, and at least part of the power unit is installed inside the perfusion chamber. The perfusion device delivers perfusion fluid to the perfusion chamber through the perfusion tubing to absorb the heat generated by the power unit during operation, reducing the risk of patient discomfort due to overheating of the power unit.

[0004] Currently, some perfusion lines are equipped with elastic elements. When the internal pressure at the location of the elastic element changes, the elastic element exhibits elastic fluctuations. A patient's blood pressure typically fluctuates cyclically between diastolic and systolic pressure. Each time the patient's blood pressure fluctuates from diastolic to systolic, the blood pressure increases, and this increased pressure is transmitted through the perfusion chamber and perfusion line to the elastic element, causing it to contract. Therefore, blood easily flows through the perfusion line towards the perfusion device. During this cyclical fluctuation of blood pressure between diastolic and systolic pressure, the elastic fluctuations of the elastic element cause blood to gradually flow through the perfusion line towards the perfusion device, ultimately leading to blood loss. Summary of the Invention

[0005] This application provides a blood pumping catheter and ventricular assist system that can significantly reduce the risk of blood flowing back along the perfusion line to the proximal side of the first flow regulating component and the perfusion device, thereby reducing blood loss in patients.

[0006] In a first aspect, embodiments of this application provide a blood pumping catheter, comprising: an infusion chamber for insertion into a patient's body; an infusion line, the distal end of which is connected to the infusion chamber, and the proximal end of which is connected to the outlet of an infusion device; an elastic element installed in the infusion line; and a first flow regulating component installed in the infusion line and located between the elastic element and the infusion chamber. When the difference between the proximal pressure and the distal pressure 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 proximal pressure and the distal pressure of the first flow regulating component is less than the first preset value, the first flow regulating component is in a cut-off state.

[0007] In some embodiments, the elastic element includes: a first filter element having a first filter element for filtering impurities and air bubbles entrained in the infusion fluid flowing through the first filter element; and / or a pressure storage element having a pressure storage chamber for drawing in infusion fluid from the infusion line and storing pressure during an increase in the pressure of the infusion fluid at the installation location of the pressure storage element; and for injecting infusion fluid into the infusion line and releasing pressure during a decrease in the pressure of the infusion fluid at the installation location of the pressure storage element.

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

[0009] In some embodiments, the blood pumping catheter further includes a second filtering component located at the distal end of the first flow regulating component. The second filtering component has a second filter element for filtering impurities and air bubbles contained in the perfusion fluid flowing through the second filter element.

[0010] In some embodiments, the first flow regulating component includes a first check valve, the opening direction of which is toward the infusion chamber.

[0011] In some embodiments, the first check valve includes: a valve body having an internal flow channel for the flow of perfusion fluid; and a valve core movably mounted 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 check valve, the valve core can press against and seal against the inner wall of the internal flow channel or the end of the internal flow channel. The contact surfaces of the valve core and the internal flow channel are located in the same plane or the radius of the contact surfaces of the valve core and the internal flow channel gradually decreases 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 line, the distal end of which is connected to the perfusion chamber, and the proximal end of which is connected to the 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 line. 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 closed 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, the opening direction of which is opposite to that of the infusion chamber.

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

[0016] In some embodiments, when the pressure at the distal end of the second flow regulating component is greater than a 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 at the distal end of the second flow regulating component is greater than or equal to a 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-port regulating valve, including a first port and two or more second ports, wherein the first port is connected to the infusion chamber through a corresponding drain pipe, and the multiple second ports are respectively connected to the first port through corresponding flow channels; a first valve group, including one or more second check valves, wherein one end of the second check valve is connected to the return port through a corresponding drain pipe, and the other end of the second check valve is connected to a portion of the second ports one-to-one, and the opening direction of the second check valve is opposite to the infusion chamber; and a second valve group, including one or more third check valves, wherein one end of the third check valve is connected to the return port through a corresponding drain pipe, and the other end of the third .... One end is connected to the other part of the second port in a one-to-one correspondence. The opening direction of the third check valve is opposite to the infusion chamber. 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 closed 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 closed 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 tubing; and / or, the blood pumping catheter further includes: a working instrument for insertion into the patient's body; and a power component connected to the working instrument to drive the working instrument to perform corresponding actions, wherein a portion of the power component is located within the perfusion chamber, or the perfusion chamber is formed by a portion of the power component enclosing it.

[0020] Secondly, embodiments of this application provide a ventricular assist system, including the aforementioned blood pumping catheter, and further including a perfusion device. The perfusion device includes: a perfusion structure having an outlet connected to the proximal end of the perfusion line for pressurizing perfusion fluid into the perfusion line; a suction structure having a return port connected to the proximal end of the drainage line for suctioning waste fluid from the drainage line; and a linkage structure connected to the perfusion structure and the suction structure, so that while the perfusion structure presses perfusion fluid into the perfusion line, the suction structure can suction waste fluid from the drainage line.

[0021] In some embodiments, the linkage structure includes a first linkage member and a second linkage member capable of synchronous movement; the infusion structure includes a first suction member and a second suction member, both of which can suction the infusion fluid to be infused and deliver the suctioned infusion fluid to the outlet. The first suction member and the second suction member are connected through a first linkage member, so that while one of the first and second suction members is delivering the suctioned infusion fluid to the outlet, the other can suction the infusion fluid to be infused; the suction structure includes a third suction member and a fourth suction member, both of which can suction waste liquid in the drainage pipeline through the return port and discharge the suctioned waste liquid. The third suction member and the fourth suction member are connected through a second linkage member, so that while one of the third and fourth suction members is discharging the suctioned waste liquid, the other can suction waste liquid in the drainage pipeline.

