CN115531715A - Interventional blood pumping assembly and pumping method - Google Patents

Abstract

The invention provides an intervention type blood pumping assembly and a pumping method, wherein the intervention type blood pumping assembly comprises: the device comprises a barrel body with a storage cavity and a pumping mechanism which partially and longitudinally penetrates through the barrel body; the pumping mechanism includes: the blood input tube and the blood output tube are formed at two ends of the cylinder body and are communicated with the storage cavity; the blood input tube and the blood output tube respectively form an input one-way valve and an output one-way valve which are exposed at two ends of the cylinder body, the input one-way valve supplies blood to flow into the storage cavity, the output one-way valve supplies the blood in the storage cavity to be discharged, and the input one-way valve and the output one-way valve are alternatively opened or closed. Through this application, avoid causing the extrusion to input check valve and output check valve and lead to input check valve and output check valve to appear closing not tight problem to play the supplementary ventricular blood output that increases, rise aorta pressure and coronary artery perfusion pressure, improve the effect of mean artery pressure, coronary artery blood flow.

Description

Interventional blood pumping assembly and pumping method

Technical Field

The invention relates to the technical field of medical instruments, in particular to an interventional blood pumping assembly and a pumping method.

Background

Heart failure (heart failure) refers to a heart circulatory disturbance syndrome caused by insufficient discharge of venous return blood volume from the heart due to the failure of the systolic function and/or diastolic function of the heart, resulting in venous system blood stasis and arterial system blood perfusion deficiency, wherein the disturbance syndrome is manifested as pulmonary congestion and vena cava congestion. In the prior art, a blood circulation device is usually adopted for heart failure assistance and extracorporeal assisted circulation, and the commonly used blood circulation device comprises a left ventricle auxiliary device, a right ventricle auxiliary device, a total artificial heart and other heart auxiliary devices and a saccule type trans-valve blood pump, and the blood pump is mainly installed in a heart to solve the problem of pumping blood of the heart. Among them, balloon-type transvalvular blood pumps, by placing the pump in the aorta, the pump draws blood from the left ventricle through the aortic valve and pumps it into the body when inflated by alternately switching between systolic and diastolic phases.

However, the one-way air intake valve and the one-way outflow valve included in the balloon-type trans-valvular blood pump in the prior art are both arranged inside the cylinder, when the pump pumps blood, the membrane in the cylinder can be extruded to shrink the membrane, the membrane can extrude the one-way air intake valve and the one-way outflow valve in the cylinder in the shrinking process, and the one-way air intake valve and the one-way outflow valve can be extruded at high frequency in the process of conveying blood by the pump, so that the one-way air intake valve and the one-way outflow valve are damaged, and the problem of untight closing of the one-way air intake valve and the one-way outflow valve occurs, so that the blood in the membrane flows back to the left ventricle when the pump inflates in the diastole, and the blood output of the left ventricle is reduced.

In view of the above, there is a need for an improved blood pumping access assembly of the prior art to solve the above-mentioned problems.

Disclosure of Invention

The invention aims to disclose an intervention type blood pumping assembly and a pumping method, which are used for solving the defects of the blood pumping intervention assembly in the prior art, in particular to avoid squeezing an input one-way valve and an output one-way valve when the blood pumping intervention assembly pumps blood so as to prevent the input one-way valve and the output one-way valve from being not closed tightly.

To achieve the above object, the present invention provides an interventional blood pumping assembly comprising: the device comprises a barrel body with a storage cavity and a pumping mechanism which partially and longitudinally penetrates through the barrel body;

the pumping mechanism includes:

the blood input tube and the blood output tube are formed at two ends of the cylinder body and are communicated with the storage cavity;

the blood input tube and the blood output tube respectively form an input one-way valve and an output one-way valve which are exposed at two ends of the cylinder body, the input one-way valve supplies blood to flow into the storage cavity, the output one-way valve supplies the blood in the storage cavity to be discharged, and the input one-way valve and the output one-way valve are alternatively opened or closed.

As a further improvement of the present invention, the pumping mechanism further comprises:

the blood transfusion device comprises a blood output pipe, a cylinder body and a blood input pipe, wherein the blood output pipe, the cylinder body and the blood input pipe are continuously penetrated through by the blood output pipe, the cylinder body and the blood input pipe, at least one saccule which is nested in the catheter and is formed in the storage cavity to expand or contract, and an extracorporeal control device which is communicated with the catheter and is used for conveying working fluid.

