Blood pumping catheter and ventricular assist system

Abstract

A blood pumping catheter and a ventricular assist system. The blood pumping catheter comprises a perfusion cavity (4), a perfusion tube (1), an elastic element, and a first flow regulating component. A distal end of the perfusion tube (1) is connected to the perfusion cavity (4). The elastic element and the first flow regulating component are both mounted on the perfusion tube (1). The first flow regulating component is located between the elastic element and the perfusion cavity (4). A first preset value is greater than or equal to zero, and when the difference between the pressure of a proximal side of the first flow regulating component and the pressure of a 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. Thus, the degree of blood loss in a patient can be reduced, and the risk of thrombus formation and resulting blockage in a perfusion apparatus (49) and the blood pumping catheter can be reduced, thereby relatively improving the operational stability and the service life of the perfusion apparatus (49) and the perfusion tube (1) on the proximal side of the blood pumping catheter.

Description

Blood pumping catheter and ventricular assist system

[0001] CROSS-REFERENCE

[0002] This application claims priority to Chinese Patent Application No. 202410835029.5, filed on June 25, 2024, entitled “Blood pumping catheter and ventricular assist system”, the entire contents of which are incorporated herein by reference. TECHNICAL FIELD

[0003] The present application relates to the technical field of medical devices, and in particular to a blood pumping catheter and a ventricular assist system. BACKGROUND

[0004] In some application scenarios, a ventricular assist system is an auxiliary system capable of pumping blood from a ventricle to other parts of the body, which is often used for patients with heart failure or heart failure, and can partially or completely replace the blood pumping function of the ventricle.

[0005] In the related art, the ventricular assist system generally includes a blood pumping catheter and a perfusion device, wherein the distal end of the blood pumping catheter is provided with a power assembly and an impeller, the power assembly is used to drive the impeller to rotate, so that the blood can flow in the pumping direction at an accelerated speed to increase the blood flow. The blood pumping catheter generally further includes a perfusion cavity and a perfusion pipeline connected to the perfusion cavity, the impeller is located outside the perfusion cavity, at least part of the power assembly is installed in the perfusion cavity, and the perfusion device is used to deliver perfusion liquid to the perfusion cavity through the perfusion pipeline to absorb heat generated by the power assembly during operation, thereby reducing the risk of patient discomfort caused by overheating of the power assembly.

[0006] At present, part of the perfusion pipeline is provided with an elastic element. During the change of the internal pressure of the perfusion pipeline at the position of the elastic element, the elastic element will have elastic fluctuations. For example, the blood pressure in the patient's body generally fluctuates periodically between diastolic pressure and systolic pressure. During each fluctuation of the patient's blood 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 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 is prone to flow to the perfusion device through the perfusion pipeline. During the periodic fluctuation of the blood pressure in the patient's body between diastolic pressure and systolic pressure, the blood in the patient's body is prone to gradually flow to the perfusion device through the perfusion pipeline due to the influence of the elastic fluctuations of the elastic element, which may further cause the loss of blood in the patient. SUMMARY

[0007] 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 to the proximal side of the first flow regulating component and the perfusion device along the perfusion pipeline, and can reduce the loss of blood in the patient.

[0008] In a first aspect, the embodiments of the present application provide a blood pumping catheter, which comprises: a perfusion cavity for being inserted into a patient; a perfusion pipeline, a distal end of the perfusion pipeline being connected to the perfusion cavity, and a proximal end of the perfusion pipeline being used for being connected to a liquid outlet of a perfusion device; an elastic element, which is installed on the perfusion pipeline; a first flow regulating component, which is installed on the perfusion pipeline and located between the elastic element and the perfusion cavity, the first flow regulating component being in a conducting state when a difference between a pressure on a proximal end side of the first flow regulating component and a pressure on a distal end side of the first flow regulating component is greater than or equal to a first preset value, and the first preset value being greater than or equal to zero, and the first flow regulating component being in a cut-off state when the difference between the pressure on the proximal end side of the first flow regulating component and the pressure on the distal end side of the first flow regulating component is less than the first preset value.

[0009] In some embodiments, the elastic element comprises: a first filtering component, which has a first filter core for filtering impurities and bubbles mixed in the perfusion liquid flowing through the first filter core; and / or a pressure storage component, which has a pressure storage cavity, the pressure storage cavity being used for sucking in the perfusion liquid from the perfusion pipeline and storing pressure during an increase of the perfusion liquid pressure at an installation position of the pressure storage component, and the pressure storage cavity being used for pressing the perfusion liquid into the perfusion pipeline and releasing pressure during a decrease of the perfusion liquid pressure at the installation position of the pressure storage component.

[0010] In some embodiments, the elastic element comprises the first filtering component and the pressure storage component, and the pressure storage component is located on a proximal end side of the first filtering component.

[0011] In some embodiments, the blood pumping catheter further comprises a second filtering component, which is located on a distal end side of the first flow regulating component, and the second filtering component has a second filter core for filtering impurities and bubbles mixed in the perfusion liquid flowing through the second filter core.

[0012] In some embodiments, the first flow regulating component comprises a first one-way valve, and an opening direction of the first one-way valve is toward the perfusion cavity.

[0013] In some embodiments, the first one-way valve comprises: a valve body, which has an internal flow channel for the flow of the perfusion liquid; and a valve core, which is movably installed on the internal flow channel, and the valve core is capable of abutting against and blocking an inner wall of the internal flow channel or an end portion of the internal flow channel when a difference between a pressure on a proximal end side of the internal flow channel and a pressure on a distal end side of the internal flow channel is less than an opening pressure of the first one-way valve, and a contact surface between the valve core and the internal flow channel is located in a same plane or gradually decreases in radius from the distal end side of the internal flow channel to the proximal end side of the internal flow channel.

[0014] In some embodiments, the blood pumping catheter further comprises a drainage pipeline, a distal end of the drainage pipeline being connected to the perfusion cavity, and a proximal end of the drainage pipeline being used for being connected to a liquid return port of the perfusion device.

[0015] In some embodiments, the blood pumping catheter further comprises a second flow regulating component installed on the liquid discharge pipeline, the second flow regulating component is in a closed state when the pressure on the distal side of the second flow regulating component is less than or equal to a second preset value, and the second flow regulating component is in an open state when the pressure on the distal side of the second flow regulating component is greater than the second preset value.

[0016] In some embodiments, the second flow regulating component comprises a second one-way valve, and the opening direction of the second one-way valve is away from the perfusion cavity.

[0017] 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 systolic pressure of the patient.

[0018] 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, and 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.

[0019] In some embodiments, the second flow regulating component comprises: a multi-port regulating valve comprising a first port and two or more second ports, the first port being connected to the perfusion cavity through a corresponding liquid discharge pipeline, and the plurality of second ports being respectively communicated with the first port through corresponding flow channels; a first valve group comprising one or more second one-way valves, one end of each second one-way valve being connected to the liquid return port through a corresponding liquid discharge pipeline, and the other end of each second one-way valve being connected to one of the second ports in one-to-one correspondence, and the opening direction of each second one-way valve being away from the perfusion cavity; and a second valve group comprising one or more third one-way valves, one end of each third one-way valve being connected to the liquid return port through a corresponding liquid discharge pipeline, and the other end of each third one-way valve being connected to another one of the second ports in one-to-one correspondence, and the opening direction of each third one-way valve being away from the perfusion cavity, the opening pressure of each second one-way valve being greater than the opening pressure of each 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 conductive state, and the second port corresponding to the third one-way valve is in a closed state, and 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 conductive state, and the second port corresponding to the second one-way valve is in a closed state.

