CN114209977A - Intracardiac pump, ventricular assist system and method for operating intracardiac assist system - Google Patents

Abstract

The invention relates to a medical apparatus, and particularly discloses an intracardiac pump, which comprises a first balloon (103) and a first catheter (101) connected with the first balloon (103) in a sealing manner, wherein a plurality of first fluid channels (102) are arranged on the first catheter (101), each first fluid channel (102) is positioned in the first balloon (103), and fluid is suitable for being input into or output from the first balloon (103) through the first catheter (101) and each first fluid channel (102). In addition, the invention also discloses a ventricular assist system and an operation method of the intracardiac assist system. The intracardiac pump has the advantages of simple structure, safe use and good use effect.

Description

Intracardiac pump, ventricular assist system and method for operating intracardiac assist system

Technical Field

The present invention relates to medical devices, and in particular, to an intracardiac pump. In addition, the invention also relates to a ventricular assist system and an operation method of the intracardiac assist system.

Background

After cardiac surgery, low cardiac output syndrome is one of the common complications, and after the low cardiac output syndrome occurs, large-dose drug treatment and/or instrument auxiliary treatment (including aortic balloon counterpulsation, ventricular assist devices, extracorporeal membrane oxygenation and the like) are generally required. In addition, in the operation process of the high-risk coronary heart disease, the heart may stop jumping at any time, so that the terminal visceral organs are seriously affected, and a ventricular assist device is required to be added, so that the success rate of the operation is increased. In addition, surgical revascularization also requires the addition of instruments to assist in increasing cardiac output.

The existing ventricular assist device generally comprises an external control device and a catheter, wherein the catheter reversely enters a ventricle through a femoral artery puncture cannula, the front end of the catheter is placed below an aortic valve and is provided with a cage-shaped blood inflow port, the catheter is positioned on an ascending aorta section and is provided with a blood outflow port, a built-in micro axial-flow pump is arranged between the inflow port and the outflow port and is connected with an external controller through a built-in lead, blood is extracted from a left chamber and is pumped into the ascending aorta through the micro axial-flow pump to establish a ventricular-ascending aorta drainage path, however, due to the complex mechanical structure of the axial-flow pump, the blood is easy to adhere in the using process and the thrombus is easy to occur; in addition, the high-speed rotation of the axial flow pump fluid wheel easily destroys blood cells, and causes hemolysis. The aortic pulsation balloon counterpulsation in the prior art has small auxiliary effect on increasing the cardiac output.

Therefore, an intracardiac pump is needed to be designed, so that the cardiac muscle burden is reduced, the cardiac output is increased, and hemolysis and thrombosis complications are reduced for the condition that the cardiac output is low during or after an operation such as high-risk coronary heart disease, acute myocardial infarction, heavy surgical blood transportation and the like.

Disclosure of Invention

In view of this, the first aspect of the present invention is to provide an intracardiac pump, which has a simple structure, is easy and convenient to operate, and has a good use effect.

In addition, the technical problem to be solved by the second aspect of the present invention is to provide a ventricular assist system, which has a simple structure, is convenient to operate, and has a good use effect.

Further, the technical problem to be solved by the third aspect of the present invention is to provide an operation method of an intracardiac assist system, which has simple operation steps and good effect.

In order to solve the above technical problems, a first aspect of the present invention provides an intracardiac pump, including a first balloon and a first conduit hermetically connected to the first balloon, the first conduit being provided with a plurality of first fluid channels, each of the first fluid channels being located in the first balloon, and a fluid being adapted to be input into or output from the first balloon through the first conduit and each of the first fluid channels.

The first balloon and the second catheter are connected with each other in a sealing mode, and the first catheter is provided with a plurality of first fluid channels, and each first fluid channel is located in the first balloon.

Preferably, the second conduit is sleeved outside the first conduit; or the first conduit is sleeved outside the second conduit; or the first guide pipe and the second guide pipe are arranged in parallel, and the cross sections of the first guide pipe and the second guide pipe are formed into mutually matched semi-circles.

More preferably, the first balloon has a diastolic volume of 10-45 ml.

Further, the first balloon is a cylindrical balloon or a shaped balloon.

In addition, the second aspect of the present invention further provides a ventricular assist system, comprising a main machine and the intracardiac pump according to any one of the technical solutions of the first aspect, wherein the main machine is connected with the intracardiac pump, the main machine comprises a first fluid pump connected with the first conduit and a control device, and the first fluid pump is suitable for inputting and outputting fluid into and out of the first balloon through the first conduit so as to enable the first balloon to expand and contract.

