Ventricular Assist Interventional System

Abstract

This application provides a ventricular assist interventional system, relating to the field of medical device technology, comprising a diaphragm pump, a first catheter, a balloon, and a pneumatic actuator. A balloon for implantation into the descending aorta to assist the heart is disposed on the surface between a bidirectional valve on the first catheter and the proximal end of the first catheter. The distal end of the first catheter is inserted into the ventricle. The balloon is connected to the pneumatic actuator via an air circuit. The proximal end of the first catheter is connected to the blood chamber of the diaphragm pump, and the medium chamber of the diaphragm pump is connected to the pneumatic actuator via an air circuit. A single pneumatic actuator simultaneously drives the diaphragm pump to aspirate or pump blood and to inflate or deflate the balloon. The inflation and deflation cycle of the balloon is synchronized with the diaphragm pumping action, thereby precisely corresponding to the systolic and diastolic phases of the heart. This reduces the number of components used in the ventricular assist interventional system and improves the technical problem of existing ventricular assist interventional systems being bulky and easily increasing the burden on patients.

Description

Technical Field

[0001] This application relates to the field of medical device technology, specifically to ventricular assist interventional systems. Background Technology

[0002] A ventricular assist system is a medical device system used to assist cardiac function, primarily for the treatment of heart diseases such as heart failure.

[0003] Current ventricular assist interventional systems mainly include: percutaneous ventricular assist devices (PVADs) and intra-aortic balloon pumps (IABPs). PVADs are typically inserted percutaneously through the skin (femoral artery, etc.) and then connected to the heart to assist or take over the heart's pumping function, increasing blood flow, enhancing blood perfusion, and reducing myocardial oxygen consumption. In the short term, this helps reduce ventricular load in high-risk patients undergoing percutaneous coronary intervention (PCI) and those with cardiogenic shock. The basic principle of IABP is to insert a catheter with a balloon into the descending aorta, distal to the opening of the left subclavian artery and above the opening of the renal artery. During diastole, the balloon inflates; before systole, the balloon deflates, improving hemodynamics and thus assisting the heart's pumping function.

[0004] Both of the above devices can assist cardiac function, and their working principles do not conflict. Therefore, a system combining PVAD and IABP has emerged. However, in related technologies, the system that combines PVAD and IABP simply mechanically combines the two, resulting in a large overall system size that can easily increase the burden on patients. Summary of the Invention

[0005] This application provides a ventricular assist interventional system designed to improve the technical problems of existing ventricular assist interventional systems being bulky and easily increasing the burden on patients.

[0006] This application provides a ventricular assist interventional system, including: a diaphragm pump, a first catheter, a balloon, and a pneumatic actuator. The diaphragm pump includes a pump housing and a diaphragm within the pump housing. The pump housing has a chamber, which is divided by the diaphragm into a blood chamber and a mediator chamber. The proximal end of the first catheter is connected to the blood chamber, and the distal end of the first catheter is inserted into the ventricle. A bidirectional valve is provided on the first catheter. The balloon is implanted in the descending aorta to assist the heart; the balloon is disposed on the outer surface of the first catheter and located between the bidirectional valve and the proximal end of the first catheter. The pneumatic actuator is connected to the mediator chamber via an air circuit and to the balloon via an air circuit. The pneumatic actuator drives the diaphragm pump to aspirate or pump blood and drives the balloon to inflate or deflate. When the mediator chamber is emptied, the balloon is in a deflated state; when the mediator chamber is inflated, the balloon is in an inflated state.

[0007] In one embodiment, the ventricular assist interventional system further includes a second catheter, the distal end of which is connected to the balloon, and the proximal end of which is connected to the pneumatic main unit's air circuit.

[0008] In one embodiment, the proximal end of the second conduit is in communication with the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity.

[0009] In one embodiment, the proximal end of the second conduit is located within the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity.

[0010] In one embodiment, the proximal end of the second conduit is connected to the pneumatic main unit to achieve an air circuit connection between the second conduit and the pneumatic main unit.

[0011] In one embodiment, the proximal end of the second conduit forms part of the cavity wall of the medium cavity, the second conduit communicates with the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity.

[0012] In one embodiment, the second conduit is fixed to the surface of the first conduit.

[0013] In one embodiment, a portion of the first conduit and a portion of the second conduit share the same conduit wall.