As a further improvement of the invention, the catheter is configured with a flow channel for communicating with the extracorporeal control device, and a through hole for communicating the flow channel with the balloon;

the extracorporeal control device drives working fluid to pass through the through hole to realize injection or extraction in the balloon, so that the balloon is switched between an expansion state and a contraction state in the storage cavity.

As a further improvement of the invention, a lead for controlling the input one-way valve and the output one-way valve to open or close is arranged in the conduit.

As a further improvement of the present invention, when the input one-way valve is in an open state, the output one-way valve is in a closed state, and the balloon is in a contracted state, so that blood flows into the storage cavity through the input one-way valve.

As a further improvement of the present invention, when the input one-way valve is in a closed state, the output one-way valve is in an open state, and the balloon is in an expanded state, so as to discharge blood in the storage chamber through the output one-way valve.

As a further improvement of the invention, the balloon is intermittently injected with a working fluid and is gradually expanded during the injection of the working fluid to expand the balloon to fill the reservoir.

As a further improvement of the invention, the catheter extends into the end formed by the ventricle and is provided with a pressure sensor.

As a further improvement of the invention, the cylinder is configured as a rigid cylindrical hollow cylinder;

the cylinder is configured to be a combination of a high polymer material and a shape memory alloy bracket, the high polymer is polytetrafluoroethylene, polyethylene and polyamide, and the shape memory alloy is nickel-titanium alloy.

Based on the same invention idea, the invention also discloses a pumping method of the intervention type blood pumping assembly, which comprises the following steps:

s1, when the input one-way valve is in an open state and the output one-way valve is in a closed state, the extracorporeal control device pumps out working fluid in the saccule to enable the saccule to contract and enable the storage cavity to generate negative pressure so as to pump blood in the heart chamber through the input one-way valve;

and S2, when the input one-way valve is in a closed state and the output one-way valve is in an open state, the extracorporeal control device injects working fluid into the balloon so as to expand the balloon and discharge the blood in the storage cavity into the aorta through the output one-way valve.

Compared with the prior art, the invention has the beneficial effects that:

the pumping mechanism extracts blood in the left ventricle through the input one-way valve to enter the storage cavity, and discharges the blood in the storage cavity into the aorta through the output one-way valve, because the input one-way valve and the output one-way valve are respectively exposed at two ends of the barrel, the pumping mechanism can not extrude the input one-way valve and the output one-way valve in the process of pumping the blood, so as to avoid damaging the input one-way valve and the output one-way valve, thereby preventing the input one-way valve and the output one-way valve from being loosely closed, further playing a role in assisting in increasing the blood output of the left ventricle, increasing the aortic pressure and the coronary perfusion pressure, and improving the functions of mean arterial pressure and coronary blood flow.

Drawings

FIG. 1 is a schematic illustration of an interventional blood pumping assembly of the present invention inserted into the aorta and left ventricle;

FIG. 2 is a schematic view of the balloon of FIG. 1 in a gradually expanded state;

FIG. 3 is a schematic view of the balloon of FIG. 2 in a gradually expanded state;

FIG. 4 is a schematic view of the balloon of FIG. 1 expanded to completely fill the storage chamber;

FIG. 5 is a flow chart of a method of pumping the interventional blood pumping assembly of the present disclosure.

Detailed Description

The present invention is described in detail with reference to the embodiments shown in the drawings, but it should be understood that these embodiments are not intended to limit the present invention, and those skilled in the art should understand that functional, methodological, or structural equivalents or substitutions made by these embodiments are within the scope of the present invention.

It should be understood that in the present application, the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "axial", "radial", etc. indicate orientations or positional relationships based on those shown in the drawings, and are only for convenience of description and simplicity of description, but do not indicate or imply that the device or element being referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be considered as limiting the present disclosure.

In particular, in the following embodiments, the term "longitudinal" refers to the longitudinal direction of the cylinder 10.

Please refer to fig. 1-5, which illustrate an embodiment of an interventional blood pumping assembly and pumping method.

The embodiment of the present invention discloses an interventional blood pumping assembly 100 for heart failure (heart failure) in human beings. When the systolic function and/or diastolic function of the heart are/is obstructed and venous return blood volume cannot be sufficiently discharged out of the heart, the intervention type blood pumping assembly 100 is required to be placed in the aorta 3 of a human body to pump blood in the left ventricle 1 into the aorta 3, so that the intervention type blood pumping assembly 100 can avoid damaging the input one-way valve 211 and the output one-way valve 221 in the process of pumping blood, prevent the problem that the input one-way valve 211 and the output one-way valve 221 are not closed tightly, avoid blood from flowing back to the left ventricle 1, and play a role in assisting in increasing the blood output of the left ventricle 1, increasing the aortic pressure and coronary perfusion pressure and improving the mean arterial pressure and coronary blood flow volume.