As a specific structural form of the present invention, the internal pump further includes a second balloon and a second conduit hermetically connected to the second balloon, the second conduit is provided with a plurality of second fluid channels, each second fluid channel is located in the second balloon, the host further includes a second fluid pump connected to the second conduit, and the second fluid pump can input or output fluid into or out of the second balloon through the second conduit.

Furthermore, the second conduit is sleeved outside the first conduit; or the first conduit is sleeved outside the second conduit; or the first conduit and the second conduit are arranged in parallel, and the cross sections of the first conduit and the second conduit are formed into mutually matched semi-circles.

More specifically, the first fluid pump and the second fluid pump are gas pumps or brine pumps.

As another specific structural form of the present invention, the present invention further includes a heartbeat detection device, the control device is connected to the heartbeat detection device, the heartbeat detection device can detect heartbeat information and feed back the heartbeat information to the control device, and the control device can control the first fluid pump and the second fluid pump according to the feedback information of the heartbeat detection device.

More specifically, the heartbeat detection device is an electrocardiogram patch or a pulse measurement device.

Further, the third aspect of the present invention also provides an operation method of the intracardiac auxiliary system, comprising the steps of:

s1, retrograde advancing a first catheter along the aorta into the aortic arch, and passing a first balloon communicating with the first catheter through the aortic valve into the left ventricle; or

Simultaneously advancing a second catheter, associated with the first catheter, into the aorta, wherein a first balloon in communication with the first catheter is advanced through the aortic valve into the left ventricle, and a second balloon in communication with the second catheter is advanced into the aorta of the heart;

s2, setting a heartbeat detection device: the heartbeat detection device is in signal connection with the control device, and the first capsule body is controlled to expand and contract independently or simultaneously by the detected heartbeat information.

Through the technical scheme, the invention has the following beneficial effects:

according to the intracardiac pump, the closed and telescopic first capsule body is arranged in the heart chamber, and when the heart chamber contracts, the first capsule body is controlled to relax, so that the volume of the heart chamber at the end of systole is reduced, and the heart discharge capacity is improved; when the ventricle relaxes, the first capsule body is controlled to contract to generate negative pressure, so that the pressure of the left atrium is reduced, and the oxygen consumption of the cardiac muscle is further reduced. And the principle of pumping blood of the intracardiac pump of the invention is the same as the heart, will not destroy the erythrocyte structure, reduce the risk that haemolysis and thrombus complication happen effectively.

Additional features and advantages of the invention will be set forth in the detailed description which follows.

Drawings

The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description serve to explain the principles of the invention and not to limit the invention. In the drawings:

FIG. 1 is a schematic diagram of a first embodiment of a ventricular assist system of the present invention;

FIG. 2 is a schematic diagram of a second embodiment of the ventricular assist system of the present invention;

FIG. 3 is a schematic structural view of a first bladder of a first embodiment of the intracardiac pump of the present invention in a deflated state;

FIG. 4 is a schematic structural view of a first bladder of a first embodiment of the intracardiac pump of the present invention in an expanded state;

FIG. 5 is a schematic structural view of a second embodiment of an intracardiac pump of the present invention with the first balloon in a deflated state and the second balloon in an inflated state;

FIG. 6 is a schematic structural view of a first embodiment of an intracardiac pump of the present invention with the first balloon in an expanded state and the second balloon in a contracted state;

FIG. 7 is one of the schematic structural views of one embodiment of the first and second conduits of the present invention;

FIG. 8 is a second schematic structural view of an embodiment of the first and second conduits of the present invention;

fig. 9 is a third schematic structural view of an embodiment of the first and second conduits of the present invention.

Description of the reference numerals

10 host 11 first fluid pump

12 controlling means 20 heartbeat detecting device

30 human 100 heart pump

101 first conduit 102 first fluid passageway

103 first capsule 104 second capsule

105 second fluid passage 107 second conduit

301 left ventricle 302 atrioventricular valve

303 aortic valve 304 left atrium

305 pulmonary vein 306 pulmonary vein

Detailed Description

The following detailed description of embodiments of the invention refers to the accompanying drawings. It should be understood that the detailed description and specific examples, while indicating the present invention, are given by way of illustration and explanation only, not limitation.