[0022] The blood pumping catheter and ventricular assist system of this application embodiment include a perfusion chamber, a perfusion line, an elastic element, and a first flow regulating component. The distal end of the perfusion line is connected to the perfusion chamber, and the proximal end of the perfusion line is used to connect to the outlet of the perfusion device. The elastic element and the first flow regulating component are both installed in the perfusion line. The first flow regulating component is located between the elastic element and the perfusion chamber. When the difference between the proximal side pressure and the distal side pressure 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 proximal side pressure and the distal side pressure 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 proximal pressure and the distal pressure of the first flow regulating component is greater than or equal to a 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 then adjusted to a conductive state, allowing the perfusion fluid flowing from the outlet of the perfusion device to flow smoothly into the perfusion chamber after passing through the elastic element and the first flow regulating component via the perfusion tubing. During each fluctuation of the patient's blood pressure from diastolic to systolic, the patient's blood pressure increases, and this increased pressure is transmitted to the distal side of the first flow regulating component via the perfusion chamber and perfusion tubing. This can easily lead to the distal pressure of the first flow regulating component being greater than the proximal pressure. When the pressure difference on the distal side 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. This prevents blood from flowing from the patient's body through the perfusion chamber and perfusion tubing to the perfusion device 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. This reduces blood loss from the patient and lowers the risk of thrombus formation and blockage in the perfusion device and blood pumping catheter. Consequently, it can relatively improve the operational stability and service life of the perfusion tubing on the proximal side of the perfusion device and blood pumping catheter. In addition, the perfusion fluid not only dissipates heat from the components in the perfusion chamber, thus reducing the risk of patient discomfort due to overheating of the components in the perfusion chamber, but also flushes away wear particles generated during the operation of the components in the perfusion chamber, preventing excessive wear of the components in the perfusion chamber and providing a certain degree of lubrication to the components in the perfusion chamber. Attached Figure Description

[0023] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments of this application will be briefly introduced below. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0024] Figure 1 This is a schematic diagram of the structure of a blood pumping catheter provided in some embodiments of this application;

[0025] Figure 2 This is a schematic diagram of the structure of a blood pumping catheter provided in other embodiments of this application;

[0026] Figure 3 Schematic diagrams of the blood pumping catheter provided in some embodiments of this application;

[0027] Figure 4 This is a schematic diagram of the structure of a blood pumping catheter provided in some embodiments of this application;

[0028] Figure 5 This application provides schematic diagrams of the structure of a ventricular assist system according to some embodiments.

[0029] Figure 6 This is a schematic diagram of the internal structure of the infusion device provided in some embodiments of this application.

[0030] In the diagram: 1. Injection pipeline; 2. Drainage pipeline; 3. First check valve; 4. Injection chamber; 5. Output shaft; 6. Working instrument; 7. Second filter component; 8. Pressure storage component; 9. First filter component; 10. Second check valve; 11. Third check valve; 12. Multi-way regulating valve; 13. Pressure sensor; 14. Outlet; 15. Return port; 16. First receiving component; 17. Second receiving component; 18. First cylinder; 19. First sub-chamber; 20. First piston; 21. First linkage component; 22. Second piston; 23. Second sub-chamber; 24. Second cylinder; 25. Third linkage component; 26. 27. Third cylinder; 28. Third sub-chamber; 29. ​​Third piston; 30. Fourth piston; 31. Fourth cylinder; 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; 49. Injection device; 50. Injection structure; 51. Suction structure; 52. Linkage structure. Detailed Implementation

[0031] The features and exemplary embodiments of various aspects of this application will be described in detail below. To make the objectives, technical solutions, and advantages of this application clearer, the 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 this application and not to limit it. For those skilled in the art, this application can be implemented without some of these specific details. The following description of the embodiments is merely to provide a better understanding of this application by illustrating examples.

[0032] It should be noted that, in this document, relational terms such as "first" and "second" are used merely to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitations, an element defined by the phrase "comprising..." does not exclude the presence of additional identical elements in the process, method, article, or apparatus that includes said element.

[0033] Currently, ventricular assist systems generally include a pumping catheter and a perfusion device. The distal end of the pumping catheter houses a power assembly and an impeller. The power assembly includes an output shaft, and the impeller is connected to a portion of the power assembly located within the perfusion chamber via the output shaft. The power assembly transmits torque to the output shaft, driving the impeller to rotate and accelerating blood flow in the pumping direction, thus increasing blood volume. The pumping catheter typically also includes a perfusion chamber and perfusion tubing connected to it. The impeller is located outside the perfusion chamber, and at least a portion of the power assembly is installed within it. Specifically, for the internal motor mode, the power assembly within the perfusion chamber includes the end of the output shaft furthest from the impeller and a bearing fitted onto the output shaft. For the external motor mode, the power assembly within the perfusion chamber includes the end of the output shaft furthest from the impeller, a bearing fitted onto the output shaft, and a transmission coil partially located within the perfusion chamber. The end of the transmission coil within the perfusion chamber is connected to the transmission shaft, and the end outside the perfusion chamber is connected to the external motor. The output shaft extends from inside the perfusion chamber to the outside. The perfusion device delivers perfusion fluid to the perfusion chamber through the perfusion tubing to absorb the heat generated by the power assembly during operation, reducing the risk of patient discomfort due to overheating of the power assembly. The heat generated by the power assembly during operation is generally due to mechanical friction. For example, during operation, the bearings on the output shaft generate heat due to friction between the inner ring of the bearing and the bearing balls.

[0034] Studies have found that a patient's blood pressure generally fluctuates cyclically between diastolic and systolic pressure. During each fluctuation from diastolic to systolic pressure, the patient's blood pressure increases, and this increased pressure is transmitted through the perfusion chamber and tubing to the elastic element, causing it to contract. Therefore, blood easily flows through the perfusion tubing to the perfusion device. During this cyclical fluctuation of blood pressure between diastolic and systolic pressure, the elastic fluctuations of the elastic element cause blood to gradually flow through the perfusion tubing towards the perfusion device, ultimately leading to blood loss.

[0035] To address the problems of the prior art, this application provides a blood pumping catheter and a ventricular assist system. A detailed description is provided below with reference to the accompanying drawings.