Referring to fig. 1, in the present embodiment, the interventional blood pumping assembly 100 comprises: a barrel 10 having a storage chamber 11, and a pumping mechanism 20 extending partially longitudinally through the barrel 10; the pumping mechanism 20 includes: a blood inlet tube 21 and a blood outlet tube 22 formed at both ends of the cylinder 10 and communicating with the reservoir chamber 11. The blood inlet tube 21 extends lengthwise along the barrel 10 through the aortic valve 2 and into the left ventricle 1. The blood outlet tube 22 extends into the aorta 3 in the longitudinal direction of the barrel 10, the blood outlet tube 22 extending in the opposite direction to the blood inlet tube 21.

Referring to fig. 1 to 4, the blood inlet tube 21 and the blood outlet tube 22 form an inlet check valve 211 and an outlet check valve 221 respectively exposed at two ends of the cylinder 10, the inlet check valve 211 provides blood to flow into the storage chamber 11, and the outlet check valve 221 provides blood to be discharged from the storage chamber 11. The blood inlet tube 21 forms an inlet check valve 211 in the left ventricle 1, so that the blood in the left ventricle 1 flows into the inlet check valve 211 in the direction of arrow a in fig. 1 and enters the storage chamber 11 along the blood inlet tube 21 for storage. The blood outlet tube 22 forms an outlet check valve 221 in the aorta 3, so that the blood in the storage chamber 11 flows to the blood outlet tube 22 in the direction of arrow B in FIG. 3 and is discharged to the aorta 3 through the outlet check valve 221.

Input check valve 211 and output check valve 221 are alternatively opened or closed. When the input check valve 211 is in an open state, the output check valve 221 is in a closed state, so that the pumping mechanism 20 sucks the blood in the left ventricle 1 into the input check valve 211 along the direction indicated by the arrow a and flows into the blood input tube 21, so that the blood flows into the storage cavity 11 along the blood input tube 21 for storage, and because the output check valve 221 is in a closed state, the pumping mechanism 20 can be prevented from sucking the blood in the aorta 3 into the storage cavity 11, so that the blood backflow is prevented; when the input check valve 211 is closed, the output check valve 221 is opened, so that the pumping mechanism 20 can discharge the blood in the storage chamber 11 into the blood output tube 22 and into the aorta 3 through the output check valve 221, so as to assist in increasing the blood output of the left ventricle 1, increasing the aortic pressure and coronary perfusion pressure, and improving the mean arterial pressure and coronary blood flow. Because the input check valve 211 is in a closed state, the pumping mechanism 20 can be prevented from discharging the blood in the storage chamber 11 to the blood input tube 21, so that the blood can be prevented from generating a squeezing effect on the input check valve 211, and the input check valve 211 can be prevented from being damaged.

Because the input check valve 211 and the output check valve 221 are respectively exposed at two ends of the cylinder 10, and the input check valve 211 and the output check valve 221 are respectively formed in the left ventricle 1 and the aorta 3, the pumping mechanism 20 can avoid squeezing the input check valve 211 and the output check valve 221 outside the cylinder 10 in the process of sucking the blood in the left ventricle 1 into the storage cavity 11 and pumping the blood into the aorta 3, thereby avoiding the problem that the input check valve 211 and the output check valve 221 are damaged due to squeezing and are not closed tightly, and the blood flows back to the left ventricle 1.

As shown in fig. 1, 3 and 4, the pumping mechanism 20 further includes: a catheter 23 continuously penetrating the blood output tube 22, the cylinder 10 and the blood input tube 21, at least one balloon 24 nested in the catheter 23 and formed in the storage chamber 11 to perform expansion or contraction, and an extracorporeal control device 26 communicating with the catheter 23 and delivering a working fluid. The extracorporeal control apparatus 26 is provided outside the human body. The extracorporeal control device 26 injects or extracts working fluid (the working fluid may be gas or liquid) into or from the balloon 24 through the catheter 23 to drive the balloon 24 to expand or contract in the storage cavity 11, and the cylinder 10 may be a rigid cylindrical hollow cylinder, so that the cylinder 10 is not easily deformed to fix the size of the storage cavity 11, and the pressure in the storage cavity 11 is also changed when the size of the balloon 24 is changed. During the contraction of the balloon 24, negative pressure is generated in the storage cavity 11, so that blood in the left ventricle 1 is extracted, and the blood is sucked into the input one-way valve 211 along the direction shown by the arrow A and flows into the storage cavity 11 along the blood input tube 21 for storage; during inflation of balloon 24, the pressure in storage chamber 11 will rise, thereby discharging the blood in storage chamber 11 in the direction of arrow B in fig. 4 to blood outlet tube 22 and out through outlet check valve 221 to aorta 3.