In the description of the present invention, it should be noted that, unless otherwise explicitly stated or limited, the terms "mounted," "disposed" or "connected" are to be construed broadly, e.g., the term "connected" may be a fixed connection, a detachable connection, or an integral connection; either directly or indirectly through intervening media, either internally or in any combination thereof. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

The present invention will be described in detail below with reference to the accompanying drawings in conjunction with embodiments.

As shown in fig. 3 and 4, a first aspect of the present invention provides an intracardiac pump, including a first balloon 103 and a first catheter 101 hermetically connected to the first balloon 103, the first catheter 101 being provided with a plurality of first fluid channels 102, each first fluid channel 102 being located in the first balloon 103, and a fluid being adapted to be input to or output from the first balloon 103 through the first catheter 101 and each first fluid channel 102.

In the intracardiac pump of the present invention, the first balloon 103 is preferably formed of a stretchable film material, so that the first balloon 103 has good relaxation and contraction effects. The first balloon 103 is connected to the first catheter 101, and the first catheter 101 is provided with a plurality of first fluid channels 102 so as to input fluid in the first catheter 101 into the first balloon 103 or output fluid in the first balloon 103, thereby enabling the first balloon 103 to expand or contract. The first balloon 103 is arranged in the left ventricle 301, when the left ventricle 301 contracts, the first balloon 103 expands, so that the volume of the left ventricle 301 in the end systole is smaller than that when the first balloon 103 is not arranged, and the heart beat volume can be improved; when the left ventricle 301 is in diastole, the first capsule 103 contracts, the left ventricle 301 generates negative pressure, the pressure of the left atrium is reduced, the oxygen consumption of the myocardium is further reduced, the structure is simple, and the using effect is very good.

The first fluid channels 102 of the present invention are used for fluid to flow between the first catheter 101 and the first balloon 103, and therefore, the first fluid channels 102 are preferably open-cell structures on the first catheter 101, and each first fluid channel 102 is disposed on a front end sidewall of the first catheter 101 and is spaced along the length direction of the first catheter 101, and each first catheter 101 is disposed inside the first balloon 103 so as to enable fluid to be pumped into or out of the first balloon 103 through the first catheter 101. The number and the opening diameter of the first fluid channels 102 are determined according to the time of pumping the fluid, and the spaced first fluid channels 102 can make the response speed of the relaxation or contraction of each part on the first balloon 103 basically the same.

As shown in fig. 5 and 6, the intracardiac pump of the present invention further comprises a second balloon 104 and a second conduit 107 hermetically connected to the second balloon 104, wherein the second conduit 107 is provided with a plurality of second fluid channels 105, and each second fluid channel 105 is located in the second balloon 104. The second balloon 104 is arranged at the aorta and functions to help even replace the aortic valve 303 when the aortic valve 303 is not functioning properly, further helping the heart to pump in or out blood.

More preferably, the second conduit 107 is sleeved outside the first conduit 101, and the second conduit 107 is provided with a plurality of second fluid channels 105, and each second fluid channel 105 is located in the second balloon 104. As shown in fig. 7, when the second conduit 107 is sleeved outside the first conduit 101, the end of the second conduit 107 is connected to the first conduit 101 in a sealing manner, and the second fluid channel 105 is preferably an open structure.

Optionally, the first conduit 101 is sleeved outside the second conduit 107, the second conduit 107 is provided with a plurality of second fluid channels 105, and each second fluid channel 105 is located in the second balloon 104. As shown in fig. 8, when the first conduit 101 is sleeved outside the second conduit 107, a gap is formed between the first conduit 101 and the second conduit 107, and in order to prevent the fluid in the second conduit 107 from affecting the fluid in the first conduit 101, the second fluid channel 105 is preferably a gas channel connected between the first conduit 101 and the second conduit 107.

Alternatively, the first conduit 101 and the second conduit 107 are juxtaposed, both being formed in cross-section in matching semi-circles. As shown in fig. 9, when the first conduit 101 and the second conduit 107 are arranged in parallel, they do not interfere with each other, and therefore, the second fluid channel 105 is preferably of an open structure. The surfaces of the first conduit 101 and the second conduit 107 abutting each other may be formed as an integral connection or may be connected by gluing.