[0036] Figure 1 This is a schematic diagram of the structure of a blood pumping catheter provided in some embodiments of this application;

[0037] Figure 5 This is a schematic diagram of the structure of a ventricular assist system provided in some embodiments of this application.

[0038] Combination Figure 1 and Figure 5As can be seen, this application provides a blood pumping catheter, including a perfusion chamber 4, a perfusion line 1, an elastic element (not shown), and a first flow regulating component (not shown). The perfusion chamber 4 is used for insertion into a patient's body; the distal end of the perfusion line 1 is connected to the perfusion chamber 4, and the proximal end of the perfusion line 1 is used to connect to the outlet 14 of the perfusion device 49. The elastic element is installed in the perfusion line 1. Specifically, the elastic element can be a functional component in the blood pumping catheter that can perform certain functions, such as a filtering component or a pressure storage component, which has an internal elastic structure, and this elastic structure is located in the flow path of the perfusion line. The first flow regulating component is installed in the infusion line 1 and located between the elastic element and the infusion chamber 4. When the difference between the proximal pressure and the distal pressure 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 proximal pressure and the distal pressure of the first flow regulating component is less than the first preset value, the first flow regulating component is in a cut-off state. It can be understood that in this application, the proximal end refers to the end facing the operator or physician, and the distal end refers to the end away from the operator or physician. The connection of components with internal media flow spaces essentially means that the internal media flow spaces of the corresponding components are connected. Specifically, in this embodiment, the two ends of the infusion line 1 are connected to the infusion chamber 4 and the outlet 14 of the infusion device 49, respectively, meaning that the flow channels inside the infusion line 1 are connected to the infusion chamber 4 and the outlet 14, respectively. Furthermore, in this application, the difference between one pressure and another pressure refers to the value obtained by subtracting the value of another pressure from the value of one pressure. For example, the difference between the proximal pressure and the distal pressure of the first flow regulating component can be understood as the difference between the value of the proximal pressure and the value of the distal pressure of the first flow 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 still other application scenarios, the difference can be less than 0.

[0039] When the difference between the proximal pressure and the distal pressure of the first flow regulating component is greater than or equal to a 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 outlet 14 of the perfusion device 49 flows smoothly to the perfusion chamber 4 after passing through the elastic element and the first flow regulating component via the perfusion line 1. During each fluctuation of the patient's blood pressure from diastolic to systolic, the patient's blood pressure increases, and the increased pressure of the blood in the patient's body is transmitted to the distal side of the first flow regulating component through the perfusion chamber 4 and the perfusion line 1, which easily leads to the distal pressure of the first flow regulating component being greater than the proximal pressure of the first flow regulating component. When the pressure difference 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. This prevents blood from flowing from the patient's body through the perfusion chamber 4 and perfusion tubing 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. This reduces blood loss from the patient and lowers the risk of thrombus formation and blockage in the perfusion device 49 and the blood pumping catheter. Consequently, it can relatively improve the operational stability and service life of the perfusion device 49 and the perfusion tubing 1 on the proximal side of the blood pumping catheter. In addition, the perfusion fluid not only dissipates heat from the components in the perfusion chamber 4, thus reducing the risk of patient discomfort due to overheating of the components in the perfusion chamber 4, but also flushes away wear particles generated during the operation of the components in the perfusion chamber 4, preventing excessive wear of the components in the perfusion chamber 4 and providing a certain degree of lubrication to the components in the perfusion chamber 4.

[0040] In some embodiments, the proximal end of the infusion tubing 1 is detachably installed at the outlet 14 of the infusion device 49. When the infusion device 49 is damaged and needs replacement, or when it needs to be replaced due to patient transfer, medical personnel can directly detach the proximal end of the infusion tubing 1 from the currently connected infusion device 49 and reinstall it at the outlet 14 of the next infusion device 49 to be connected, making the operation convenient. Specifically, the proximal end of the infusion tubing 1 can be detachably installed at the outlet 14 of the infusion device 49 using a Luer connector. The Luer connector has a mature structure, is easy to design and manufacture, or can be purchased directly, resulting in low cost.

[0041] like Figure 1As shown, in some embodiments, the elastic element includes a first filter element 9 having a first filter cartridge for filtering impurities and air bubbles mixed in with the perfusion fluid flowing through the first filter cartridge. Air bubbles entering the patient's body can form air embolisms. By setting up the filter element, the risk of impurities and air bubbles flowing into the patient's body and causing discomfort to the patient can be reduced.

[0042] like Figure 1 As shown, in some embodiments, the elastic element includes a pressure storage component 8, which has a pressure storage cavity. Specifically, at least one wall of the pressure storage cavity is elastic. During an increase in the injection fluid pressure at the installation location of the pressure storage component 8, the injection fluid pressure within the pressure storage cavity increases, causing the elastic wall of the pressure storage cavity to expand outwards, increasing the volume of the pressure storage cavity. This allows the pressure storage cavity to draw injection fluid from the injection line 1 and store pressure. Conversely, during a decrease in the injection fluid pressure at the installation location of the pressure storage component 8, the injection fluid pressure within the pressure storage cavity decreases, causing the elastic wall of the pressure storage cavity to contract inwards, decreasing the volume of the pressure storage cavity. This allows the pressure storage cavity to pressurize injection fluid into the injection line 1 and release pressure. It is understood that the injection fluid pressure at the installation location of the pressure storage component 8 refers to the injection fluid pressure located near the pressure storage component 8 and within the injection line 1. When the pressure of the injection fluid output by the injection device 49 fluctuates, the pressure storage component 8 can smooth out the peaks and fill the valleys of the injection fluid pressure in the injection pipeline 1, so that the pressure of the injection fluid in the injection pipeline 1 is relatively stable.

[0043] like Figure 1 As shown, in some embodiments, the elastic element includes a first filter element 9 and a pressure storage element 8, with the pressure storage element 8 located on the proximal side of the first filter element 9. The pressure storage element 8 is close to the infusion device 49, enabling it to quickly respond to and absorb pressure fluctuations in the infusion fluid caused during the operation of the infusion device 49.