The cylinder 10 may also be a combination of polymer material and shape memory alloy support (not shown), the polymer may be Polytetrafluoroethylene (PTFE), polyethylene (PE), or polyamide; the shape memory alloy may be a nickel titanium alloy. The shape memory alloy stent (not shown) in the cylinder 10 is covered by a high polymer material, can be compressed in the catheter 23, is conveyed through the catheter 23 and is placed at the descending aorta 3, a plurality of shape memory alloy support legs (not shown) extend out of the vessel wall of the aorta 3, the cylinder 10 expands, and the shape memory alloy support legs support the vessel wall so as to fix the catheter 23 and prevent the movement of the catheter 23 caused by the power of blood flow.

Specifically, catheter 23 is configured with a flow channel 231 communicating with external control device 26, and a through hole 232 communicating flow channel 231 with balloon 24; the extracorporeal control apparatus 26 drives the working fluid through the through-hole 232 to perform injection or extraction inside the balloon 24, so as to switch the balloon 24 between the expanded state or the contracted state inside the storage chamber 11. The working fluid is injected into the flow channel 231 in the catheter 23 through the extracorporeal control device 26, the working fluid is injected into the balloon 24 through the through hole 232 in the flow channel 231 in the direction indicated by the arrow C in fig. 2, so that the balloon 24 is expanded, and the balloon 24 can discharge the blood in the storage chamber 11 into the blood output tube 22 in the direction indicated by the arrow B during the expansion process, and discharge the blood to the aorta 3 through the output check valve 221. The working fluid in the flow channel 231 is pumped out by the extracorporeal control device 26, and the working fluid in the balloon 24 enters the flow channel 231 through the through hole 232, so that the balloon 24 contracts and generates negative pressure in the storage cavity 11, thereby pumping the blood in the left ventricle 1, and the blood is sucked into the input one-way valve 211 along the direction of arrow a and flows into the storage cavity 11 along the blood input tube 21 for storage. The balloon 24 is controlled by the extracorporeal control device 26 to alternately expand and contract, and the process is repeated, so that blood enters the storage cavity 11 from the left ventricle 1 and is discharged to the aorta 3, and the functions of assisting in increasing the blood output of the left ventricle 1, increasing the aortic pressure and the coronary perfusion pressure, and improving the mean arterial pressure and the coronary blood flow are achieved.

It should be noted that the number of balloons 24 may be one or more, and only complete filling or partial filling of storage chamber 11 may be achieved. This embodiment is preferably one balloon 24. The balloon 24 is made of a polymer material with good biocompatibility, such as polyamide, polytetrafluoroethylene (PTFE) or TPU (Thermoplastic polyurethanes), etc., so as to reduce damage and injury to blood during expansion and contraction of the balloon 24. Balloon 24 has good expandability and contractibility.

The conduit 23 is internally provided with a lead 27 for controlling the opening or closing of the input check valve 211 and the output check valve 221. The input check valve 211 and the output check valve 221 are alternatively opened or closed by the lead 27. When the input check valve 211 is in the open state, the output check valve 221 is in the closed state. When the input check valve 211 is in the closed state, the output check valve 221 is in the open state.

Illustratively, the input check valve 211 or the output check valve 221 may be configured as an annular body (not shown) that is hooped to the blood input tube 21 and has a circular ring shape, and the inside of the annular body is a hollow structure (not shown) in which an annular balloon (not shown) that performs expansion or contraction is disposed, the annular balloon being provided with at least one delivery tube (not shown), and an extracorporeal delivery device (not shown) that communicates with the annular balloon and delivers the operation fluid through the delivery tube. The extracorporeal conveying device conveys or outputs the working fluid to the annular air bag through the conveying pipe so as to control the annular air bag to expand or contract in the annular body. When the annular air bag is expanded, the inner blood input tube 21 or the inner blood output tube 22 is squeezed to limit the blood circulation in the blood input tube 21 or the blood output tube 22, so that the blood input tube 21 or the blood output tube 22 is closed. When the annular air bag is contracted, the squeezing effect on the blood input tube 21 or the blood output tube 22 is canceled, so that the blood input tube 21 or the blood output tube 22 can be restored to a non-squeezed state to facilitate blood circulation, and the blood input tube 21 or the blood output tube 22 is opened. At the same time, the extracorporeal delivery device will control the input check valve 211 and the output check valve 221 to open or close alternatively.