[0020] In some embodiments, the difference between the third preset value and the second preset value is between 1 kPa and 20 kPa.

[0021] In some embodiments, the first flow regulating component has a smaller flow area than the perfusion pipeline; and / or, the blood pumping catheter further comprises: a working instrument for use in the patient; a power assembly connected to the working instrument to drive the working instrument to perform corresponding actions, part of the power assembly being located in the perfusion chamber or the perfusion chamber being enclosed by part of the power assembly.

[0022] In the second aspect, the embodiments of the present application provide a ventricular assist system, which comprises the above-mentioned blood pumping catheter and further comprises a perfusion device, the perfusion device comprising: 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; and a linkage structure connected to the perfusion structure and the suction structure to enable the perfusion structure to press perfusion liquid into the perfusion pipeline while the suction structure is able to suck waste liquid in the drainage pipeline.

[0023] In some embodiments, the linkage structure comprises first and second linkage members capable of synchronous movement; the perfusion structure comprises first and second pumping members, each of which is capable of sucking perfusion liquid to be perfused and delivering the sucked perfusion liquid to the liquid outlet, the first and second pumping members being connected by the first linkage member so that one of the first and second pumping members is capable of delivering the sucked perfusion liquid to the liquid outlet while the other is capable of sucking perfusion liquid to be perfused; and the suction structure comprises third and fourth pumping members, each of which is capable of sucking waste liquid in the drainage pipeline through the liquid return port and discharging the sucked waste liquid, the third and fourth pumping members being connected by the second linkage member so that one of the third and fourth pumping members is capable of discharging the sucked waste liquid while the other is capable of sucking waste liquid in the drainage pipeline.

[0024] The blood pumping catheter and the ventricular assist system provided by the embodiments of the present application, the blood pumping catheter comprising a perfusion chamber, a perfusion pipeline, an elastic element and a first flow regulating component, the distal end of the perfusion pipeline being connected to the perfusion chamber, the proximal end of the perfusion pipeline being used to connect to the liquid outlet of a perfusion device, the elastic element and the first flow regulating component being both installed on the perfusion pipeline, the first flow regulating component being located between the elastic element and the perfusion chamber, the first flow regulating component being in an open 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 a first preset value, the first preset value being greater than or equal to zero, the first flow regulating component being in a closed 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 less than the first preset value.

[0025] In a case that 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 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, and the first flow regulating component is adjusted to be in the on state, so that the perfusion fluid flowing out of the liquid outlet of the perfusion device can flow smoothly to the perfusion cavity through the perfusion pipeline, the elastic element and the first flow regulating component.

[0026] In the process that the blood of the patient fluctuates from the diastolic pressure to the systolic pressure each time, the blood pressure in the patient increases, and the increased pressure of the blood in the patient is transmitted to the distal side of the first flow regulating component through the perfusion cavity and the perfusion pipeline, which is likely to cause 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. In a case that 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 be in the off state, which can avoid the blood in the patient flowing to the perfusion device through the perfusion cavity and the perfusion pipeline 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.

[0027] Therefore, the present application can reduce the blood loss of the patient, reduce the risk of thrombosis and blockage in the perfusion device and the blood pumping catheter, thereby relatively improving the operation stability and operation life of the perfusion pipeline on the proximal side of the perfusion device and the blood pumping catheter. In addition, the perfusion fluid can play a heat dissipation role on the components in the perfusion cavity, thereby reducing the risk of patient discomfort caused by overheating of the components in the perfusion cavity, and can also flush away the wear particles generated during the operation of the components in the perfusion cavity, thereby avoiding excessive wear of the components in the perfusion cavity and playing a certain degree of lubrication on the components in the perfusion cavity. BRIEF DESCRIPTION OF DRAWINGS

[0028] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required to be used in the embodiments of the present application will be briefly introduced as follows, and other drawings can also be obtained by those of ordinary skill in the art without creative labor on the basis of these drawings.

[0029] FIG. 1 is a structural schematic diagram of a blood pumping catheter provided by some embodiments of the present application;

[0030] FIG. 2 is a structural schematic diagram of a blood pumping catheter provided by some other embodiments of the present application;

[0031] FIG. 3 is a structural schematic diagram of a blood pumping catheter provided by some other embodiments of the present application;

[0032] Fig. 4 is a schematic diagram of a blood pump catheter according to some embodiments of the present application;

[0033] Fig. 5 is a schematic diagram of a ventricular assist system according to some embodiments of the present application;

[0034] Fig. 6 is a schematic diagram of an internal structure of a perfusion device according to some embodiments of the present application. DETAILED DESCRIPTION

[0035] The features and exemplary embodiments of the various aspects of the present application will be described in detail below with reference to the drawings. The following detailed description is merely intended to explain the present application, and is not intended to limit the present application. The present application can be implemented without some of the specific details of the embodiments. The following description of the embodiments is merely provided to give a better understanding of the present application through showing examples of the present application.

[0036] It should be noted that the terms such as first and second, etc., are merely used 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. Also, the terms "include", "comprise" or any other variants thereof are intended to cover non-exclusive inclusion, so that a process, method, article or apparatus including a list of elements does not only include those elements, but also includes other elements not explicitly listed, or further includes elements inherent in such a process, method, article or apparatus. Without more limitations, the elements defined by the statement "comprise" do not exclude the presence of additional identical elements in the process, method, article or apparatus including the elements.

[0037] Currently, a ventricular assist system generally comprises a blood pumping catheter and a perfusion device, wherein a distal end of the blood pumping catheter is provided with a power assembly and an impeller, the power assembly comprises an output shaft, the impeller is connected to a part of the power assembly located in a 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 the blood can flow in the pumping direction at a high speed to increase the blood flow. The blood pumping catheter generally further comprises a perfusion cavity and a perfusion pipeline connected to 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. It can be understood that the blood pumping catheter in the present application can provide mechanical circulation support for medical catheters, which can promote blood flow through physical action. In some application scenarios, the blood pumping catheter can realize blood pumping to assist the heart to pump blood in the left ventricle into the aorta. In other application scenarios, the blood pumping catheter can also realize the pumping of blood and thrombus mixture, and then can cooperate with the filtering structure to realize the relative separation of thrombus and blood, that is, cooperate with other structures to realize thrombus aspiration. The above is only a part of examples of the application scenarios of the blood pumping catheter, other applications compatible with the principle of the blood pumping catheter are also within the protection scope of the present application, and the present application does not specifically limit this.

[0038] Specifically, for the in-vivo motor mode, the power assembly in the perfusion cavity comprises an output shaft away from one end of the impeller, a bearing sleeved on the output shaft, etc. For the in-vitro motor mode, the power assembly in the perfusion cavity comprises an output shaft away from one end of the impeller, a bearing sleeved on the output shaft, a transmission cable located inside the perfusion cavity, etc., wherein one end of the transmission cable located in the perfusion cavity is connected to the output shaft, and the other end of the transmission cable located outside the perfusion cavity is connected to the in-vitro motor. The output shaft extends from the perfusion cavity to the outside of the perfusion cavity, and the perfusion device is used to deliver perfusion liquid to the perfusion cavity through the perfusion pipeline to absorb the heat generated by the power assembly during operation, thereby reducing the risk of patient discomfort caused by overheating of the power assembly. Generally, the heat generated by the power assembly during operation is due to mechanical friction, for example, the corresponding bearing inner ring and bearing inner ring will generate heat due to friction between the bearing inner ring and the bearing inner ring and the bearing ball during operation of the bearing of the output shaft.