[0044] Figure 2 This is a schematic diagram of the structure of a blood pumping catheter provided in some other embodiments of this application.

[0045] like Figure 2 As shown, in some embodiments, the blood pumping catheter further includes a second filter element 7 located distal to the first flow regulating element. The second filter element 7 has a second filter cartridge for filtering impurities and air bubbles entrained in the perfusion fluid flowing through the second filter cartridge. The second filter element 7 can filter out as many tiny air bubbles as possible generated by the first flow regulating element during the adjustment of its operating state, thereby reducing the risk of these air bubbles entering the patient's body and causing discomfort.

[0046] like Figure 1As shown, in some embodiments, the first flow regulating component includes a first one-way valve 3, which opens towards the injection chamber 4. This design is simple and low-cost. It should be noted that "opening direction of the one-way valve towards a component" means that the outlet of the one-way valve is close to the corresponding component. Specifically, in this embodiment, "opening direction of the first one-way valve 3 towards the injection chamber 4" means that the outlet of the first one-way valve 3 faces the injection chamber 4, and the injection fluid flowing through the first one-way valve 3 can only flow from the side furthest from the injection chamber 4 to the side closest to the injection chamber 4. In other embodiments, a solenoid valve can be used instead of the first one-way valve 3 to achieve the corresponding function by adjusting the valve opening of the corresponding solenoid valve. That is, the solenoid valve controls the opening and closing of the valve according to the liquid pressure on both sides of the valve body, achieving unidirectional flow performance along the injection 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 allow the perfusion fluid to flow into the perfusion chamber 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, thereby reducing the energy consumption of the perfusion device 49 and improving the operational stability of the perfusion device 49 and the blood pumping catheter. It should be noted that the opening pressure of the one-way valve refers to the pressure difference between the inlet and outlet during forward conduction. That is, in this embodiment, the opening pressure of the first one-way valve 3 is equal to a first preset value. When the difference between the proximal pressure and the distal pressure of the first one-way valve 3 is greater than 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 to the distal side of the first one-way valve 3.

[0048] In some embodiments, the first check valve 3 includes a valve body and a valve core. The valve body has an internal flow channel for the flow of injection fluid. The valve core is movably mounted within the internal flow channel. Specifically, the first check valve 3 further includes a reset member connected to the valve core. The reset member provides a reset force to the valve core pointing towards the proximal side of the first check valve 3. The opening pressure of the first check valve 3 is equal to the sum of the frictional force between the valve core and the valve body and the reset force. The reset member can be an elastic element, such as a coil spring, leaf spring, or diaphragm spring. When the pressure difference between the proximal and distal sides of the internal flow channel is greater than or equal to the opening pressure of the first one-way valve 3, there is a gap between the valve core and the internal flow channel for the perfusion fluid to flow through. When the pressure difference between the proximal and distal sides of the internal flow channel is less than the opening pressure of the first one-way valve 3, the valve core can press against and seal against the inner wall or end of the internal flow channel to keep the internal flow channel in a closed 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 decreases from the distal side to the proximal side of the internal flow channel. In other words, there is no step-like abrupt change 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 closed state or switching to the open state, air bubbles are less likely to appear at the contact position between the valve core and the internal flow channel, thereby reducing the risk of corresponding air bubbles entering the patient's body and causing patient discomfort. It is understood that the proximal pressure of the internal flow channel is the same as the proximal pressure of the first flow regulating component; the distal pressure of the internal flow channel is the same as the distal pressure of the first flow regulating component.

[0049] In the existing technology, some power components within the perfusion chamber 4 experience mutual friction during operation, generating heat and wear particles. After the perfusion fluid enters the perfusion chamber 4 through the perfusion pipe 1, it exchanges heat with the components within the perfusion chamber 4 to achieve cooling. The perfusion fluid that has completed heat exchange mixes with the wear particles to form waste liquid. Currently, this waste liquid is generally discharged into the patient's body through the gap between the output shaft 5 and the wall of the perfusion chamber 4, which can easily cause patient discomfort. Furthermore, since the total amount of waste liquid that a patient can absorb is limited, it is necessary to control the flow rate of the perfusion fluid within a predetermined range to ensure that the total amount of waste liquid entering the patient's body during surgery meets requirements, which can easily lead to unsatisfactory heat dissipation from the perfusion chamber 4.

[0050] Figure 3 This is a schematic diagram of the structure of a blood pumping catheter provided in some embodiments of this application.

[0051] like Figures 1 to 3As shown, in some embodiments, the blood pumping catheter also includes a drainage line 2, the distal end of which is connected to the perfusion chamber 4, and the proximal end of which is connected to the return port 15 of the perfusion device 49. Most of the waste fluid can be discharged through the drainage line 2 to the return port 15 of the perfusion device 49, which can reduce the risk of patient discomfort caused by a large amount of waste fluid 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 fluid in the perfusion line 1.

[0052] In some embodiments, the proximal end of the drainage line 2 is detachably installed to the return port 15 of the infusion device 49. When the infusion device 49 is damaged and needs to be replaced, or when the infusion device 49 needs to be replaced due to the need to transfer a patient, medical personnel can directly detach the proximal end of the drainage line 2 from the connected infusion device 49 and reinstall it to the return port 15 of the next infusion device 49 to be connected, which is convenient. Specifically, the proximal end of the drainage line 2 can be detachably installed to the return port 15 of the infusion device 49 through a Luer connector. The Luer connector has a mature structure, is easy to design and manufacture, or can be purchased directly, and has a low cost.