The structural forms of the first conduit 101 and the second conduit 107 are not limited to the three structural forms, but the first conduit 101 is sleeved outside the second conduit 107, the front end of the second conduit 107 is provided with a plurality of second fluid channels 105, the first conduit 101 and the second conduit 107 are eccentrically arranged, the second fluid channels 105 are arranged on the eccentric side walls of the first conduit 101 and the second conduit 107, the first conduit 101 and the second conduit 107 are formed into an internally tangent structure, and the second fluid channels 105 are arranged at the tangent position.

As another preferred embodiment of the present invention, the first balloon 103 has a diastolic volume of 10-45 ml. The average heart rate of a normal adult is 75 beats/min, and the amount of auxiliary pump blood that can be provided by the first capsule 103 is 750ml to 3375 ml. The first capsule 103 of the present invention can provide up to 60% of the heart's pumping volume, as calculated on average 4L-5L/min of normal human pumping volume.

As a further preferred embodiment of the present invention, the first balloon 103 is a cylindrical balloon or a shaped balloon. It should be noted that the cylindrical balloon means a structure formed as a cylindrical balloon when the first balloon 103 is in the diastolic state. In the actual use process, the irregular capsule body with the same or similar internal shape as the ventricle in contraction can be selected according to the difference of the specific structure and the use position in the ventricle, so that the inner wall of the ventricle is attached to the outer peripheral surface of the first capsule body 103 as much as possible in contraction of the ventricle, and the displacement is effectively improved.

In addition, the second aspect of the present invention also provides a ventricular assist system comprising a host 10 and an intracardiac pump 100 according to any one of claims 1 to 5, the host 10 being connected to the intracardiac pump 100, the host 10 comprising a first fluid pump 11 connected to a first conduit 101 and a control device 12, the first fluid pump 11 being adapted to input and output fluid into and from a first balloon 103 through the first conduit 101 to enable expansion and contraction of the first balloon 103.

Taking the left ventricle 301 as an example, the present invention includes a main machine 10 and an intracardiac pump 100, wherein the intracardiac pump 100 includes a closed and retractable first balloon 103 disposed in the left ventricle 301 and a first catheter 101 hermetically connected to the first balloon 103, and the other end of the first catheter 101 extends to the outside of the body. When the left ventricle 301 contracts, the first balloon 103 relaxes, so that the overall volume of the left ventricle 301 at the end of the systolic phase decreases; when the ventricle 301 is in diastole, the first capsule 103 begins to contract to generate negative pressure, so that blood in the left atrium 304 can flow into the left ventricle 301, the pressure of the left atrium 304 is reduced, oxygen consumption of cardiac muscle is reduced, and the blood discharge of the heart is improved. The working principle of pumping blood by the ventricular assist system is the same as that of pumping blood by the heart, so that the structure of red blood cells in the blood cannot be damaged in the working process of the ventricular assist system, the occurrence probability of hemolysis and thrombosis complications is effectively reduced, and the ventricular assist system is simple in structure and good in using effect.

In the ventricular assist system of the present invention, the heart beat detection device 20 can detect the contraction and relaxation of the ventricle, so as to provide a trigger signal for the contraction and relaxation of the first balloon 103.

A first embodiment of the ventricular assist system of the present invention is specifically described with reference to fig. 1 to 4: the intracardiac pump 100 comprises a main machine 10 and an intracardiac pump 100 connected with the main machine 10, wherein the intracardiac pump 100 comprises a first capsule 103 and a first conduit 101 connected with the first capsule 103, the main machine 10 comprises a first fluid pump 11 and a control device 12 which are connected with the first conduit 101, and the first fluid pump 11 is a gas pump. Taking the intracardiac pump 100 as an example, arranged in the left ventricle 301, the control device 12 is able to control the first fluid pump 11 to pump gas into the first balloon 103 when the first balloon 103 is contracted, so that the first balloon 103 is expanded; the control means 12 is also able to control the first fluid pump 11 to pump gas from the first balloon 103 at ventricular diastole, such that the first balloon 103 contracts.