[0039] The elastic element is internally provided with an elastic structure, and in some application scenarios, the elastic element can play a specific function of filtering or pressure storage. It is found through research that the blood pressure in the patient's body generally fluctuates periodically between diastolic pressure and systolic pressure. During each fluctuation of the patient's blood 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 is transmitted to the elastic element through the perfusion cavity and the perfusion pipeline, causing the elastic element to contract, so that the blood in the patient's body is easily flowed to the perfusion device through the perfusion pipeline. During the periodic fluctuation of the blood pressure in the patient's body between diastolic pressure and systolic pressure, the blood in the patient's body is easily flowed to the perfusion device through the perfusion pipeline under the influence of the elastic fluctuation of the elastic element, which may further cause the blood loss of the patient.

[0040] To solve the above problems, the embodiment of the present application provides a pump blood catheter and a ventricular assist system. The following will be described in detail in combination with the drawings.

[0041] It can be known from combination of FIG. 1 and FIG. 5 that the embodiment of the present application provides a pump blood catheter, which comprises a perfusion cavity 4, a perfusion pipeline 1, an elastic element (not indicated) and a first flow regulating component (not indicated). The perfusion cavity 4 is used for being inserted into the 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 for being connected to the liquid outlet 14 of the perfusion device 49. The elastic element is installed in the perfusion pipeline 1. Specifically, the elastic element can be a functional element in the pump blood catheter which can realize a certain function, for example, a filtering component or a pressure storage component, which is internally provided with an elastic structure, and the elastic structure is located on the flow path of the perfusion pipeline 1. The first flow regulating component is installed in the perfusion pipeline 1 and located between the elastic element and the perfusion cavity 4. In the case that the difference between the pressure on the proximal end side of the first flow regulating component and the pressure on the distal end 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; in the case that the difference between the pressure on the proximal end side of the first flow regulating component and the pressure on the distal end 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.

[0042] It can be understood that in the present application, the proximal end refers to the end towards the operator or physician, and the distal end refers to the end away from the operator or physician. Among them, the proximal end side refers to the side close to the proximal end relative to a certain component, and the distal end side refers to the side close to the distal end relative to a certain component. For example, the proximal end side of the first flow regulating component refers to the side of the first flow regulating component connected to the liquid outlet 14, and the distal end side refers to the side of the first flow regulating component connected to the perfusion cavity 4. The proximal end side and the distal end side of other components are the same, and the subsequent application will not be repeated. Among them, the elastic element is located between the proximal end side of the first flow regulating component and the liquid outlet 14. The components having a medium flow space connected therein substantially mean that the internal medium flow spaces of the corresponding components are connected, and specifically, in the present embodiment, the two ends of the perfusion pipeline 1 are connected with the perfusion cavity 4 and the liquid outlet 14 of the perfusion device 49 respectively, which means that the flow channels inside the perfusion pipeline 1 are connected with the perfusion cavity 4 and the liquid outlet 14 respectively.

[0043] In addition, the difference between one pressure and another pressure in the present application refers to the value obtained by subtracting the value of the other pressure from the value of the pressure. For example, the difference between the proximal end side pressure of the first flow regulating component and the distal end side pressure of the first flow regulating component can be understood as the difference between the value of the proximal end side pressure of the first flow regulating component and the value of the distal end side pressure of the first flow regulating component. Based on this, in some application scenarios, the difference can be greater than 0, in other application scenarios, the difference can be equal to 0, and in other application scenarios, the difference can be less than 0.

[0044] In the case that the difference between the proximal end side pressure of the first flow regulating component and the distal end side pressure 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 at the proximal end side of the first flow regulating component is not less than the perfusion liquid pressure at the distal end side of the first flow regulating component, and the first flow regulating component is adjusted to the on state. The perfusion liquid flowing out of the liquid outlet 14 of the perfusion device 49 can flow smoothly to the perfusion cavity 4 through the perfusion pipeline 1, the elastic element and the first flow regulating component.

[0045] In the process of each fluctuation of the patient's blood pressure 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 is 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. In the case where 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 the closed state, which can avoid the blood in the patient's body flowing to the perfusion device 49 through the perfusion cavity 4 and the perfusion pipeline 1 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.

[0046] Therefore, the present application can reduce the blood loss of the patient, reduce the risk of thrombosis and blockage in the perfusion device 49 and the blood pumping 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 pumping catheter. In addition, the perfusion liquid can play a heat dissipation role on the components in the perfusion cavity 4, thereby reducing the risk of patient discomfort caused by overheating of the components in the perfusion cavity 4, and can also flush away the wear particles generated during the operation of the components in the perfusion cavity 4, improve the excessive wear of the components in the perfusion cavity 4, and play a certain degree of lubrication on the components in the perfusion cavity 4.

[0047] In some embodiments, the proximal end of the perfusion pipeline 1 can be detachably mounted to the liquid outlet 14 of the perfusion device 49. When the perfusion device 49 needs to be replaced due to damage or needs to be replaced due to the need to transfer the patient, medical staff can directly detach the proximal end of the perfusion pipeline 1 from the connected perfusion device 49 and re-mount it to the liquid outlet 14 of the next to be connected perfusion device 49, which is convenient to operate. Specifically, the proximal end of the perfusion pipeline 1 can be detachably mounted to the liquid outlet 14 of the perfusion device 49 through a luer joint. The structure of the luer joint is relatively mature, which is convenient to design and process or directly purchased, and the cost is relatively low.

[0048] As shown in FIG. 1, in some embodiments, the elastic element includes a first filtering component 9 having a first filter core for filtering impurities and bubbles mixed in the perfusion liquid flowing through the first filter core. The bubbles entering the patient's body can form air embolism. By providing a filtering component, the risk of patient discomfort caused by impurities and bubbles flowing into the patient's body can be reduced.

[0049] As shown in FIG. 1, in some embodiments, the elastic element comprises a pressure storage component 8, which has a pressure storage cavity. At least one cavity wall of the pressure storage cavity is elastic. During the process of increasing the perfusion liquid pressure at the installation position of the pressure storage component 8, the perfusion liquid pressure in the pressure storage cavity increases, the elastic cavity wall of the pressure storage cavity expands outward, the volume of the pressure storage cavity increases, so that the pressure storage cavity can suck in the perfusion liquid from the perfusion pipeline 1 and store pressure. During the process of reducing the perfusion liquid pressure at the installation position of the pressure storage component 8, the perfusion liquid pressure in the pressure storage cavity decreases, the elastic cavity wall of the pressure storage cavity contracts inward, the volume of the pressure storage cavity decreases, so that the pressure storage cavity can press the perfusion liquid into the perfusion pipeline 1 and release pressure.

[0050] It can be understood that the perfusion liquid pressure at the installation position of the pressure storage component 8 refers to the perfusion liquid pressure near the position of the pressure storage component 8 and in the perfusion pipeline 1. In the case of fluctuation of the perfusion liquid pressure output by the perfusion device 49, the pressure storage component 8 can play a role in peak clipping and valley filling for the pressure of the perfusion liquid in the perfusion pipeline 1, so that the perfusion liquid pressure in the perfusion pipeline 1 is relatively stable.

