CN113509639A

CN113509639A - Aortic heart pump auxiliary device

Info

Publication number: CN113509639A
Application number: CN202110622876.XA
Authority: CN
Inventors: 曾建新; 罗建方
Original assignee: Shenzhen Maiteng Medical Technology Co ltd
Current assignee: Shenzhen Maiteng Medical Technology Co ltd
Priority date: 2021-06-03
Filing date: 2021-06-03
Publication date: 2021-10-19

Abstract

The invention relates to the technical field of medical instruments, in particular to an aortic heart pump auxiliary device, which comprises: the combined bag comprises an inner bag, a middle bag and an outer bag which are sequentially connected in series, the combined catheter comprises an inner bag tube, a middle bag tube and an outer bag tube which are arranged in parallel, and the controller is connected with the outer pump and is used for controlling the outer pump to sequentially inflate the inner bag tube, the middle bag tube and the outer bag tube during diastole so as to sequentially expand the combined bag from the far end to the near end, and sequentially deflate the inner bag tube, the middle bag tube and the outer bag tube during systole so as to sequentially contract the combined bag from the far end to the near end. This patent adopts combination bag and combination pipe, makes the combination bag can realize easily that it expands or contracts in proper order from the gasbag distal end to near-end to it is bigger to the drive effect of blood to whole body blood supply perfusion in the drive aorta when making the combination bag inflation, and it is also bigger to the suction effect of heart bloodletting when making the combination bag shrink.

Description

Aortic heart pump auxiliary device

Technical Field

The invention relates to the technical field of medical instruments, in particular to an aortic heart pump auxiliary device.

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. Heart failure is not an independent disease but the terminal stage of progression of heart disease. Most of these heart failures begin with left heart failure, which manifests itself primarily as pulmonary circulation congestion. The survival rate of the heart failure treatment drug for two years is about 80 percent, and the survival rate for five years is only about 50 percent. The treatment of heart failure must seek a breakthrough to save a large number of people who die frequently.

The principle of the aorta internal bag counterpulsation (IABP) is that a slender air bag is arranged at the near end of a descending aorta and is connected with an external pump through a catheter, when the heart is in diastole, the external pump quickly pumps air into the air bag to expand the air bag to occupy the blood space in the aorta, and the expanded air bag is quickly expanded due to the closing of an aortic valve, so that the blood supply perfusion of the whole body is increased, the diastolic pressure is increased, the circulation is supported, the work load of the heart, particularly the left ventricle, is greatly reduced, and the blood supply is greatly improved; when the heart contracts, the external pump quickly sucks gas to enable the air bag to contract, so that the aortic pressure is instantaneously reduced, the left ventricular ejection resistance of the heart, namely the afterload of the heart is reduced, the cardiac blood discharge amount is increased (including blood is passively sucked into the main artery), the oxygen consumption of the cardiac muscle is reduced, and therefore left ventricular ejection is increased. Here, the control unit may adjust the size of the airbag by controlling the amount of gas introduced into the airbag.

In the conventional aortic inner bag counterpulsation, the expansion process and the contraction process of an air bag of the conventional aortic inner bag counterpulsation are uniformly carried out, namely, the whole air bag is uniformly expanded or contracted and cannot or cannot be sequentially expanded or contracted from the far end to the near end of the air bag, so that the driving effect of driving the blood in the aorta to the whole body blood supply perfusion is insufficient when the air bag is expanded, and the suction effect of the air bag on heart blood discharge is insufficient when the air bag is contracted.

Disclosure of Invention

In order to overcome the defects in the prior art, the invention provides an aortic heart pump auxiliary device, which is characterized in that on the basis of the prior aortic inner bag counterpulsation technology, a unique structural design is adopted for a balloon and a catheter, and a combined balloon and a combined catheter are adopted, so that the combined balloon can be sequentially expanded or contracted from the far end to the near end of the combined balloon easily in the expansion or contraction process, and the combined balloon has a larger driving effect on driving the blood in the aorta to the whole body blood supply perfusion when expanded, can promote the whole body blood supply perfusion, has a larger suction effect on heart blood discharge when contracted, and can promote the flow of left ventricle blood to the aorta.

The task of the invention is realized by the following technical scheme:

an aortic heart pump assist device comprising: the combined capsule is placed in an aorta when in use, and comprises at least three independent soft capsules which are connected in series in sequence, wherein the inner capsule is positioned at the far end, the outer capsule is positioned at the near end, and the middle capsule is positioned between the inner capsule and the outer capsule; the combined catheter comprises a plurality of independent catheters which are in one-to-one correspondence with the independent soft capsules, wherein an inner capsule tube is introduced into the inner capsule, an outer capsule tube is introduced into the outer capsule, and a middle capsule tube is introduced into the middle capsule; the external pump is connected with each independent conduit and can fill or extract fluid into or from the corresponding independent soft bag through each independent conduit, and the fluid is gas or liquid; and the controller is connected with the external pump and is used for controlling the external pump to sequentially fill the fluid into the internal bladder tube, the middle bladder tube and the external bladder tube during diastole so as to sequentially expand the combined bladder from the far end to the near end, and sequentially pump the fluid through the internal bladder tube, the middle bladder tube and the external bladder tube during systole so as to sequentially contract the combined bladder from the far end to the near end.