The first embodiment of the ventricular assist system operates as follows: first, a puncture is made in the femoral artery, the first catheter 101 is advanced retrograde along the aorta into the aortic arch, and the first balloon 103 is advanced through the aortic valve 303 into the left ventricle 301. At this time, the initial state of the first balloon 103 is shown in fig. 3, where the ventricle is in a diastolic state and the volume in the ventricle is maximum. Next, when it is detected that the left ventricle 301 starts to contract, the volume in the left ventricle 301 gradually decreases, the atrioventricular valve 302 starts to close, the aortic valve 303 starts to open, and the blood in the ventricle flows in the direction of the aorta. At the same time, the first fluid pump 11 pumps gas from the first fluid channel 102 through the first conduit 101 outside the body into the first balloon 103, and the first balloon 103 begins to expand, further reducing the volume in the left ventricle 301, effectively increasing the displacement of blood from the left ventricle 301 into the aorta. The volume of the first balloon 103 reaches a maximum when the ventricle contracts to a minimum, while the volume in the left ventricle 301 is at a minimum throughout the cycle. Next, the ventricles begin to relax, the volume in the left ventricle 301 gradually increases, the atrioventricular valve 302 begins to open, the aortic valve 303 begins to close, a partial vacuum is created in the ventricles, and blood flows from the pulmonary veins 301 into the left atrium 304. At the same time, the first balloon 103 contracts rapidly, again creating a partial vacuum, reducing the left atrial load. Finally, the ventricle relaxes to the state of fig. 3 and the first balloon 103 contracts to the initial state, and a work cycle is completed.

As a specific configuration of the present invention, the intracardiac pump 100 further includes a second balloon 104 and a second conduit 107 hermetically connected to the second balloon 104, the second conduit 107 is provided with a plurality of second fluid channels 105, each second fluid channel 105 is located in the second balloon 104, the host 10 further includes a second fluid pump connected to the second conduit 107, and the second fluid pump is capable of inputting or outputting fluid into or from the second balloon 104 through the second conduit 107.

A second embodiment of the invention is described with reference to fig. 5 and 6: comprises a main machine 10 and an intracardiac pump 100 connected with the main machine 10, wherein the intracardiac pump 100 comprises a first capsule 103, a first catheter 101 connected with the first capsule 103, a second capsule 104 and a second catheter 107 connected with the second capsule 104, the first catheter 101 passes through the second capsule 104, and the second capsule 104 is arranged at the aorta; the main unit 10 comprises a first fluid pump 11 connected to the first conduit 101, a second fluid pump connected to the second conduit 107, and a control device 12, the first fluid pump 11 and the second fluid pump being each a gas pump. Taking the intracardiac pump 100 as an example, arranged in the left ventricle 301, the control device 12 is able to control the first fluid pump 11 to pump gas into the first balloon 103 when the first balloon 103 is contracted, so that the first balloon 103 is expanded; the control device 12 can also control the first fluid pump 11 to pump gas out of the first capsule 103 when the ventricle is in diastole, so that the first capsule 103 is contracted, and simultaneously control the second fluid pump to pump gas into the second capsule 104, thereby effectively solving the problem that the aortic valve 303 is not closed completely when the first catheter 101 passes through the aortic valve 303, and avoiding partial aortic blood flowing back into the left ventricle 301 during diastole, which causes the ventricular blood drawing pressure to be reduced, and further influencing the cardiac blood discharge. In the second embodiment of the present invention, while the ventricle is diastolic, the second balloon 104 is controlled to close the aorta, so as to prevent the decrease of the blood flow of the heart caused by the insufficiency or the loss of the function of the aortic valve 303 due to the first catheter 101 passing through the aortic valve 303, and both of them are performed simultaneously, thereby ensuring the normal blood drainage function of the heart.

It should be noted that the first fluid pump 11 and the second fluid pump may be two independent pump bodies, or may be configured as one pump body, and cooperate with corresponding control switches, so as to control the normal operation of the first capsule 103 and the second capsule 104 simultaneously.

The operation of the second embodiment of the ventricular assist system is: first, as shown in fig. 5, the intracardiac pump 100 is in an initial state, in which the first balloon 103 is in a contracted state with a minimum volume and the second balloon 104 is in a relaxed state with a maximum volume; next, before the aortic valve 303 is opened, the second balloon 104 contracts rapidly, and the volume contracts to the minimum state, in this state, the atrioventricular valve 302 is closed, the left ventricle begins to contract, the volume in the left ventricle 301 decreases gradually, the aortic valve 303 is opened, at this time, the blood in the left ventricle 301 flows towards the aorta, and at the same time, the first balloon 103 begins to relax, the volume in the left ventricle 301 further decreases, the flow of the blood in the left ventricle 301 towards the aorta continues to increase, when the volume of the left ventricle 301 contracts to the minimum, the volume of the first balloon 103 relaxes to the maximum as shown in fig. 6; immediately following closure of the aortic valve 303, the second balloon 104 relaxes and rapidly reaches its maximum volume, engaging the aortic wall, closing the aorta, the left ventricle 301 begins to relax, the atrioventricular valve 302 opens, a partial vacuum is created in the left ventricle 301 and blood begins to flow from the pulmonary veins 305 and 306 into the left atrium 304. At the same time, the first balloon 103 of the intracardiac pump 100 contracts rapidly, further increasing the volume in the left ventricle 301 and increasing the inflow of blood.