Further, the catheter 23 extends into the distal end 233 formed by the left ventricle 1 to provide a pressure sensor 25. The input check valve 211 is formed between the pressure sensor 25 and the cylinder 10. The pressure sensor 25 is used for monitoring the pressure change in the left ventricle 1, and the balloon 24 can completely fill the storage cavity 11 or partially fill the storage cavity 11 by adjusting the expansion volume of the balloon 24 according to the pressure in the left ventricle 1, so as to adjust the amount of blood pumped into the aorta 3 by the pumping mechanism 20; the amount of blood pumped into the aorta 3 by the pumping mechanism 20 can be adjusted by adjusting the frequency of opening and closing the input check valve 211 and the output check valve 221 and the switching frequency of the balloon 24 between the expanded state and the contracted state, so as to prevent hypertension or hypotension caused by excessive or insufficient pressure in the left ventricle 1.

Illustratively, the balloon 24 is intermittently injected with the working fluid, and the balloon 24 is gradually expanded during the injection of the working fluid to expand the balloon 24 to fill the storage lumen 11. The extracorporeal control device 26 intermittently injects the working fluid into the balloon 24, and the expansion amplitude of one side of the balloon 24 close to the input one-way valve 211 is larger than that of the other side (refer to the expansion state of the balloon 24a in fig. 2 and the balloon 24B in fig. 3), so that the balloon 24 discharges the blood in the storage cavity 11 into the blood output tube 22 along the direction indicated by the arrow B in the process of gradual expansion until the state of the balloon 24c in fig. 4 is formed, and thus the blood in the storage cavity 11 is completely discharged into the blood output tube 22, and the balloon 24 is prevented from discharging the blood in the storage cavity 11 into the blood input tube 21, so that the blood is prevented from squeezing the input one-way valve 211, and the input one-way valve 211 is prevented from being damaged.

The outer diameter of the cylinder 10 is smaller than the inner diameter of the blood vessel. To prevent the cartridge 10 from occluding the aorta 3 and to facilitate blood flow around the cartridge 10.

Illustratively, as shown in fig. 1 to 5, based on the interventional blood pumping assembly 100 disclosed in the foregoing embodiments, the present application further discloses a pumping method of the interventional blood pumping assembly, comprising the following steps:

step S1, when the input check valve 211 is in the open state and the output check valve 221 is in the closed state, the extracorporeal control device 26 extracts the working fluid in the balloon 24 to contract the balloon 24 and generate a negative pressure in the storage chamber 11, so as to extract the blood in the left ventricle 1 through the input check valve 211. The lead 27 controls the input check valve 211 to open, the output check valve 221 to close, the extracorporeal control device 26 pumps the working fluid in the flow channel 231, so that the working fluid in the balloon 24 enters the flow channel 231 through the through hole 232, the balloon 24 contracts and generates negative pressure in the storage cavity 11, and thus blood in the left ventricle 1 is pumped, and the blood is sucked into the input check valve 211 along the direction of the arrow A and flows into the storage cavity 11 along the blood input tube 21 for storage.

Step S2, when the input check valve 211 is in the closed state and the output check valve 221 is in the open state, the extracorporeal control device 26 injects the working fluid into the balloon 24 to expand the balloon 24 and discharge the blood in the storage chamber 11 to the aorta 3 through the output check valve 221. The input one-way valve 211 is controlled to be closed and opened through the lead 27, the output one-way valve 221 is controlled to be opened, the working fluid is injected into the flow channel 231 in the guide pipe 23 through the extracorporeal control device 26, the working fluid is injected into the balloon 24 through the through hole 232 in the direction shown by an arrow C in fig. 2 in the flow channel 231, so that the balloon 24 is expanded, and the balloon 24 can discharge the blood in the storage cavity 11 into the blood output pipe 22 in the direction shown by an arrow B in the expanding process and is discharged to the aorta 3 through the output one-way valve 221. The balloon 24 is controlled by the extracorporeal control device 26 to alternately expand and contract, and the process is repeated, so that blood enters the storage cavity 11 from the left ventricle 1 and is discharged to the aorta 3, and the functions of assisting in increasing the blood output of the left ventricle 1, increasing the aortic pressure and the coronary perfusion pressure, and improving the mean arterial pressure and the coronary blood flow are achieved.