[0014] In one embodiment, the balloon surrounds the outer surface of the first catheter.

[0015] In one embodiment, the number of balloons is one or more.

[0016] According to the ventricular assist interventional system in the above embodiments, a balloon for implantation in the descending aorta to assist the heart is disposed on the surface between the bidirectional valve on the first catheter and the proximal end of the first catheter. The distal end of the first catheter is used for insertion into the ventricle. The balloon is connected to the pneumatic host's air circuit. The proximal end of the first catheter is connected to the blood chamber of the diaphragm pump, and the medium chamber of the diaphragm pump is connected to the pneumatic host's air circuit. A single pneumatic host simultaneously drives the diaphragm pump to aspirate or pump blood and drives the balloon to inflate or contract. When the medium chamber is emptied, the balloon is in a contracted state; when the medium chamber is filled, the balloon is in an inflated state. The inflation and deflation cycle of the balloon is synchronized with the diaphragm pump's blood pumping action, thereby accurately corresponding to the heart's systole and diastole. This simplifies the number of components used in the ventricular assist interventional system. Furthermore, integrating the balloon onto the first catheter helps reduce the overall size of the ventricular assist interventional system, thereby reducing the burden on patients and improving the technical problem of existing ventricular assist interventional systems being bulky and easily increasing the burden on patients. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of a ventricular assist interventional system provided in one embodiment of this application.

[0018] Figure 2 This is a schematic diagram of another ventricular assist interventional system provided in one embodiment of this application.

[0019] Figure 3 This is a schematic diagram of the structure of another ventricular assist interventional system provided in one embodiment of this application.

[0020] Figure 4 This is a schematic diagram illustrating an application scenario of a ventricular assist interventional system provided in one embodiment of this application.

[0021] in:

[0022] 1. Ventricular Assist Interventional System; 10. Diaphragm Pump; 110. Pump Housing; 120. Diaphragm; 130. Blood Chamber; 140. Media Chamber; 20. First Catheter; 210. Two-Way Valve; 30. Balloon; 40. Pneumatic Unit; 50. Second Catheter; 2. Heart; 3. Aorta. Detailed Implementation

[0023] The present application will be further described in detail below with reference to specific embodiments and accompanying drawings. Similar elements in different embodiments are referred to by associated similar element reference numerals. In the following embodiments, many details are described to facilitate a better understanding of the present application. However, those skilled in the art will readily recognize that some features may be omitted in different situations, or may be replaced by other elements, materials, or methods. In some cases, certain operations related to the present application are not shown or described in the specification. This is to avoid obscuring the core parts of the present application with excessive description. For those skilled in the art, detailed description of these related operations is not necessary; they can fully understand the related operations based on the description in the specification and general technical knowledge in the art.

[0024] In the various embodiments of this application, "proximal" and "distal" refer to the position of the ventricular assist intervention system relative to the user in the usage environment. The end closer to the user is designated as "proximal" and the end farther from the user is designated as "distal".

[0025] Furthermore, the features, operations, or characteristics described in the specification can be combined in any suitable manner to form various embodiments, and the operational steps involved in each embodiment can also be rearranged or adjusted in a manner that is obvious to those skilled in the art. Therefore, the specification and drawings are only for clearly describing a particular embodiment and do not imply that they represent the necessary composition and / or order.

[0026] The serial numbers assigned to components in this document, such as "first" and "second," are used only to distinguish the described objects and have no sequential or technical meaning. The terms "connection" and "linkage" used in this application, unless otherwise specified, include both direct and indirect connections (linkages).

[0027] The inventive concept of this application is as follows:

[0028] Current ventricular assist interventional systems mainly include PVAD and IABP. PVAD is typically inserted percutaneously through the skin (femoral artery, etc.) and then connects to the heart to assist or take over the heart's pumping function, increasing blood flow, enhancing blood perfusion, and reducing myocardial oxygen consumption. In the short term, it helps reduce ventricular load in high-risk PCI patients and those with cardiogenic shock. The basic principle of IABP is to insert a catheter with a balloon into the descending aorta, distal to the opening of the left subclavian artery and above the opening of the renal artery, via the arterial system. During diastole, the balloon inflates; before systole, the balloon deflates, improving hemodynamics and thus assisting the heart's pumping function.