[0051] As shown in FIG. 1, in some embodiments, the elastic element comprises a first filter component 9 and a pressure storage component 8, and the pressure storage component 8 is located on the proximal side of the first filter component 9. The pressure storage component 8 is close to the perfusion device 49 and can quickly respond to and absorb the fluctuation of the perfusion liquid pressure caused by the operation of the perfusion device 49.

[0052] As shown in FIG. 2, in some embodiments, the blood pumping catheter further comprises a second filter component 7 located on the distal side of the first flow regulating component, and the second filter component 7 has a second filter core for filtering impurities and bubbles mixed in the perfusion liquid flowing through the second filter core. The second filter component 7 can maximize the filtering of the tiny bubbles generated by the first flow regulating component during the adjustment of the working state, thereby reducing the risk of corresponding bubbles entering the patient's body and causing discomfort to the patient.

[0053] As shown in FIG. 1, in some embodiments, the first flow regulating component comprises a first one-way valve 3, and the opening direction of the first one-way valve 3 is toward the perfusion cavity 4. The structure is simple and the cost is low. It should be noted that the opening direction of the one-way valve toward a certain component means that the outlet of the one-way valve is close to the corresponding component. Specifically, in this embodiment, the opening direction of the first one-way valve 3 toward the perfusion cavity 4 means that the outlet of the first one-way valve 3 is toward the perfusion cavity 4, and the perfusion liquid flowing through the first one-way valve 3 can only flow from the side away from the perfusion cavity 4 to the side close to the perfusion cavity 4.

[0054] In other embodiments, the first check valve 3 can also be replaced by an electromagnetic valve to achieve the corresponding functions by adjusting the valve opening degree 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 to achieve the performance of one-way conduction on the perfusion path.

[0055] In some embodiments, the opening pressure of the first check valve 3 is less than or equal to 30 kpa, and further, the opening pressure of the first check valve 3 can be between 1 kpa and 13 kpa. If the opening pressure of the first check valve 3 is too high, the perfusion device 49 needs to provide a higher perfusion liquid pressure to make the perfusion liquid flow to the perfusion cavity 4. Therefore, by limiting the opening pressure of the first check valve 3, the demand for the perfusion liquid 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.

[0056] It should be noted that the opening pressure of the check valve refers to the pressure difference between the inlet and the outlet when the valve is in a forward conduction state. That is, in the present embodiment, the opening pressure of the first check valve 3 is equal to the first preset value. When the pressure difference between the proximal side of the first check valve 3 and the distal side of the first check valve 3 is greater than the opening pressure of the first check valve 3, the first check valve 3 is opened, and the perfusion liquid can flow from the proximal side of the first check valve 3 to the distal side of the first check valve 3.

[0057] 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 perfusion liquid, and the valve core is movably installed in the internal flow channel. Specifically, the first check valve 3 further includes a reset member connected to the valve core, the reset member being used to provide a reset force to the valve core pointing to the proximal side of the first check valve 3, and the opening pressure of the first check valve 3 being equal to the sum of the friction force between the valve core and the valve body and the reset force. The reset member can be an elastic member, such as a coil spring, a leaf spring, or a diaphragm spring.

[0058] In the case that 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 greater than or equal to the opening pressure of the first one-way valve 3, the valve core has a spacing area with the internal flow channel for the perfusion liquid to flow. In the case that 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 3, the valve core can abut and block the inner wall of the internal flow channel 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 of the valve core and the internal flow channel is located in the same plane or the contact surface of the valve core and the internal flow channel gradually decreases in radius from the distal side of the internal flow channel to the proximal side of the internal flow channel. That is, the contact surface of the valve core and the internal flow channel does not have a step-like mutation, so that in the process of switching the first one-way valve 3 to the cut-off state or the conductive state, the contact position of the valve core and the internal flow channel is not easy to have bubbles, thereby reducing the risk of corresponding bubbles entering the patient's body and causing discomfort to the patient. It can be understood that the pressure on the proximal side of the internal flow channel is equal to the pressure on the proximal side of the first flow regulating component, and the pressure on the distal side of the internal flow channel is equal to the pressure on the distal side of the first flow regulating component.

[0059] In the related art, part of the power assembly in the perfusion cavity 4 rubs against each other during operation, which generates heat and also generates wear particles. After the perfusion liquid enters the perfusion cavity 4 through the perfusion pipeline 1, it exchanges heat with the components in the perfusion cavity 4 to achieve the purpose of cooling. After the perfusion liquid completes heat exchange and mixes with the wear particles, waste liquid is formed. At present, the waste liquid is generally discharged into the patient's body through the gap between the output shaft 5 and the cavity wall of the perfusion cavity 4, which is easy to cause discomfort to the patient. In addition, since the total amount of waste liquid that can be absorbed by the patient is limited, it is necessary to control the flow rate of the perfusion liquid 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 is easy to cause the heat dissipation effect of the perfusion cavity 4 to be unsatisfactory.

[0060] As shown in FIGS. 1-3, in some embodiments, the blood pumping catheter further comprises a liquid discharge pipeline 2, the distal end of the liquid discharge pipeline 2 is connected to the perfusion cavity 4, and the proximal end of the liquid discharge pipeline 2 is used to be connected to the liquid return port 15 of the perfusion device 49. Most of the waste liquid can be discharged to the liquid return port 15 of the perfusion device 49 through the liquid discharge pipeline 2, which can reduce the risk of causing discomfort to the patient due to a large amount of waste liquid entering the patient's body, and in addition, the heat dissipation effect of the perfusion cavity 4 can be improved by increasing the flow rate of the perfusion liquid in the perfusion pipeline 1.

[0061] In some embodiments, the proximal end of the drainage pipeline 2 is detachably installed at the liquid return port 15 of the perfusion device 49. When the perfusion device 49 needs to be replaced due to damage or transfer of the patient, the medical staff can directly detach the proximal end of the drainage pipeline 2 from the connected perfusion device 49 and reattach it to the liquid return port 15 of the next perfusion device 49 to be connected, which is convenient to operate. Specifically, the proximal end of the drainage pipeline 2 can be detachably installed at the liquid return port 15 of the perfusion device 49 through a luer joint. The luer joint has a relatively mature structure, which is convenient to design and process or directly purchased, and has a low cost.

[0062] As shown in FIG. 3, in some embodiments, the blood pumping conduit further comprises a second flow regulating component installed at the drainage pipeline 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.

[0063] When the pressure on the distal side of the second flow regulating component is less than or equal to the second preset value, the waste liquid in the perfusion cavity 4 has a relatively small pressure after the perfusion liquid flows into the perfusion cavity 4 and forms the waste liquid. The blood outside the perfusion cavity 4 is easy to enter the perfusion cavity 4. Adjusting the second flow regulating component to the closed state can improve the problem that the patient's blood flows to the perfusion device 49 through the drainage pipeline 2 and the second flow regulating component. When the pressure on the distal side of the second flow regulating component is greater than the second preset value, the waste liquid in the perfusion cavity 4 has a relatively large pressure after the perfusion liquid flows into the perfusion cavity 4 and forms the waste liquid. Thus, the blood in the patient's body can be largely blocked outside the perfusion cavity 4. That is, after the second flow regulating component is adjusted to the open state, the blood in the patient's body is not easy to enter the perfusion cavity 4, and the liquid flowing into the drainage pipeline 2 is basically waste liquid, which can relatively reduce the loss of the patient's blood.