[0053] like Figure 3 As shown, in some embodiments, the blood pumping catheter further includes a second flow regulating component installed in the drainage line 2. 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 closed 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. When the pressure at the distal end of the second flow regulating component is less than or equal to the first preset value, after the perfusion fluid flows into the perfusion chamber 4 and forms waste fluid, the pressure of the waste fluid in the perfusion chamber 4 is relatively low, and blood outside the perfusion chamber 4 can easily enter the perfusion chamber 4. Adjusting the second flow regulating component to the cut-off state can prevent the patient's blood from flowing to the perfusion device 49 through the drainage pipe 2 and the second flow regulating component. When the pressure at the distal end of the second flow regulating component is greater than the first preset value, after the perfusion fluid flows into the perfusion chamber 4 and forms waste fluid, the pressure of the waste fluid in the perfusion chamber 4 is relatively high, which can largely block the blood in the patient's body from entering the perfusion chamber 4. In other words, after adjusting the second flow regulating component to the open state, the blood in the patient's body is not easy to enter the perfusion chamber 4, and the liquid flowing into the drainage pipe 2 is basically waste fluid, which can relatively reduce the patient's blood loss.

[0054] like Figure 3As shown, in some embodiments, the second flow regulating component includes a second one-way valve 10, the opening direction of which is away from the filling chamber 4. This design is simple and low-cost. It should be noted that "opening direction away from a component" means that the inlet of the one-way valve is close to the corresponding component. Specifically, in this embodiment, "opening direction away from the filling chamber 4" means that the inlet of the second one-way valve 10 is close to the filling chamber 4, and the waste liquid flowing through the second one-way valve 10 can only flow from the side closest to the filling chamber 4 to the side furthest from the filling chamber 4. In other embodiments, a solenoid valve can also be used as the second flow regulator. The corresponding function can be achieved by adjusting the valve opening degree of the solenoid valve. That is, the corresponding solenoid valve can control the opening and closing of the valve according to the liquid pressure on both sides of the valve body, achieving unidirectional flow performance along the filling 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, blood outside the perfusion chamber 4 can be prevented from entering the perfusion chamber 4 as much as possible, thereby reducing the risk of blood loss. Since the second preset value is less than 30 kPa, a large amount of waste fluid can be prevented from entering the patient's body due to excessive pressure on the distal side of the second flow regulating component. At the same time, excessive waste fluid pressure in the drainage line 2 can be prevented, thereby improving the working stability of the drainage line 2.

[0056] In some embodiments, the second preset value is greater than or equal to the patient's systolic blood pressure. That is, the patient's blood pressure alone cannot trigger the second flow regulation 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 regulating component is greater than a 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. That is, when the pressure on the distal side of the second flow regulating component is greater than the third preset value, the flow resistance of the waste liquid flowing through the second flow regulating component is relatively small, and the waste liquid in the infusion chamber 4 can be quickly discharged through the drainage pipe 2 and the second flow regulating component, thereby preventing a large amount of waste liquid from entering the patient's body.

[0058] Figure 4 This is a schematic diagram of the structure of a blood pumping catheter provided in some embodiments of this application.

[0059] like Figure 4As shown, in some embodiments, the second flow 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 two or more second ports. The first port is connected to the injection chamber 4 through a corresponding drain pipe 2, and the multiple second ports are respectively connected to the first port through corresponding flow channels. The first valve group includes one or more second check valves 10. One end of the second check valve 10 is connected to the return port 15 through a corresponding drain pipe 2, and the other end of the second check valve 10 is connected to a portion of the second ports one by one. Correspondingly, the opening direction of the second check valve 10 is opposite to that of the filling chamber 4; the second valve group includes one or more third check valves 11, one end of the third check valve 11 is connected to the return port 15 through a corresponding drain pipe 2, and the other end of the third check valve 11 is connected to another part of the second ports one by one, and the opening direction of the third check valve 11 is opposite to that of the filling 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 a 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 closed 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 closed state. It is understood that the first resistance value is the sum of the flow resistance 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 resistance 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, there are two second ports, and one second check valve 10 and one third check valve 11. The valve body structures included in the second flow regulating component are all relatively conventional, and the overall structure is simple.

[0060] like Figure 4 As shown, in some embodiments, the blood pumping catheter further includes a pressure sensor 13 installed in the drainage line. The pressure sensor 13 is located at the distal end of the second flow regulating component to accurately monitor the waste fluid pressure at the corresponding location. In some embodiments, the pressure sensor 13 feeds back the monitored waste fluid pressure to a multi-way regulating valve 12, which, based on the received waste fluid pressure, controls the first port to connect with the corresponding second port.

[0061] In some embodiments, the opening pressure of the second check valve 10 can be from 11 kPa to 30 kPa, and the opening pressure of the third check valve 11 can be from 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, factors such as blood pressure fluctuations can easily cause the periodic fluctuation range of the pressure on the distal side of the second flow regulating component to be greater than the aforementioned difference. Therefore, it is necessary to frequently adjust the internal structure of the second flow regulating component to make the second flow regulating component frequently switch between the first resistance value and the second resistance value, which will lead to 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 can prevent a large amount of waste fluid from flowing into the patient's body due to excessive waste fluid pressure in the perfusion chamber 4, and at the same time, it can avoid damage to the blood pumping catheter due to excessive waste fluid 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 area of ​​the first flow regulating component is smaller than the flow area of ​​the perfusion line 1. The flow area refers to the area of ​​the fluid flow cross section. In this embodiment, the flow area of ​​the perfusion line 1 refers to the area of ​​the perfusion fluid flowing through the perfusion line 1, and the flow area of ​​the first flow regulating component refers to the area of ​​the perfusion fluid flowing through the location of the first flow regulating component. When the difference between the proximal pressure and the distal pressure 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 perfusion fluid on the proximal side of the first flow regulating component can flow smoothly to the distal side of the first flow regulating component, thereby entering the perfusion chamber 4. However, due to factors such as fluctuations in the patient's blood pressure and elastic fluctuations in the elastic element, the blood may form turbulence or eddies. Similarly, there is a risk that blood may be gradually conducted through the perfusion line 1 to the perfusion device 49, resulting in blood loss. By limiting the flow area of ​​the first flow regulating component to be smaller than that of the perfusion line 1, the flow velocity of the perfusion fluid at the location of the first flow regulating component is relatively fast. Although the blood may form turbulence or eddies due to factors such as fluctuations in the patient's blood pressure and elastic fluctuations in the perfusion line 1, the risk of blood being conducted to the proximal side of the first flow regulating component can be reduced to a large extent because the flow area of ​​the first flow regulating component is relatively small and the flow velocity of the perfusion fluid at the location of the first flow regulating component is relatively fast, which can further reduce the patient's blood loss.