[0029] Both of the aforementioned devices can assist cardiac function, and their working principles do not conflict. Therefore, systems combining PVAD and IABP have emerged. However, in related technologies, these systems merely mechanically combine the two. Specifically, some technologies allow patients to use both PVAD and IABP simultaneously to assist cardiac function. However, these solutions have several problems. For example, they require two separate procedures to insert the PVAD and IABP devices into the patient's body. Furthermore, because these technologies only mechanically combine PVAD and IABP, each device performs its own function and is controlled by two separate drive units, resulting in a large overall system size that can increase the burden on the patient.

[0030] Based on the above phenomena, the inventors creatively combined PVAD and IABP to achieve mutual functional cooperation between the two, so that the combined system of PVAD and IABP can achieve a 1+1>2 effect.

[0031] Please see Figure 1 This application provides a ventricular assist interventional system 1, which includes a diaphragm pump 10, a first catheter 20, a balloon 30, and a pneumatic motor 40. The diaphragm pump 10 includes a pump housing 110 and a diaphragm 120 located in the pump housing 110. The pump housing 110 has a chamber, which is divided by the diaphragm 120 into a blood chamber 130 and a medium chamber 140.

[0032] The proximal end of the first catheter 20 is used to connect to the blood chamber 130, and the distal end of the first catheter 20 is used to insert into the ventricle. A bidirectional valve 210 is provided on the first catheter 20. This embodiment does not limit the specific location of the bidirectional valve 210. For example, in this embodiment, the bidirectional valve 210 can be located near the distal end of the first catheter 20 and away from the proximal end. The first catheter 20 can absorb blood under the drive of the diaphragm pump 10 and pump the blood out from the bidirectional valve 210.

[0033] Specifically, in this embodiment, the distal end of the first catheter 20 is the blood aspiration port, and the first catheter 20 can have a blood pumping port at the bidirectional valve 210. The bidirectional valve 210 can be used to control the flow direction of blood in the first catheter 20, and thus the bidirectional valve 210 can be used to avoid or reduce the situation of blood backflow. When the diaphragm pump 10 drives the first catheter 20 to draw blood, the blood enters the blood chamber through the blood aspiration port and the bidirectional valve. When the diaphragm pump 10 drives the first catheter 20 to pump blood, the blood enters the ascending aorta 3 through the bidirectional valve and the blood pumping port.

[0034] The balloon 30 is implanted in the descending aorta 3 to assist the heart 2. In this embodiment, the balloon 30 is disposed on the outer surface of the first catheter 20 and located between the bidirectional valve 210 and the proximal end of the first catheter 20. This application does not limit the connection method between the balloon 30 and the first catheter 20. For example, in one embodiment, the balloon 30 can be fixedly sleeved on the outer surface of the first catheter 20.

[0035] Furthermore, in this embodiment, the number of balloons 30 can be set to one, and the balloon 30 can surround the outer surface of the first catheter 20. That is, in this embodiment, the balloon 30 can be set as a ring structure, and the first catheter 20 can be inserted at the center of the balloon 30. When the balloon 30 inflates, part of the outer surface of the balloon 30 contacts the inner wall of the descending aorta 3 and blocks the descending aorta 3, thereby increasing the diastolic pressure at the root of the descending aorta 3 and increasing the perfusion pressure of the coronary artery. It can be understood that, compared with the first catheter 20, using a single balloon 30 to block the descending aorta 3 has a better blocking effect, thereby increasing the perfusion pressure of the coronary artery more. This is beneficial for reducing the left ventricular ejection resistance when the balloon 30 deflates and contracts, ultimately reducing the afterload of the heart 2. Furthermore, compared to using multiple balloons 30, during the inflation and deflation of the balloons 30, some blood may accumulate and be stored in the gaps between the balloons 30. Using a single balloon 30 can avoid or reduce the problem of blood accumulation and storage in the balloon 30.

[0036] Furthermore, in some other embodiments, the number of balloons 30 can also be set to multiple, with multiple balloons 30 evenly surrounding the outer surface of the first catheter 20, and the contraction and expansion processes of each balloon 30 being synchronized. It is understood that because multiple balloons 30 are used, the response time of each balloon's contraction and expansion is shorter, thereby making the entire ventricular assist interventional system 1 more sensitive. It should be noted that this application embodiment does not limit the number of balloons 30; the specific number can be set according to actual conditions.