[0064] As shown in FIG. 3, in some embodiments, the second flow regulating component comprises a second one-way valve 10. The opening direction of the second one-way valve 10 is away from the perfusion cavity 4, which has a simple structure and a low cost. It should be noted that the opening direction of the one-way valve away from a 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 away from the perfusion cavity 4 means that the inlet of the second one-way valve 10 is close to the perfusion cavity 4. 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.

[0065] In other embodiments, the second one-way valve 10 can also be replaced by an electromagnetic valve, and the corresponding functions can be realized by adjusting the opening of the valve of the 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, so as to realize the one-way conduction performance on the perfusion path.

[0066] In some embodiments, the second preset value is between 11 kPa and 30 kPa. Since the second preset value is greater than 11 kPa, the blood outside the perfusion cavity 4 can be minimized to enter the perfusion cavity 4, so as to reduce the risk of blood loss. Since the second preset value is less than 30 kPa, the risk of excessive pressure of the waste liquid in the drainage pipeline 2 can be reduced, and the working stability of the drainage pipeline 2 can be improved.

[0067] In some embodiments, the second preset value is greater than or equal to the systolic pressure of the patient. That is, the blood pressure of the patient cannot independently cause the second flow regulating component to open, which can greatly reduce the risk of blood loss.

[0068] 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. 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 perfusion cavity 4 can be quickly discharged through the drainage pipeline 2 and the second flow regulating component, thereby reducing the risk of a large amount of waste liquid entering the patient's body.

[0069] As shown in FIG. 4, 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 perfusion cavity 4 through a corresponding drainage pipeline 2. The plurality of second ports are respectively communicated with the first port through corresponding flow channels. The first valve group includes one or more second one-way valves 10. One end of the second one-way valve 10 is connected to the liquid return port 15 through a corresponding drainage pipeline 2, and the other end of the second one-way valve 10 is connected to a part of the second ports one by one. The opening direction of the second one-way valve 10 is away from the perfusion cavity 4.

[0070] The second valve group comprises one or more than one third one-way valve 11, one end of the third one-way valve 11 is connected to the liquid outlet 15 through the corresponding liquid discharge pipeline 2, and the other end of the third one-way valve 11 is connected to the other part of the second port one by one, and the opening direction of the third one-way valve 11 is opposite to the perfusion cavity 4. The opening pressure of the second one-way valve 10 is greater than the opening pressure of the third one-way 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.

[0071] 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 10 is in the on state, and the second port corresponding to the third one-way valve 11 is in the 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 11 is in the on state, and the second port corresponding to the second one-way valve 10 is in the off state.

[0072] It can be understood that the first resistance value is the sum of the flow resistance generated in the process that the waste liquid flows 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 in the process that the waste liquid flows through the multi-way regulating valve 12 and the first valve group. Specifically, in the embodiment, the number of the second ports is two, and the number of the second one-way valve 10 and the third one-way valve 11 is one. The valve body structure contained in the second flow regulating component is relatively conventional, and the overall structure is simple.

[0073] As shown in FIG. 4, in some embodiments, the blood pumping catheter further comprises a pressure sensor 13 installed on the liquid discharge pipeline 2, which is located on the distal side of the second flow regulating component, so as to accurately monitor the waste liquid pressure at the corresponding position, and can be fed back to the second flow regulating component. At least part of the components in the second flow regulating component adjusts its state based on the received waste liquid pressure, so that it is in the off state or in the on state.

[0074] Further, in combination with the foregoing embodiments, in some of the 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 first port and the corresponding second port to be in the on state based on the received waste liquid pressure.

[0075] In the embodiment, when the pressure sensor 13 detects that the pressure value is less than the third preset value, the second one-way valve 10 is opened, and the third one-way valve 11 is closed. At this time, the elastic fluctuation on the liquid discharge pipeline 2 can be improved by means of the second one-way valve 10, and the conduction of the elastic fluctuation to the blood flow is hindered. When the pressure sensor 13 detects that the pressure value is greater than the third preset value, the third one-way valve 11 is opened, and the second one-way valve 10 is closed. At this time, the waste liquid in the perfusion cavity 4 can be quickly discharged through the liquid discharge pipeline 2.

[0076] In some embodiments, the opening pressure of the second one-way valve 10 can be 11 kPa to 30 kPa, and the opening pressure of the third one-way valve 11 can be 1 kPa to 10 kPa.

[0077] 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, 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 due to factors such as blood pressure fluctuations. Therefore, the internal structure of the second flow regulating component needs to be frequently adjusted to frequently switch the second flow regulating component between the first resistance value and the second resistance value, which can cause poor system stability of the blood pumping catheter. Since the difference between the third preset value and the second preset value is at most 20 kPa, the problem of a large amount of waste liquid flowing into the patient's body due to excessive waste liquid pressure in the perfusion lumen 4 can be improved, and the risk of damage to the blood pumping catheter due to excessive waste liquid pressure on the distal side of the second flow regulating component can be reduced. Further, the difference between the third preset value and the second preset value is 13 kPa.

[0078] In some embodiments, the flow area of the first flow regulating component is less than the flow area of the perfusion line 1. The flow area refers to the area of the flow cross section. In the present embodiment, the flow area of the perfusion line 1 refers to the area of the flow cross section of the perfusion liquid flowing through the perfusion line 1, and the flow area of the first flow regulating component refers to the area of the flow cross section of the perfusion liquid flowing through the position of the first flow regulating component.

[0079] 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, the first flow regulating component is in a conductive state, and the perfusion liquid 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 lumen 4. However, due to factors such as blood pressure fluctuations of the patient and elastic fluctuations of the elastic element, blood can form turbulent flow or vortex flow, and there is also a risk that blood gradually conducts through the perfusion line 1 to the perfusion device 49, resulting in blood loss.

[0080] By limiting the flow area of the first flow regulating component to be less than the flow area of the perfusion line 1, the flow rate of the perfusion liquid at the position of the first flow regulating component is relatively fast. Due to factors such as blood pressure fluctuations of the patient and elastic fluctuations of the perfusion line 1, blood can form turbulent flow or vortex flow, but since the flow area of the first flow regulating component is relatively small and the flow rate of the perfusion liquid at the position of the first flow regulating component is relatively fast, the risk of blood conducting to the proximal side of the first flow regulating component can be greatly reduced, and blood loss of the patient can be further reduced.

[0081] In some embodiments, the blood-pumping catheter further comprises a working instrument 6 for interventional use in the patient's body and a power assembly connected to the working instrument 6 to drive the working instrument 6 to perform corresponding actions, part of the power assembly being located in the perfusion cavity 4 or the perfusion cavity 4 being enclosed by part of the power assembly.

[0082] 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 being rotatably connected to the perfusion cavity 4 through a corresponding bearing, and the other end of the output shaft 5 being fixedly connected to the impeller. For the extracorporeal motor mode, the perfusion cavity 4 is enclosed by a perfusion cavity wall, and the power assembly in the perfusion cavity 4 includes the end of the output shaft 5 away from the impeller, a bearing sleeved on the output shaft 5, a transmission cable located partially inside the perfusion cavity 4, and the like. The power assembly further includes an extracorporeal motor located outside the patient's body. Here, one end of the transmission cable located inside the perfusion cavity 4 is connected to a transmission shaft, and the other end of the transmission cable located outside the perfusion cavity 4 is connected to the extracorporeal motor. The extracorporeal motor can drive the impeller to rotate through the transmission cable and the transmission shaft.