[0064] In some embodiments, the blood pumping catheter further includes a working device 6 and a power assembly. The working device 6 is used for insertion into the patient's body; the power assembly is connected to the working device 6 to drive the working device 6 to complete corresponding actions. Part of the power assembly is located within the perfusion chamber 4, or the perfusion chamber 4 is formed by a portion of the power assembly. Specifically, the working device 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 perfusion chamber 4 via a corresponding bearing, and the other end of the output shaft 5 is fixed to the impeller. In the external motor mode, the perfusion chamber 4 is formed by the perfusion chamber wall. The power assembly within the perfusion chamber 4 includes the end of the output shaft 5 away from the impeller, a bearing sleeved on the output shaft 5, and a transmission coil partially located inside the perfusion chamber 4. The power assembly also includes an external motor located outside the patient's body, wherein the end of the transmission coil located within the perfusion chamber 4 is connected to the transmission shaft, and the transmission coil... One end of the wire located outside the perfusion chamber 4 is connected to an external motor. The external motor can drive the impeller to rotate through the transmission wire and the transmission shaft. In the internal motor mode, the power component includes an internal motor for intervention in the patient's body. The internal motor has a housing, and the perfusion chamber 4 is formed by the housing of the internal motor. That is, the perfusion chamber 4 can be the internal space of the housing of the internal motor. The power component in the perfusion chamber 4 includes the end of the output shaft 5 away from the impeller, the 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 This is a schematic diagram of the internal structure of the infusion device 49 provided in some embodiments of this application.

[0066] like Figure 5 and Figure 6 As shown in the illustration, this application also provides a ventricular assist system, including the aforementioned blood pumping catheter and 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 an outlet 14 connected to the proximal end of the perfusion line 1 for injecting perfusion fluid into the perfusion line 1. The suction structure 51 has a return outlet 15 connected to the proximal end of the drainage line 2 for aspirating waste fluid from the drainage line 2. The linkage structure 52 connects the perfusion structure 50 and the suction structure 51, so that while the perfusion structure 50 injects perfusion fluid into the perfusion line 1, the suction structure 51 can aspirate waste fluid from the drainage line 2. By setting the linkage structure 52, the perfusion structure 50 and the suction structure 51 can operate synchronously, resulting in a high degree of synchronicity between the injection of perfusion fluid into the heat dissipation chamber and the discharge of waste fluid, thereby reducing the risk of waste fluid entering the patient's body and the patient's blood being discharged from the drainage line. 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 about by the above embodiments, which will not be repeated here.

[0067] like Figure 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 infusion structure 50 includes a first suction member and a second suction member, both of which can suction the infusion fluid to be infused and transport the suctioned infusion fluid to the outlet 14. The first suction member and the second suction member are connected through the first linkage member 21, so that while one of the first and second suction members is transporting the suctioned infusion fluid to the outlet 14, the other can suction the infusion fluid to be infused; the suction structure 51 includes a third suction member and a fourth suction member, both of which can suction the waste liquid in the drain pipe 2 through the return port 15 and discharge the suctioned waste liquid. The third suction member and the fourth suction member are connected through the second linkage member 48, so that while one of the third and fourth suction members is discharging the suctioned waste liquid, the other can suction the waste liquid in the drain pipe 2. It can achieve continuous perfusion of perfusion fluid and continuous aspiration of waste fluid, which can better maintain the continuity of perfusion fluid injection and waste fluid discharge, and reduce the risk of wear particles causing blockage of power components, wear particles entering the patient's body, or blood flowing out of the patient's body.

[0068] like Figure 6 As shown, in some embodiments, the infusion structure 50 further includes a first receiving member 16, a first pipeline assembly, a second pipeline assembly, a third pipeline assembly, and a fourth pipeline assembly. The first receiving member 16 has a first receiving cavity for receiving the infusion fluid to be infused. A first suction member and a second suction member are distributed along a first direction. The first suction member includes a first cylinder 18 and a first piston 20 slidably connected to the first cylinder 18. The first cylinder 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 receiving member 16 and the first suction member, so that the infusion fluid in the first receiving cavity flows into the first sub-cavity 19. The two ends of the second pipeline assembly are respectively connected to the first suction member and the outlet. The first sub-cavity 19 is connected to the outlet 14 to allow the infusion fluid in the first sub-cavity 19 to flow to the outlet 14. The second pumping component includes a second cylinder 24 and a second piston 22 slidably connected to the second cylinder 24. The second cylinder 24 and the second piston 22 enclose a second sub-cavity 23. The first piston 20 is located in the first sub-cavity 19 near the second sub-cavity 23, and the second piston 22 is located in the second sub-cavity 23 near the first sub-cavity 19. The two ends of the third pipeline assembly are respectively connected to the first receiving member 16 and the second pumping component to allow the infusion fluid in the first receiving cavity to flow to the second sub-cavity 23. The two ends of the fourth pipeline assembly are respectively connected to the second pumping component and the outlet 14 to allow the infusion fluid in the second sub-cavity 23 to flow to the outlet 14.