[0037] The pneumatic actuator 40 is connected to the media chamber 140 via an air passage, and also to the balloon 30 via an air passage. The pneumatic actuator 40 is used to drive the diaphragm pump 10 to aspirate or pump blood. Specifically, the pneumatic actuator 40 can inflate or deflate the media chamber 140 to achieve the absorption or pumping of blood. The pneumatic actuator 40 is also used to drive the balloon 30 to inflate or deflate, enabling the pneumatic actuator 40 to inflate or deflate the balloon 30.

[0038] Furthermore, in this embodiment, the pneumatic main unit 40 can also be configured such that when the medium chamber 140 is evacuated, the balloon 30 is in a contracted state, and when the medium chamber 140 is inflated, the balloon 30 is in an inflated state. That is to say, in this embodiment, the inflation and deflation cycle of the balloon 30 is synchronized with the working cycle of the diaphragm pump 10, and the ventricular assist intervention system 1 exhibits a significant synergistic effect throughout the entire working process synchronized with the cardiac cycle.

[0039] Specifically, during the systole of heart 2, the medium chamber 140 of diaphragm pump 10 is emptied, causing the blood chamber 130 of diaphragm pump 10 to begin drawing blood. At the same time, balloon 30 is simultaneously emptied and collapsed. This combined action not only directly reduces the preload of the left ventricle through suction, but also significantly reduces the pressure at the root of the aorta 3 and the afterload of the left ventricle by making room for the balloon 30 to collapse in the aorta 3. This achieves a double unloading of heart 2, greatly reduces myocardial oxygen consumption, and makes blood suction more efficient.

[0040] During diastole, the pneumatic actuator 40 injects a medium into the media chamber 140, and the positive pressure pushes the blood in the blood chamber 130 out at high speed. At the same time, the balloon 30 inflates and expands synchronously. This combined action not only directly increases cardiac output through active blood pumping, but the inflation of the balloon 30 also increases diastolic pressure, enhances coronary perfusion, and further propels the pumped blood forward, achieving a dual pressurization effect during diastole and maximizing blood perfusion to the myocardium and other vital organs.

[0041] It should be noted that the embodiments of this application do not limit the specific air path connection method between the pneumatic main unit 40 and the medium cavity 140, nor does it limit the specific air path connection method between the pneumatic main unit 40 and the balloon 30. For example, in some embodiments, the pneumatic main unit 40 can be directly connected to the balloon 30 through an air path, and in other embodiments, the pneumatic main unit 40 can be indirectly connected to the balloon 30 through an air path.

[0042] For example, please refer to Figure 1 In this embodiment, the ventricular assist intervention system 1 may further include a second catheter 50, the distal end of which is connected to the balloon 30, and the proximal end of which is connected to the pneumatic host 40 via the air passage. The pneumatic host 40 can inflate and deflate the balloon 30 through the second catheter 50.

[0043] Furthermore, in one embodiment, the proximal end of the second conduit 50 can be connected to the medium cavity 140. The second conduit 50 can be connected to the pneumatic host 40 through the medium cavity 140 to achieve air circuit connection. When the pneumatic host 40 inflates the medium cavity 140, the gas can also pass through the medium cavity 140 to inflate the balloon 30. When the pneumatic host 40 deflates the medium cavity 140, the gas in the balloon 30 can also be extracted through the medium cavity 140.

[0044] It should be noted that the embodiments of this application do not limit the specific manner in which the proximal end of the second catheter 50 communicates with the medium cavity 140. For example, in one embodiment, the proximal end of the second catheter 50 may be located on the inner surface of the medium cavity 140 to achieve communication between the proximal end of the second catheter 50 and the medium cavity 140. For another example, please refer to... Figure 1 In another embodiment, the proximal end of the second catheter 50 may be located within the medium cavity 140. That is, in this embodiment, the proximal end of the second catheter 50 extends into the interior of the medium cavity 140. The specific form adopted can be set according to the actual situation and is not limited here.

[0045] In addition, please see Figure 2 In another embodiment, the proximal end of the second conduit 50 can be directly connected to the pneumatic host 40 to realize the air path connection between the second conduit 50 and the pneumatic host 40. That is to say, in this embodiment, the second conduit 50 can be connected to the pneumatic host 40 as a separate branch. In this embodiment, the pneumatic host 40 can also drive the balloon 30 to contract during the contraction of the driving medium cavity 140 and drive the balloon 30 to expand during the expansion of the driving medium cavity 140, so that the inflation and deflation cycle of the balloon 30 is synchronized with the working cycle of the diaphragm pump 10.