[0083] For the intracorporeal motor mode, the power assembly includes an intracorporeal motor for interventional use in the patient's body, the intracorporeal motor having a housing, and the perfusion cavity 4 being enclosed by the housing of the intracorporeal motor, that is, the perfusion cavity 4 can be the internal space of the housing of the intracorporeal motor. Specifically, the power assembly in the perfusion cavity 4 includes a rotor assembly and a stator assembly. The rotor assembly includes a magnetic steel and an output shaft 5, the magnetic steel being sleeved on the output shaft 5 and rotating synchronously with the output shaft 5, and the intracorporeal motor being able to drive the impeller to rotate through the output shaft 5. The stator assembly includes an iron core and a winding, the winding being fixed in the housing through the iron core.

[0084] The stator assembly and the magnetic steel in the rotor assembly form a gap space in the housing, and the perfusion pipeline 1 and the drainage pipeline 2 are both in communication with the gap space. The perfusion fluid in the perfusion device 49 passes through the perfusion pipeline 1, the gap space, and the drainage pipeline 2 to exit the intracorporeal motor in this way. This design reduces the possibility of thrombosis by transporting perfusion fluid into the gap space and making it difficult for ventricular blood to enter the internal space of the housing with the help of perfusion pressure, thereby improving the problems of intracorporeal motor overheating and stalling caused by thrombosis.

[0085] In addition, in addition to the stator assembly and the rotor assembly, the power assembly in the perfusion cavity 4 further includes the bearing sleeved on the output shaft 5 away from the impeller and other intracorporeal motor components in the housing. On this basis, the perfusion fluid entering the gap space can also flow to the bearing and flush it, thereby carrying away the particles and heat generated during the operation of the intracorporeal motor. It should be noted that the first flow regulating assembly can also have a similar structure to the second flow regulating assembly described above, that is, the first flow regulating assembly can also include multiple one-way valves with different opening pressures, and the embodiments of the present application do not limit this.

[0086] As shown in FIG. 3, the embodiment of the present application further provides a blood pumping catheter, which comprises a perfusion cavity 4, a drainage pipeline 2, and a second flow regulating component. The perfusion cavity 4 is used for interventional treatment of a patient. A proximal end of the drainage pipeline 2 is connected to a liquid return port 15 of a perfusion device 49, and the second flow regulating component is installed on the drainage pipeline 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.

[0087] When the pressure on the distal side of the second flow regulating component is less than or equal to the second preset value, the perfusion liquid flows into the perfusion cavity 4 and forms waste liquid, and the pressure of the waste liquid in the perfusion cavity 4 is relatively small, so that the blood outside the perfusion cavity 4 is easy to enter the perfusion cavity 4. Adjusting the second flow regulating component to the closed state can improve the problem that the blood of the patient flows to the perfusion device 49 through the drainage pipeline 2 and the second flow regulating component. When the pressure on the distal side of the second flow regulating component is greater than the second preset value, the perfusion liquid flows into the perfusion cavity 4 and forms waste liquid, and the pressure of the waste liquid in the perfusion cavity 4 is relatively large, so that the blood in the patient can be blocked outside the perfusion cavity 4 to a large extent. That is, after the second flow regulating component is adjusted to the open state, the blood in the patient is not easy to enter the perfusion cavity 4, and the liquid flowing into the drainage pipeline 2 is basically waste liquid, so that the blood loss of the patient can be relatively reduced.

[0088] As shown in FIG. 3, in some embodiments, the second flow regulating component comprises a second one-way valve 10, and the opening direction of the second one-way valve 10 is away from the perfusion cavity 4. The structure is simple, and the cost is low. It should be noted that the opening direction of the one-way valve away from a component means that the inlet of the one-way valve is close to the corresponding component. Specifically, in the embodiment, the opening direction of the second one-way valve 10 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.

[0089] In other embodiments, an electromagnetic valve can be used to replace the second one-way valve 10, and the corresponding functions can be realized by adjusting the opening degree of the valve 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, so as to realize the performance of one-way conduction on the perfusion path.

[0090] As shown in FIGS. 5 and 6, the application also provides a ventricular assist system, which comprises the blood pumping catheter described above, and further comprises a perfusion device 49, the perfusion device 49 comprising a perfusion structure 50, a suction structure 51 and a linkage structure 52, the perfusion structure 50 having a liquid outlet 14 connected to a proximal end of the perfusion pipeline 1 for pressing perfusion liquid into the perfusion pipeline 1, the suction structure 51 having a liquid return port 15 connected to a proximal end of the drainage pipeline 2 for sucking waste liquid in the drainage pipeline 2, and the linkage structure 52 connected to the perfusion structure 50 and the suction structure 51 to enable the perfusion structure 50 to suck waste liquid in the drainage pipeline 2 while the perfusion structure 50 is pressing perfusion liquid into the perfusion pipeline 1.

[0091] The linkage structure 52 is provided in the application to ensure that the perfusion structure 50 and the suction structure 51 operate synchronously, so that the injection of perfusion liquid and the discharge of waste liquid in the heat dissipation cavity have high synchronism, thereby reducing the risk of waste liquid entering the patient's body and the patient's blood flowing out of the drainage pipeline. In addition, since the ventricular assist system comprises the blood pumping catheter in the above embodiment, it has at least all the beneficial effects brought by the above embodiment, which will not be described here.

[0092] As shown in FIG. 6, in some embodiments, the linkage structure 52 comprises a first linkage member 21 and a second linkage member 48 capable of synchronous movement. The perfusion structure 50 comprises a first suction member and a second suction member, both of which are capable of sucking perfusion liquid to be perfused and delivering the sucked perfusion liquid to the liquid outlet 14, and the first suction member and the second suction member are connected by the first linkage member 21, so that one of the first suction member and the second suction member can deliver the sucked perfusion liquid to the liquid outlet 14 while the other one can suck perfusion liquid to be perfused.

[0093] The suction structure 51 comprises a third suction member and a fourth suction member, both of which are capable of sucking waste liquid in the drainage pipeline 2 through the liquid return port 15 and discharging the sucked waste liquid, and the third suction member and the fourth suction member are connected by the second linkage member 48, so that one of the third suction member and the fourth suction member can discharge the sucked waste liquid while the other one can suck waste liquid in the drainage pipeline 2.

[0094] The above embodiment can realize continuous perfusion of perfusion liquid and continuous suction of waste liquid, better maintain the continuity of injection of perfusion liquid and discharge of waste liquid, and reduce the risk of obstruction of the power assembly by wear particles, entry of wear particles into the patient's body, or flow of blood to the outside of the patient's body.

[0095] As shown in FIG. 6, in some embodiments, the perfusion structure 50 further comprises a first containing member 16, a first pipeline assembly, a second pipeline assembly, a third pipeline assembly and a fourth pipeline assembly. The first containing member 16 has a first containing cavity for containing perfusion liquid to be perfused. The first and second pumping members are distributed along the first direction. The first pumping member comprises a first cylinder 18 and a first piston 20 slidingly connected to the first cylinder 18. The first cylinder 18 and the first piston 20 enclose a first sub-cavity 19. Two ends of the first pipeline assembly are connected to the first containing member 16 and the first pumping member respectively, so that the perfusion liquid in the first containing cavity flows into the first sub-cavity 19.