[0069] The drainage structure also includes a second receiving member 17, a fifth pipeline assembly, a sixth pipeline assembly, a seventh pipeline assembly, and an eighth pipeline assembly. The second receiving member 17 has a second receiving cavity for containing waste liquid. A third and fourth pumping member are distributed along a first direction. The third pumping member includes a third cylinder 26 and a third piston 28 slidably connected to the third cylinder 26. The third cylinder 26 and the third piston 28 enclose a third sub-cavity 27. The two ends of the sixth pipeline assembly are respectively connected to the third pumping member and the return port 15, so that waste liquid at the return port 15 flows to the third sub-cavity 27. The two ends of the fifth pipeline assembly are respectively connected to the second receiving member 17 and the third pumping member, so that waste liquid at the third... Waste liquid in sub-cavity 27 flows into second receiving cavity; the fourth pumping component includes a fourth cylinder 31 and a fourth piston 29 slidably connected to the fourth cylinder 31. The fourth cylinder 31 and the fourth piston 29 enclose a fourth sub-cavity 30. The third piston 28 is located in the third sub-cavity 27 near the fourth sub-cavity 30, and the fourth piston 29 is located in the fourth sub-cavity 30 near the third sub-cavity 27. The two ends of the eighth pipeline assembly are respectively connected to the fourth pumping component and the return port 15, so that the waste liquid at the return port 15 flows into the fourth sub-cavity 30. The two ends of the seventh pipeline assembly are respectively connected to the second receiving component 17 and the fourth pumping component, so that the waste liquid in the fourth sub-cavity 30 flows into the second receiving cavity.

[0070] The linkage structure 52 also includes a third linkage 25 connected to the first linkage 21 and the second linkage 48, so that the first linkage 21 and the second linkage 48 can move synchronously. The first linkage 21 can be a first gear shaft, the second linkage 48 can be a second gear shaft, and the third linkage 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 the second direction.

[0071] In some embodiments, the first direction and the second direction are perpendicular to the axial direction of the drive gear, that is, the first gear shaft and the second gear shaft can be arranged at the same height along the axial direction of the drive gear, thereby reducing the overall height of the linkage structure 52. When the drive gear rotates clockwise to move the first gear axially away from the first sub-cavity 19, the first piston 20 and the second piston 22 simultaneously slide away from the first sub-cavity 19, the volume in the first sub-cavity 19 increases and the volume in the second sub-cavity 23 decreases, the injection fluid in the first receiving cavity can flow to the first sub-cavity 19 through the first pipeline assembly, and the injection fluid in the second sub-cavity 23 can flow to the outlet 14 through the fourth pipeline assembly, so that the proximal side pressure of the first flow regulating component increases to the point that the difference between the proximal side pressure and the distal side pressure of the first flow regulating component is greater than or equal to the first preset value, the first flow regulating component is adjusted to the conducting state, and the injection fluid flowing out from the outlet 14 flows through the injection pipeline 1 through the elastic element. After the first flow regulating component, the fluid can flow smoothly into the injection chamber 4. After entering the injection chamber 4, the injection fluid mixes with the wear particles in the injection chamber 4 to form waste fluid 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 far 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 fluid in the injection chamber 4 flows through the drain pipe 2 and the second flow regulating component to the return port 15. The waste fluid at the return port 15 can flow to the fourth sub-chamber 30 through the eighth pipe assembly, and the waste fluid in the third sub-chamber 27 can flow to the second receiving chamber through the fifth pipe assembly.

[0072] As the drive gear rotates counterclockwise to move the first gear axially closer to the first sub-cavity 19, the first piston 20 and the second piston 22 simultaneously slide towards the first sub-cavity 19. The volume of the first sub-cavity 19 decreases while the volume of the second sub-cavity 23 increases. The infusion fluid in the first receiving cavity can flow to the second sub-cavity 23 through the third pipeline assembly, and the infusion fluid in the first sub-cavity 19 can flow to the outlet 14 through the second pipeline assembly. This increases the proximal pressure of the first flow regulating component until the difference between the proximal and distal pressures of the first flow regulating component is greater than or equal to a first preset value. The first flow regulating component is then switched to the conducting state, and the infusion fluid flowing from the outlet 14 flows through the infusion pipeline 1 and passes through the elastic element. After the first flow regulating component, the fluid can flow smoothly into the injection chamber 4. After entering the injection chamber 4, the injection fluid mixes with the wear particles in the injection chamber 4 to form waste fluid 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 far 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 fluid in the injection chamber 4 flows through the drain pipe 2 and the second flow regulating component to the return port 15. The waste fluid at the return port 15 can flow to the third sub-chamber 27 through the sixth pipe assembly, and the waste fluid in the fourth sub-chamber 30 can flow to the second receiving chamber through the seventh pipe assembly.

[0073] like Figure 5 As shown, in some embodiments, the first piping assembly includes a first pipe 32 and a first valve 33; the second piping assembly includes a second pipe 34 and a second valve 35; the third piping assembly includes a third pipe 36 and a third valve 37; and the fourth piping assembly includes a fourth pipe 39 and a fourth valve 38. The first valve 33 and the third valve 37 can be one-way valves with their opening direction opposite to the first receiving member 16, and the second valve 35 and the fourth valve 38 can be one-way valves with their opening direction towards the outlet 14. The fifth piping assembly includes a fifth pipe 40 and a fifth valve 41; the sixth piping assembly includes a sixth pipe 42 and a sixth valve 43; the seventh piping assembly includes a seventh pipe 44 and a seventh valve 45; and the eighth piping assembly includes an eighth pipe 46 and an eighth valve 47. The fifth valve 41 and the seventh valve 45 can be one-way valves with their opening direction towards the second receiving member 17, and the sixth valve 43 and the eighth valve 47 can be one-way valves with their opening direction opposite to the return port 15. By setting multiple one-way valves, backflow of injection fluid and waste fluid in the corresponding pipelines can be prevented. The structure is simple and easy to implement.

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

[0075] like Figure 5 As shown, in some embodiments, for the infusion structure 50, the first and second pipelines can be merged into one pipeline near the first sub-cavity 19 and then connected to the first sub-cavity 19; the third and fourth pipelines can be merged into one pipeline near the second sub-cavity 23 and then connected to the second sub-cavity 23; the first and third pipelines can be merged into one pipeline near the first receiving cavity and then connected to the first receiving cavity; and the second and fourth pipelines can be merged into one pipeline near the liquid outlet 14 and then connected to the liquid outlet 14. It is understood that a similar arrangement method can also be adopted for the suction structure 51 to simplify the pipeline structure of the infusion device 49.