[0046] Please see Figure 3 In this embodiment, the proximal end of the second catheter 50 forms part of the wall structure of the medium cavity 140. The second catheter 50 communicates with the medium cavity 140 and is connected to the pneumatic main unit 40 through the medium cavity 140. It is understood that because a portion of the proximal region of the second catheter 50 shares the same structure as the wall of the medium cavity 140, the connection stability between the second catheter 50 and the medium cavity 140 is higher in this embodiment, and the flow area between the second catheter 50 and the medium cavity 140 is also larger. This facilitates synchronizing the inflation and deflation cycles of the balloon 30 with the blood flow action of the diaphragm pump 10.

[0047] In this embodiment, the second catheter 50 can be fixed to the surface of the first catheter 20, so that when the operator uses the ventricular assist intervention system 1, only one injury is caused to the patient's body to install the entire ventricular assist intervention system 1 in the patient's body, which helps to reduce the burden on the patient.

[0048] The embodiments of this application do not limit the fixing method between the second conduit 50 and the first conduit 20. For example, in some embodiments, the second conduit 50 and the first conduit 20 can be fixed by means of bonding, etc., and in other embodiments, the second conduit 50 can be fixed by being fitted onto the first conduit 20.

[0049] Furthermore, in this embodiment, the second catheter 50 and the first catheter 20 can also be configured as an integrally formed structure. That is, in this embodiment, a portion of the first catheter 20 and a portion of the second catheter 50 share the same tube wall. This not only improves the connection stability between the second catheter 50 and the first catheter 20, but also helps to reduce the volume occupied by the first catheter 20 and the second catheter 50, thereby helping to reduce harm to the patient's body.

[0050] It should be noted that the embodiments of this application do not limit the specific structural forms of the first conduit 20 and the second conduit 50. For example, in one embodiment, the second conduit 50 can be located inside the first conduit 20, that is, the second conduit 50 can be enclosed inside the first conduit 20, in which case a portion of the inner wall of the first conduit 20 and a portion of the outer wall of the second conduit 50 can be shared. In another embodiment, the second conduit 50 can be located outside the first conduit 20, that is, in this embodiment, a portion of the outer wall of the first conduit 20 and a portion of the outer wall of the second conduit 50 can be shared. The specific form adopted can be set according to the actual situation and is not limited here.

[0051] The following describes the working principle of a ventricular assist interventional system 1 provided in an embodiment of this application:

[0052] Please see Figure 4After the ventricular assist device 1 is implanted in the patient, the distal end of the first catheter 20 can be located in the left ventricle, and the bidirectional valve 210 can be located in the ascending aorta, while the balloon 30 can be located in the descending aorta 3. During the systole of the heart 2, the media chamber 140 of the diaphragm pump 10 is evacuated by the main unit, generating negative pressure. This negative pressure is transmitted to the blood chamber 130 of the diaphragm pump 10, causing the first catheter 20 to begin aspirating blood. At the same time, as the media chamber 140 is evacuated, the balloon 30 connected to it is also emptied and collapses synchronously. The aspiration effect of the first catheter 20 directly reduces the preload (volume load) of the left ventricle. The collapse of the balloon 30 instantly creates more space in the aorta 3, greatly reducing the pressure at the root of the aorta 3, that is, significantly reducing the afterload (pressure load) that the left ventricle needs to overcome for ejection. The simultaneous reduction of the preload and afterload of the left ventricle significantly reduces the work done by the heart 2 during systole, and significantly reduces myocardial oxygen consumption, creating extremely favorable conditions for myocardial repair.