As a preferred technical solution, the combination catheter is inserted from a proximal end of the combination balloon, wherein the inner balloon tube sequentially passes through the outer balloon tube and the middle balloon tube and extends into the inner balloon, the middle balloon tube passes through the outer balloon tube and extends into the corresponding middle balloon, and the outer balloon tube extends into the outer balloon.

As a preferable technical scheme, the distal end of at least one independent catheter extends to and is connected with the distal end of the corresponding independent soft sac, a plurality of perforations are arranged on the wall of the independent catheter at intervals corresponding to the independent soft sac, and the density and/or the pore size of the perforations are sequentially reduced from the distal end to the proximal end.

As a preferable technical scheme, the number of the middle bags is one, and the length of the middle bags is larger than that of the inner bags and the outer bags.

Preferably, the size of each independent soft bag when being inflated can block the blood flow of the aorta, and the size when being deflated can not obstruct the blood flow of the aorta.

As a preferable technical solution, the aortic heart pump assist device further comprises a sensor, the sensor is connected with the controller, and the sensor can monitor heart beat rhythm in real time and send data to the controller, so that the controller can control the operation of the extracorporeal pump according to the heart beat rhythm.

As a preferred technical scheme, the controller is provided with a parameter setting module, a heart normal pulsation rhythm can be preset through the parameter setting module, and when the sensor monitors the cardiac arrest, the controller can control the operation of the extracorporeal pump according to the preset heart normal pulsation rhythm.

As a preferable technical solution, the aortic heart pump assisting device further comprises a fixing stent system for positioning the combined sac in the aorta, wherein the fixing stent system comprises a stent main body, a distal net and a proximal net, the stent main body is a spiral metal wire with an elastic expansion function so as to be capable of elastically expanding and supporting on the inner wall of the aorta in a natural state, and the combined sac therein can be fixed through the distal net and the proximal net connected with the stent main body.

Preferably, the fixing support system further comprises a centering wire, the centering wire penetrates through the center of the support main body and is connected to the distal net, and each independent catheter is attached to the centering wire and extends along with the centering wire.

As a preferred technical scheme, the extracorporeal pump comprises a pump shell, at least three independent chambers are arranged in the pump shell at intervals, each independent chamber is communicated with each independent conduit in a one-to-one correspondence mode, the corresponding independent chamber, the independent conduits and the independent soft bags form a closed space, the fluid is filled in the closed space, an electromagnetic driving mechanism is arranged between any two adjacent independent chambers, each electromagnetic driving mechanism comprises a permanent magnet and electromagnets, the permanent magnets are fixedly arranged, the electromagnets are movably arranged on two sides of the permanent magnet and can reciprocate relative to the permanent magnet, the two electromagnets are respectively connected with the side walls of the independent chambers on the two sides, the electrifying time and the direction of each electromagnet can be controlled through the controller, and therefore the electromagnet is driven to reciprocate by magnetic force generated between the electromagnet and the corresponding permanent magnet so as to enable the independent chambers to contract or expand, and then the fluid is filled into or pumped out of the corresponding independent soft balloon through the corresponding independent catheter so as to expand or contract the corresponding independent soft balloon.

Compared with the prior art, the aortic heart pump auxiliary device has the advantages that on the basis of the existing aortic inner bag counterpulsation technology, the air bag and the catheter are designed in a unique structure, the combined bag and the combined catheter are adopted, so that the combined bag can be expanded or contracted from the far end to the near end of the combined bag easily in the expansion or contraction process, the driving effect on driving the blood in the aorta to the whole body blood supply perfusion is larger when the combined bag is expanded, the whole body blood supply perfusion can be promoted, the suction effect on heart blood discharge is larger when the combined bag is contracted, and the flow of the blood in the left ventricle to the aorta can be promoted.

The conception, specific structure and effects of the present invention will be further described in conjunction with the accompanying drawings to fully understand the objects, features and effects of the present invention.

Drawings

FIG. 1 is a schematic structural diagram of an aortic heart pump assist device in an embodiment;

FIG. 2 is a schematic view of the aortic heart pump assist device in an embodiment;

FIG. 3 is a schematic cross-sectional view of the combination catheter of the aortic heart pump assist device;

fig. 4 is a schematic diagram of the structure of an extracorporeal pump in an aortic heart pump assist device.

The combined type heart-protecting device comprises a combined capsule 1, an inner capsule 11, a middle capsule 12, an outer capsule 13, a combined catheter 2, an inner capsule tube 21, a middle capsule tube 22, a middle capsule tube through hole 221, an outer capsule tube 23, an outer capsule tube through hole 231, a stent main body 3, a distal net 31, a proximal net 32, a center positioning metal wire 4, an extracorporeal pump 5, a pump shell 51, an independent chamber 52, an electromagnetic driving mechanism 53, a permanent magnet 531, an electromagnet 532, an aorta 10 and a heart 20.