The above-listed detailed description is only a specific description of a possible embodiment of the present invention, and they are not intended to limit the scope of the present invention, and equivalent embodiments or modifications made without departing from the technical spirit of the present invention should be included in the scope of the present invention.

It will be evident to those skilled in the art that the invention is not limited to the details of the foregoing illustrative embodiments, and that the present invention may be embodied in other specific forms without departing from the spirit or essential attributes thereof. The present embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein. Any reference sign in a claim should not be construed as limiting the claim concerned.

Furthermore, it should be understood that although the present description refers to embodiments, not every embodiment may contain only a single embodiment, and such description is for clarity only, and those skilled in the art should integrate the description, and the embodiments may be combined as appropriate to form other embodiments understood by those skilled in the art.

Claims (10)

1. An interventional blood pumping assembly, comprising:

the device comprises a barrel body with a storage cavity and a pumping mechanism partially and longitudinally penetrating through the barrel body;

the pumping mechanism includes:

the blood input tube and the blood output tube are formed at two ends of the cylinder body and are communicated with the storage cavity;

the blood input tube and the blood output tube respectively form an input one-way valve and an output one-way valve which are exposed at two ends of the cylinder body, the input one-way valve supplies blood to flow into the storage cavity, the output one-way valve supplies the blood in the storage cavity to be discharged, and the input one-way valve and the output one-way valve are alternatively opened or closed.

2. The interventional blood pumping assembly of claim 1, wherein the pumping mechanism further comprises:

the blood transfusion device comprises a blood output pipe, a cylinder body and a blood input pipe, wherein the blood output pipe, the cylinder body and the blood input pipe are continuously penetrated through by the blood output pipe, the cylinder body and the blood input pipe, at least one saccule which is nested in the catheter and is formed in the storage cavity to expand or contract, and an extracorporeal control device which is communicated with the catheter and is used for conveying working fluid.

3. The interventional blood pumping assembly of claim 2, wherein the catheter is configured with a flow channel in communication with the extracorporeal control device and a through-hole communicating the flow channel with the balloon;

the extracorporeal control device drives working fluid to pass through the through hole to realize injection or extraction in the balloon, so that the balloon is switched between an expansion state and a contraction state in the storage cavity.

4. The interventional blood pumping assembly of claim 2, wherein a lead is disposed within the catheter for controlling the input and output check valves to open or close.

5. The interventional blood pumping assembly of claim 4, wherein the output check valve is closed and the balloon is deflated when the input check valve is in an open state to allow blood to flow into the storage lumen through the input check valve.

6. The interventional blood pumping assembly of claim 4, wherein the output check valve is in an open state and the balloon is in an expanded state when the input check valve is in a closed state to expel blood from the storage lumen through the output check valve.

7. The interventional blood pumping assembly of claim 6, wherein the balloon is intermittently injected with a working fluid and gradually expands the balloon during the injection of the working fluid to expand the balloon to fill the storage lumen.

8. The interventional blood pumping assembly of claim 2, wherein the catheter extends into a ventricular-formed end set pressure sensor.

9. The interventional blood pumping assembly of any one of claims 1 to 8, wherein the barrel is configured as a rigid cylindrical hollow barrel;

the cylinder body is configured to be a combination of a high polymer material and a shape memory alloy bracket, the high polymer is polytetrafluoroethylene, polyethylene and polyamide, and the shape memory alloy is nickel-titanium alloy.

10. A method of pumping an interventional blood pumping assembly according to any one of claims 2-9, comprising the steps of:

s1, when the input one-way valve is in an open state and the output one-way valve is in a closed state, the extracorporeal control device pumps out working fluid in the saccule to enable the saccule to contract and enable the storage cavity to generate negative pressure so as to pump blood in the heart chamber through the input one-way valve;

and S2, when the input one-way valve is in a closed state and the output one-way valve is in an open state, the extracorporeal control device injects working fluid into the balloon so as to expand the balloon and discharge the blood in the storage cavity into the aorta through the output one-way valve.

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