[0053] The flow rate of blood drawn from the left ventricle through the inlet of the first catheter 20 becomes faster and more efficient due to the reduced afterload. During diastole, the pneumatic actuator 40 injects media into the media chamber 140 of the diaphragm pump 10, and the positive pressure pushes the diaphragm 120 of the blood chamber 130, pumping the stored blood out at high speed and injecting it into the ascending aorta 3 through the outlet of the bidirectional valve 210 on the first catheter 20. At the same time, the inflation of the media chamber 140 causes the balloon 30 to inflate and expand synchronously. The diaphragm pump 10 is connected to the pneumatic actuator 40, which actively pushes the diaphragm pump 10 to pump out blood, providing a strong forward blood flow and directly increasing cardiac output. The inflation of the balloon 30 occupies part of the space within the aorta 3, which not only increases diastolic pressure and enhances coronary perfusion, but also further promotes the forward flow of blood pumped out by the bidirectional valve 210 and helps reduce blood backflow. The combined effect of active blood pumping and balloon 30 counterpulsation can more effectively increase diastolic blood pressure, thereby greatly improving blood perfusion of the myocardium and vital organs (brain and kidneys).

[0054] In summary, according to the ventricular assist interventional system 1 in the above embodiments, a balloon 30 for implanting the descending aorta 3 to assist the heart 2 is disposed on the surface between the bidirectional valve 210 on the first catheter 20 and the proximal end of the first catheter 20. The distal end of the first catheter 20 is used for insertion into the ventricle. The balloon 30 is connected to the pneumatic host 40 via an air circuit. The proximal end of the first catheter 20 is connected to the blood chamber 130 of the diaphragm pump 10, and the medium chamber 140 of the diaphragm pump 10 is connected to the pneumatic host 40 via an air circuit. A single pneumatic host 40 simultaneously drives the diaphragm pump 10 to aspirate or pump blood and drives the balloon 30 to inflate or contract. Furthermore, when the media chamber 140 is emptied, the balloon 30 is in a contracted state; when the media chamber 140 is inflated, the balloon 30 is in an inflated state. The inflation and deflation cycle of the balloon 30 is synchronized with the blood flow of the diaphragm pump 10, thereby precisely corresponding to the systole and diastole of the heart 2. This simplifies the number of components used in the ventricular assist interventional system 1. In addition, integrating the balloon 30 onto the first catheter 20 helps to reduce the overall volume of the ventricular assist interventional system 1, thereby reducing the burden on patients and improving the technical problem of the existing ventricular assist interventional system 1 being bulky and easily increasing the burden on patients.

[0055] The above examples illustrate the present invention only to aid in understanding it and are not intended to limit the scope of the invention. Those skilled in the art can make various simple deductions, modifications, or substitutions based on the principles of this invention.

Claims

1. A ventricular assist interventional system, characterized in that, include: A diaphragm pump, the diaphragm pump comprising a pump housing and a diaphragm disposed within the pump housing, the pump housing having a chamber divided by the diaphragm into a blood chamber and a medium chamber; A first catheter, the proximal end of which is used to connect to the blood chamber, and the distal end of which is used to insert into the ventricle, and the first catheter is provided with a two-way valve; A balloon for implantation in the descending aorta to assist the heart; the balloon is disposed on the outer surface of the first catheter and located between the bidirectional valve and the proximal end of the first catheter; A pneumatic main unit is connected to the air passage of the medium cavity and the air passage of the balloon. The pneumatic main unit is used to drive the diaphragm pump to aspirate or pump blood and to drive the balloon to inflate or contract. When the medium cavity is emptied, the balloon is in a contracted state. When the medium cavity is filled, the balloon is in an inflated state; as well as The second catheter has its distal end connected to the balloon and its proximal end connected to the pneumatic main unit's air circuit. The proximal end of the second conduit is connected to the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity; Alternatively, the proximal end of the second conduit is located within the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity; Alternatively, the proximal end of the second conduit forms part of the cavity wall of the medium cavity, the second conduit communicates with the medium cavity, and the second conduit is connected to the pneumatic main unit's air circuit through the medium cavity.

2. The ventricular assist interventional system as described in claim 1, characterized in that, The proximal end of the second conduit is connected to the pneumatic main unit to realize the air circuit connection between the second conduit and the pneumatic main unit.

3. The ventricular assist interventional system as described in any one of claims 1-2, characterized in that, The second conduit is fixed to the surface of the first conduit.

4. The ventricular assist interventional system as described in any one of claims 1-2, characterized in that, A portion of the first conduit and a portion of the second conduit share the same conduit wall.

5. The ventricular assist interventional system as described in claim 1, characterized in that, The balloon surrounds the outer surface of the first catheter.

6. The ventricular assist interventional system as described in claim 1, characterized in that, The number of balloons is one or more.

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