The operation of the first capsule 103 in the second embodiment of the present application is the same as that of the first capsule 103 in the first embodiment, and a second capsule 104 is added to the first embodiment, and the operation of the second capsule 104 is as follows: when the heart is in a diastolic state, due to the influence of the first catheter 101, the aortic valve 303 may be under the condition of incomplete closure, at this time, gas is pumped into the second capsule 104 through the second fluid pump, so that the second capsule 104 is expanded to close the aorta, and replace the function of the aortic valve 303, so that the condition that blood flows back into the left ventricle 301 due to incomplete closure of the aortic valve 303 is avoided when the blood is in the diastolic state, and the blood drawing pressure of the left ventricle 301 is prevented from being reduced to influence the cardiac blood discharge.

More specifically, the first fluid pump 11 and the second fluid pump are gas pumps or brine pumps.

As another specific structural form of the present invention, a heartbeat detection device 20 is further included, the control device 12 is connected to the heartbeat detection device 20, the heartbeat detection device 20 can detect heartbeat information and feed back the heartbeat information to the control device 12, and the control device 12 can control the first fluid pump 11 and the second fluid pump according to the feedback information of the heartbeat detection device 20.

More specifically, the heartbeat detecting device 20 is an electrocardiograph patch or a pulse measuring device.

The ventricular assist system of the present invention detects the contraction and relaxation of the ventricle by the heartbeat detecting device 20. The heartbeat detecting device 20 can be an external device, such as an electrocardiograph detecting device, a pulse measuring device, etc. The heartbeat detecting device 20 controls the first fluid pump 11 or the second fluid pump to pump fluid into or out of the first capsule 103 or the second capsule 104 respectively according to the detected heartbeat information.

The third aspect of the present invention also provides an operation method of the intracardiac assist system, comprising the steps of:

s1, retrograde advancing the first catheter 101 along the aorta into the aortic arch, the first balloon 103 passing through the aortic valve 303 into the left ventricle 301; or

The second catheter 107 is retrograde along the aorta simultaneously with the first catheter 101, the first balloon 103 passes through the aortic valve 303 into the left ventricle 301, and the second balloon 104 is positioned at the aorta of the heart;

s2, setting the heartbeat detecting device 20: the heartbeat detecting device 20 is connected with the control device 12 by signals, and the detected heartbeat information can control the first capsule 103 independently or control the expansion and contraction of the first capsule 103 and the second capsule 104 simultaneously. When the left ventricle 301 starts to contract, the first fluid pump 11 pumps fluid into the first balloon 103 through the first catheter 101, and when the left ventricle 301 starts to relax, the first fluid pump 11 pumps fluid into the first balloon 103 through the first catheter 101; if insufficient pressure is detected in the left ventricle 301 during diastole, the second fluid pump pumps fluid through the second conduit 107 into the second balloon, which then seals off the aorta after diastole.

As can be seen from the above technical solutions, the ventricular assist system of the present invention includes a first balloon 103 and a first catheter 101 hermetically connected to the first balloon 103, the first catheter 101 is provided with a plurality of first fluid channels 102, each first fluid channel 102 is located in the first balloon 103, and fluid is suitable for being input into or output from the first balloon 103 through the first catheter 101 and each first fluid channel 102. The intracardiac pump of the invention sets up the first utricule 103 in the left ventricle 301, in the course of contraction or relaxation of the left ventricle 301, the first utricule 103 is synchronous to relax or contract, enhance the function of pumping blood of the heart, and because its working principle is the same as the working principle of the heart, will not destroy the erythrocyte structure in the course of using, and then reduce the risk that hemolysis and thrombus complication take place effectively.