[0076] The above description is merely a specific implementation of this application. Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the specific working processes of the systems, modules, and units described above can be referred to the corresponding processes in the foregoing method embodiments, and will not be repeated here. It should be understood that the protection scope of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and these modifications or substitutions should all be covered within the protection scope of this application.

Claims

1. A blood pumping catheter, characterized in that, include: A perfusion chamber is used for interventional procedures within the patient's body. An infusion line, the distal end of which is connected to the infusion chamber, and the proximal end of which is connected to the outlet of the infusion device; An elastic element is installed in the injection pipeline; A first flow regulating component is installed in the infusion pipeline and located between the elastic element and the infusion chamber. When the difference between the proximal pressure and the distal pressure of the first flow regulating component is greater than or equal to a first preset value, the first flow regulating component is in the conducting state, and the first preset value is greater than or equal to zero. When the difference between the proximal pressure and the distal pressure of the first flow regulating component is less than the first preset value, the first flow regulating component is in a cut-off state.

2. The blood pumping catheter according to claim 1, characterized in that, The elastic element includes: A first filtration component, the first filtration component having a first filter element, for filtering impurities and air bubbles entrained in the perfusion fluid flowing through the first filter element; and / or, A pressure storage component has a pressure storage chamber. During the process of increasing the pressure of the injection fluid at the installation position of the pressure storage component, the pressure storage chamber is used to draw in injection fluid from the injection pipeline and store pressure; during the process of decreasing the pressure of the injection fluid at the installation position of the pressure storage component, the pressure storage chamber is used to pressurize the injection pipeline and release pressure.

3. The blood pumping catheter according to claim 2, characterized in that, The elastic element includes the first filter element and the pressure storage element, with the pressure storage element located on the proximal side of the first filter element.

4. The blood pumping catheter according to claim 1 or 2, characterized in that, The blood pumping catheter also includes a second filtering component located at the distal end of the first flow regulating component. The second filtering component has a second filter element for filtering impurities and air bubbles mixed in with the perfusion fluid flowing through the second filter element.

5. The blood pumping catheter according to claim 1, characterized in that, The first flow regulating component includes a first check valve, the opening direction of which is toward the infusion chamber.

6. The blood pumping catheter according to claim 5, characterized in that, The first flow regulating component includes a first check valve, the opening direction of the first check valve being toward the infusion chamber, and the first check valve comprising: The valve body has an internal flow channel for the flow of injection fluid; The valve core is movably mounted 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 press against and seal against the inner wall of the internal flow channel or the end of the internal flow channel. The contact surface between the valve core and the internal flow channel is located in the same plane or the radius of the contact surface between the valve core and the internal flow channel gradually decreases from the distal side of the internal flow channel to the proximal side of the internal flow channel.

7. The blood pumping catheter according to claim 1, characterized in that, It also includes a drain line, the distal end of which is connected to the infusion chamber, and the proximal end of which is connected to the return port of the infusion device.

8. The blood pumping catheter according to claim 7, characterized in that, It also 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 the open state.

9. The blood pumping catheter according to claim 8, characterized in that, The second flow regulating component includes a second check valve, the opening direction of which is opposite to that of the infusion chamber.

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

11. The blood pumping catheter according to claim 8, characterized in that, When the pressure at the distal end 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 at the distal end 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, characterized in that, The second flow regulating component includes: A multi-port regulating valve includes a first port and two or more second ports. The first port is connected to the infusion chamber through a corresponding drain pipe, and the multiple second ports are respectively connected to the first port through corresponding flow channels. The first valve group includes one or more second check valves. One end of the second check valve is connected to the return port through a corresponding drain pipe. The other end of the second check valve is connected to a portion of the second ports in a one-to-one correspondence. The opening direction of the second check valve is opposite to the infusion chamber. The second valve assembly includes one or more third check valves. One end of each third check valve is connected to the return port via a corresponding drain pipe, and the other end of each third check valve is connected to another portion of the second ports. The opening direction of the third check valve is opposite to that of the infusion chamber, and the opening pressure of the second check valve is greater than that of the third check valve. When the pressure at the distal end 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 closed state; when the pressure at the distal end 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 closed state.

13. The blood pumping catheter according to claim 11, characterized in that, 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, characterized in that, The flow area of ​​the first flow regulating component is smaller than the flow area of ​​the injection pipeline; and / or, The blood pumping catheter also includes: Working instruments, used for interventional procedures within the patient's body; A power assembly is connected to the working instrument to drive the working instrument to complete corresponding actions. Part of the power assembly is located inside the infusion chamber, or the infusion chamber is formed by the enclosing of part of the power assembly.

15. A ventricular assist system, characterized in that, The blood pumping catheter included in any one of claims 1 to 14 further includes an infusion device, the infusion device comprising: The infusion structure has a liquid outlet connected to the proximal end of the infusion pipeline for pressurizing the infusion pipeline with infusion fluid. The suction structure has a return port, which is connected to the proximal end of the drain pipe and is used to suction the waste liquid in the drain pipe. A linkage structure is connected to the injection structure and the suction structure, so that while the injection structure injects injection fluid into the injection pipeline, the suction structure can suction waste liquid from the drainage pipeline.

16. The ventricular assist system according to claim 15, characterized in that, The linkage structure includes a first linkage component and a second linkage component capable of synchronous movement; The infusion structure includes a first suction component and a second suction component. Both the first and second suction components can draw up the infusion fluid to be infused and deliver the drawn-up infusion fluid to the outlet. The first and second suction components are connected by the first linkage component, so that while one of the first and second suction components is delivering the drawn-up infusion fluid to the outlet, the other can draw up the infusion fluid to be infused. The suction structure includes a third suction component and a fourth suction component. Both the third and fourth suction components can suction the waste liquid in the drain pipe through the return port and discharge the suctioned waste liquid. The third and fourth suction components are connected by the second linkage component, so that while one of the third and fourth suction components is discharging the suctioned waste liquid, the other can suction the waste liquid in the drain pipe.

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