[0096] The second pumping member comprises a second cylinder 24 and a second piston 22 slidingly 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 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. Two ends of the third pipeline assembly are connected to the first containing member 16 and the second pumping member respectively, so that the perfusion liquid in the first containing cavity flows into the second sub-cavity 23. Two ends of the fourth pipeline assembly are connected to the second pumping member and the liquid outlet 14 respectively, so that the perfusion liquid in the second sub-cavity 23 flows into the liquid outlet 14.

[0097] The liquid discharging structure further comprises a second containing member 17, a fifth pipeline assembly, a sixth pipeline assembly, a seventh pipeline assembly and an eighth pipeline assembly. The second containing member 17 has a second containing cavity for containing waste liquid. The third and fourth pumping members are distributed along the first direction. The third pumping member comprises a third cylinder 26 and a third piston 28 slidingly connected to the third cylinder 26. The third cylinder 26 and the third piston 28 enclose a third sub-cavity 27.

[0098] The sixth pipeline assembly is connected to the third pumping member and the liquid return port 15 at two ends, so that the waste liquid at the position of the liquid return port 15 flows to the third sub-cavity 27. The fifth pipeline assembly is connected to the second containing member 17 and the third pumping member at two ends, so that the waste liquid in the third sub-cavity 27 flows to the second containing cavity. The fourth pumping member includes a fourth cylinder 31 and a fourth piston 29 slidingly connected to the fourth cylinder 31, and the fourth cylinder 31 and the fourth piston 29 form a fourth sub-cavity 30. 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 eighth pipeline assembly is connected to the fourth pumping member and the liquid return port 15 at two ends, so that the waste liquid at the position of the liquid return port 15 flows to the fourth sub-cavity 30. The seventh pipeline assembly is connected to the second containing member 17 and the fourth pumping member at two ends, so that the waste liquid in the fourth sub-cavity 30 flows to the second containing cavity.

[0099] 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. 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 meshing with the first gear shaft and the second gear shaft. The two ends of the first gear shaft are fixedly connected to the first piston 20 and the second piston 22, respectively. The two ends of the second gear shaft are fixedly connected to the third piston 28 and the fourth piston 29, respectively. The first gear shaft and the second gear shaft are located on the two sides of the driving gear along the second direction, and the first direction intersects the second direction.

[0100] In some embodiments, the first direction, the second direction and the axis direction of the driving gear are perpendicular to each other, that is, the first gear shaft and the second gear shaft can be arranged at the same height along the axis direction of the driving gear, thereby reducing the overall height of the linkage structure 52. When the driving gear rotates in the clockwise direction to move the first gear shaft 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 of the first sub-cavity 19 increases and the volume of the second sub-cavity 23 decreases. The perfusion liquid in the first containing cavity can flow to the first sub-cavity 19 through the first pipeline assembly, and the perfusion liquid in the second sub-cavity 23 can flow to the liquid outlet 14 through the fourth pipeline assembly. 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 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 smoothly flow to the perfusion cavity 4 through the perfusion pipeline 1, the elastic element and the first flow regulating component. After the perfusion liquid enters the perfusion cavity 4, it mixes with the abrasive particles in the perfusion cavity 4 to form waste liquid with a certain pressure.

[0101] Meanwhile, the second gear shaft, the third piston 28 and the fourth piston 29 slide towards the third sub-cavity 27, the volume of the third sub-cavity 27 decreases and the volume of the fourth sub-cavity 30 increases, in the case that the distal side pressure of the second flow regulating component is greater than the second preset value, the second flow regulating component is in an open state, the waste liquid in the perfusion cavity 4 flows through the second flow regulating component via the liquid discharge pipeline 2 and reaches the liquid return port 15, the waste liquid at the position of the liquid return port 15 can flow to the fourth sub-cavity 30 via the eighth pipeline assembly, and the waste liquid in the third sub-cavity 27 can flow to the second containing cavity via the fifth pipeline assembly.

[0102] When the driving gear rotates in the counterclockwise direction to move the first gear shaft towards 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 and the volume of the second sub-cavity 23 increases, the perfusion liquid in the first containing cavity can flow to the second sub-cavity 23 via the third pipeline assembly, and the perfusion liquid in the first sub-cavity 19 can flow to the liquid outlet 14 via the second pipeline assembly, so that the proximal side pressure of the first flow regulating component increases to the difference between the proximal side pressure of the first flow regulating component and the distal side pressure of the first flow regulating component being greater than or equal to the first preset value, and the first flow regulating component is adjusted to a conducting state. The perfusion liquid flowing out of the liquid outlet 14 can smoothly flow to the perfusion cavity 4 via the perfusion pipeline 1, the elastic element and the first flow regulating component, and the perfusion liquid mixed with the wear particles in the perfusion cavity 4 forms waste liquid with a certain pressure.

[0103] Meanwhile, the second gear shaft, the third piston 28 and the fourth piston 29 slide towards the third sub-cavity 27, the volume of the third sub-cavity 27 decreases and the volume of the fourth sub-cavity 30 increases, in the case that the distal side pressure of the second flow regulating component is greater than the second preset value, the second flow regulating component is in an open state, the waste liquid in the perfusion cavity 4 flows through the second flow regulating component via the liquid discharge pipeline 2 and reaches the liquid return port 15, the waste liquid at the position of the liquid return port 15 can flow to the fourth sub-cavity 30 via the eighth pipeline assembly, and the waste liquid in the third sub-cavity 27 can flow to the second containing cavity via the fifth pipeline assembly.

[0104] As shown in FIG. 5, 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 opening direction away from the first containing member 16, and the second valve 35 and the fourth valve 38 can be one-way valves with opening direction towards the liquid outlet 14.

[0105] 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. The fifth valve 41 and the seventh valve 45 can be one-way valves with an opening direction towards the second containing member 17, and the sixth valve 43 and the eighth valve 47 can be one-way valves with an opening direction away from the liquid outlet 15. The use of multiple one-way valves can improve the problem of backflow of perfusion liquid and waste liquid in the corresponding pipelines, and the structure is simple and easy to implement.

[0106] In some embodiments, the opening pressure of the one-way valve included in the perfusion device 49 can be 1 kPa to 10 kPa.

[0107] As shown in FIG. 5, in some embodiments, for the perfusion structure 50, the first pipeline and the second pipeline can be merged into one pipeline near the first sub-cavity 19 and then communicated to the first sub-cavity 19, the third pipeline and the fourth pipeline can be merged into one pipeline near the second sub-cavity 23 and then communicated to the second sub-cavity 23, the first pipeline and the third pipeline can be merged into one pipeline near the first containing cavity and then communicated to the first containing cavity, and the second pipeline and the fourth pipeline can be merged into one pipeline near the liquid outlet 14 and then communicated to the liquid outlet 14. It can be understood that, for the suction structure 51, a similar arrangement method can also be used to simplify the pipeline structure of the perfusion device 49.

[0108] It can be understood that the perfusion device 49 described above is only a part of an example, and does not constitute a limitation on the corresponding structure of the perfusion device 49. Depending on different actual needs, the perfusion device 49 can also use other structure forms, and the specific structure form of the perfusion device 49 is not limited in the embodiments of the present application.