The preferred embodiments of the present invention have been described in detail with reference to the accompanying drawings, however, the present invention is not limited to the specific details of the above embodiments, and various simple modifications can be made to the technical solution of the present invention within the technical idea of the present invention, and these simple modifications are within the protective scope of the present invention.

It should be noted that the various features described in the above embodiments may be combined in any suitable manner without departing from the scope of the invention. The invention is not described in detail in order to avoid unnecessary repetition.

In addition, any combination of the various embodiments of the present invention is also possible, and the same should be considered as the disclosure of the present invention as long as it does not depart from the spirit of the present invention.

Claims (12)

1. An intracardiac pump comprising a first balloon (103) and a first catheter (101) sealingly connected to said first balloon (103), said first catheter (101) being provided with a plurality of first fluid channels (102), each of said first fluid channels (102) being located within said first balloon (103), fluid being adapted to be delivered to or from said first balloon (103) through said first catheter (101) and each of said first fluid channels (102).

2. The intracardiac pump according to claim 1, wherein the diastolic volume of the first balloon (103) is 10-45 ml.

3. The intracardiac pump according to claim 1, wherein the first balloon (103) is a cylindrical balloon or a shaped balloon.

4. An intracardiac pump according to any one of claims 1 to 3, further comprising a second balloon (104) and a second conduit (107) sealingly connected to said second balloon (104), said second conduit (107) being provided with a plurality of second fluid channels (105), each of said second fluid channels (105) being located within said second balloon (104).

5. An intracardiac pump according to claim 4, wherein the second conduit (107) is externally sleeved to the first conduit (101); or

The first conduit (101) is sleeved outside the second conduit (107); or

The first conduit (101) and the second conduit (107) are arranged in parallel, and the cross sections of the first conduit and the second conduit are formed into mutually matched semi-circles.

6. A ventricular assist system comprising a host (10) and an intracardiac pump (100) according to any one of claims 1 to 3, the host (10) being connected to the intracardiac pump (100), the host (10) comprising a first fluid pump (11) connected to the first conduit (101) and a control device (12), the first fluid pump (11) being adapted to input and output fluid into and from the first balloon (103) through the first conduit (101) to enable expansion and contraction of the first balloon (103).

7. A ventricular assist system as claimed in claim 6, wherein the intracardiac pump (100) further comprises a second balloon (104) and a second conduit (107) sealingly connected to the second balloon (104), the second conduit (107) being provided with a plurality of second fluid channels (105), each second fluid channel (105) being located within the second balloon (104), the host (10) further comprising a second fluid pump connected to the second conduit (107), the second fluid pump being capable of inputting or outputting fluid into or out of the second balloon (104) through the second conduit (107).

8. A ventricular assist system according to claim 7, wherein the second catheter (107) is sleeved outside the first catheter (101); or

The first conduit (101) is sleeved outside the second conduit (107); or

The first conduit (101) and the second conduit (107) are arranged in parallel, and the cross sections of the first conduit and the second conduit are formed into mutually matched semi-circles.

9. A ventricular assist system according to claim 7, characterized in that the first fluid pump (11) and the second fluid pump are gas pumps or saline pumps.

10. A ventricular assist system according to any one of claims 7 to 9, further comprising a heartbeat detection device (20), the control device (12) being connected to the heartbeat detection device (20), the heartbeat detection device (20) being capable of detecting heartbeat information and feeding back to the control device (12), the control device (12) being capable of controlling the first fluid pump (11) and the second fluid pump in accordance with feedback information of the heartbeat detection device (20).

11. A ventricular assist system according to claim 10, wherein the heartbeat detection device (20) is a cardiac electrical patch or a pulse measurement device.

12. A method of operating an intracardiac assist system, comprising the steps of:

s1, retrograde advancing the first catheter (101) along the aorta into the aortic arch and passing a first balloon (103) in communication with the first catheter (101) through the aortic valve (303) into the left ventricle (301); or

Retrograde tracing a second catheter (107) along the aorta simultaneously with the first catheter (101), wherein a first balloon (103) communicating with the first catheter (101) is passed through the aortic valve (303) into the left ventricle (301), and a second balloon (104) communicating with the second catheter (101) is provided at the aorta of the heart;

s2, setting a heartbeat detection device (20): the heartbeat detection device (20) is in signal connection with the control device (12), and the first capsule (103) is controlled to expand and contract independently or the first capsule (103) and the second capsule (104) are controlled to expand and contract simultaneously through detected heartbeat information.

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