[0109] The above describes only specific implementation manners of the present application, and those skilled in the art can clearly understand that, for the convenience and brevity of description, the specific working processes of the above-described system, modules and units can refer to the corresponding processes in the foregoing method embodiments, which will not be described herein. It should be understood that the protection scope of the present application is not limited thereto, and any person skilled in the art can easily think of various equivalent modifications or replacements within the technical range disclosed in the present application, and these modifications or replacements should be covered within the protection scope of the present application.

Claims

1. A pump blood conduit, comprising: a perfusion chamber for being inserted into a patient's body; a perfusion line, a distal end of the perfusion line being connected to the perfusion chamber, a proximal end of the perfusion line being used for being connected to a liquid outlet of a perfusion device; a resilient element installed on the perfusion line; a first flow regulating component installed on the perfusion line and located between the resilient element and the perfusion chamber; the first flow regulating component is in an open state when a difference between a pressure on a proximal end side of the first flow regulating component and a pressure on a distal end side of the first flow regulating component is greater than or equal to a first preset value, the first preset value being greater than or equal to zero; the first flow regulating component is in a closed state when the difference between the pressure on the proximal end side of the first flow regulating component and the pressure on the distal end side of the first flow regulating component is less than the first preset value.

2. The blood pump catheter of claim 1, wherein, the resilient element comprises: a first filter component, the first filter component having a first filter core for filtering impurities and air bubbles mixed in perfusion liquid flowing through the first filter core; and / or a pressure storage component, the pressure storage component having a pressure storage chamber, the pressure storage chamber being used for sucking in perfusion liquid from the perfusion line and storing pressure during an increase of perfusion liquid pressure at a position where the pressure storage component is installed, the pressure storage chamber being used for pressing perfusion liquid into the perfusion line and releasing pressure during a decrease of perfusion liquid pressure at the position where the pressure storage component is installed.

3. The blood pump catheter of claim 2, wherein, the resilient element comprises the first filter component and the pressure storage component, the pressure storage component being located on a proximal end side of the first filter component.

4. The blood pump catheter of claim 1 or 2, wherein, the pump blood conduit further comprises a second filter component located on a distal end side of the first flow regulating component, the second filter component having a second filter core for filtering impurities and air bubbles mixed in perfusion liquid flowing through the second filter core.

5. The blood pump catheter of claim 1, wherein, the first flow regulating component comprises a first one-way valve, an opening direction of the first one-way valve being toward the perfusion chamber.

6. The blood pump catheter of claim 5, wherein, the first flow regulating component comprises a first one-way valve, an opening direction of the first one-way valve being toward the perfusion chamber, the first one-way valve comprising: a valve body having an internal flow passage for the flow of perfusion liquid; a valve core being movably installed on the internal flow passage; the valve core is capable of abutting against and blocking an inner wall of the internal flow passage or an end portion of the internal flow passage when a difference between a pressure on a proximal end side of the internal flow passage and a pressure on a distal end side of the internal flow passage is less than an opening pressure of the first one-way valve, a contact surface of the valve core with the internal flow passage being located in a same plane or gradually decreasing in radius from the distal end side of the internal flow passage to the proximal end side of the internal flow passage.

7. The pump blood conduit according to claim 1, further comprising a drainage line, a distal end of the drainage line being connected to the perfusion chamber, a proximal end of the drainage line being used for being connected to a liquid return port of the perfusion device.

8. The blood pump catheter of claim 7, further comprising a second flow regulating component installed on the liquid discharge line, the second flow regulating component being in a closed state when a pressure on a distal side of the second flow regulating component is less than or equal to a second preset value, and the second flow regulating component being in an open state when the pressure on the distal side of the second flow regulating component is greater than the second preset value.

9. The pump blood conduit of claim 8, wherein, The second flow regulating component comprises a second one-way valve, an opening direction of the second one-way valve being opposite to the perfusion cavity.

10. The blood pump catheter of claim 8, wherein, The second preset value is between 11 kPa and 30 kPa, or the second preset value is greater than or equal to a systolic pressure of the patient.

11. The pump blood conduit of claim 8, wherein, 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, a 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.

12. The blood pump catheter of claim 11, wherein, The second flow regulating component comprises: a multi-port regulating valve comprising a first port and two or more second ports, the first port being connected to the perfusion cavity through a corresponding liquid discharge line, and the plurality of second ports being respectively communicated with the first port through corresponding flow passages; a first valve group comprising one or more second one-way valves, one end of each second one-way valve being connected to the liquid return port through a corresponding liquid discharge line, and the other end of each second one-way valve being connected to a corresponding one of the second ports, an opening direction of each second one-way valve being opposite to the perfusion cavity; a second valve group comprising one or more third one-way valves, one end of each third one-way valve being connected to the liquid return port through a corresponding liquid discharge line, and the other end of each third one-way valve being connected to a corresponding one of the second ports, an opening direction of each third one-way valve being opposite to the perfusion cavity, and an opening pressure of each second one-way valve being greater than an opening pressure of each third one-way valve, when the pressure on the distal side of the first port is less than the third preset value, the second ports corresponding to the second one-way valves are in a conductive state, and the second ports corresponding to the third one-way valves are in a closed state; and when the pressure on the distal side of the first port is greater than or equal to the third preset value, the second ports corresponding to the third one-way valves are in the conductive state, and the second ports corresponding to the second one-way valves are in the closed state.

13. The blood pump catheter of claim 11, wherein, A difference between the third preset value and the second preset value is between 1 kPa and 20 kPa.

14. The blood pump catheter of claim 1, wherein, An over-flow area of the first flow regulating component is less than an over-flow area of the perfusion line. and / or, The blood pump catheter further comprises: a working instrument for interventional operation on a patient; a power assembly connected to the working instrument to drive the working instrument to complete a corresponding action, part of the power assembly being located in the perfusion cavity, or the perfusion cavity being enclosed by part of the power assembly.

15. A ventricular assist system comprising the blood pumping catheter of any one of claims 1 to 14, further comprising a perfusion device, the perfusion device comprising: a perfusion structure having a liquid outlet connected to a proximal end of the perfusion conduit for pressing perfusion liquid into the perfusion conduit; a suction structure having a liquid return outlet connected to a proximal end of the liquid discharge conduit for suctioning waste liquid in the liquid discharge conduit; a linkage structure connected to the perfusion structure and the suction structure to enable the perfusion structure to press perfusion liquid into the perfusion conduit while the suction structure is able to suction waste liquid in the liquid discharge conduit.

16. The ventricular assist system of claim 15, wherein, the linkage structure comprises a first linkage member and a second linkage member capable of synchronous movement; the perfusion structure comprises a first suction member and a second suction member, each capable of suctioning perfusion liquid to be perfused and delivering the suctioned perfusion liquid to the liquid outlet, the first suction member and the second suction member are connected by the first linkage member such that one of the first suction member and the second suction member is capable of delivering the suctioned perfusion liquid to the liquid outlet while the other is capable of suctioning perfusion liquid to be perfused; the suction structure comprises a third suction member and a fourth suction member, each capable of suctioning waste liquid in the liquid discharge conduit through the liquid return outlet and discharging the suctioned waste liquid, the third suction member and the fourth suction member are connected by the second linkage member such that one of the third suction member and the fourth suction member is capable of discharging the suctioned waste liquid while the other is capable of suctioning waste liquid in the liquid discharge conduit.

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