Detailed Description

In order to make the objects, technical solutions and advantages of the present invention more clearly apparent, the present invention will be further described in detail below by taking an intelligent medical instrument using an aortic heart pump assisting device of the present invention as an example, and with reference to the accompanying drawings. It should be understood that the description of the specific embodiments is intended to be illustrative of the invention and is not intended to limit the invention.

It should be noted that when an element is referred to as being "connected" to another element, it can be directly connected to the other element, or indirectly connected through intervening elements, or be physically, electrically, or signally connected, depending on the application.

As shown in fig. 1-4, an aortic heart pump assist device, comprising: the combined bag 1 is of a long-strip capsule-shaped structure when being expanded, is placed in an aorta 10 when being used, and comprises three independent soft bags which are sequentially connected in series, wherein the inner bag 11 is positioned at the far end, the outer bag 13 is positioned at the near end, the middle bag 12 is positioned between the inner bag 11 and the outer bag 13, and the length of the middle bag 12 is greater than that of the inner bag 11 and the outer bag 13; the combined catheter 2 comprises three independent catheters which are in one-to-one correspondence with the independent soft capsules, wherein an inner capsule tube 21 is communicated with the inner capsule 11, an outer capsule tube 23 is communicated with the outer capsule 13, and a middle capsule tube 22 is communicated with the middle capsule 12; the external pump 5 is provided with three suction ports which are respectively connected with the inner bag tube 21, the middle bag tube 22 and the outer bag tube 23 and can respectively fill or extract gas into or from the corresponding inner bag 11, the middle bag 12 and the outer bag 13 through the inner bag tube 21, the middle bag tube 22 and the outer bag tube 23; and the controller is in wired or wireless signal connection with the extracorporeal pump 5 and is used for controlling the extracorporeal pump 5 to sequentially inflate the combined bags 1 from the far end to the near end by sequentially inflating the internal bag tube 21, the middle bag tube 22 and the external bag tube 23 with air when the heart 20 is in diastole and sequentially deflate the combined bags 1 from the far end to the near end by sequentially extracting the air from the internal bag tube 21, the middle bag tube 22 and the external bag tube 23 when the heart 20 is in systole. The controller belongs to the mature prior art and is omitted in the drawing. The fluid is preferably a gas, and in other embodiments, other fluids, such as liquids, may be used. The inner bag 11, the middle bag 12 and the outer bag 13 can be formed by connecting three independent air bags together in a bonding mode or the like, or can be formed by arranging two membranes in a long air bag at intervals for separation.

The working process is as follows: when the heart 20 is in diastole, the controller controls the external pump 5 to inflate through the internal bladder tube 21 to expand the internal bladder 11, then inflate through the internal bladder tube 22 to expand the internal bladder 12, and finally inflate through the external bladder tube 23 to expand the external bladder 13, namely the expansion process of the combined bladder 1 is from the far end to the near end, so that the driving effect of driving the blood in the aorta 10 to the whole body blood supply perfusion is larger when the combined bladder 1 is expanded, and the whole body blood supply perfusion can be promoted; at the beginning of the contraction of the heart 20, the external pump 5 firstly pumps air through the inner bag tube 21 to enable the inner bag 11 to contract and deflate, then pumps air through the middle bag tube 22 to enable the middle bag 12 to contract and deflate, and finally pumps air through the outer bag tube 23 to enable the outer bag 13 to contract and deflate, namely, the contraction process of the combined bag 1 is that the combined bag contracts from the far end to the near end in sequence, when the outer bag 13 does not contract, the inner bag 11 and the middle bag 12 contract to generate negative pressure in the area where the inner bag and the middle bag are located, pressure difference is generated between the inner bag and the middle bag and the left ventricle of the heart 20, the suction effect on left ventricle ejection is larger, and left ventricle blood can be enabled to flow to the aorta 10.

Compared with the prior art, the aortic heart pump auxiliary device adopts the combined bag 1 and the combined catheter 2, so that the combined bag 1 can be easily expanded or contracted from the far end to the near end of the combined bag 1 in sequence in the expansion or contraction process, the driving effect of the combined bag 1 on driving blood in the aorta 10 to whole body blood supply perfusion is larger when the combined bag 1 is expanded, the whole body blood supply perfusion can be promoted, the suction effect on blood discharge of the heart 20 when the combined bag 1 is contracted is also larger, and the flow of left ventricle blood to the aorta 10 can be promoted.

As a preferred embodiment, the combination catheter 2 is inserted from the proximal center of the combination balloon 1, wherein the inner balloon tube 21 passes through the outer balloon tube 23 and the middle balloon tube 22 in sequence and extends into the inner balloon 11, the middle balloon tube 22 passes through the outer balloon tube 23 and extends into the middle balloon 12, and the outer balloon tube 23 extends into the outer balloon 13. The design enables the catheter to pass through the air sac instead of being arranged outside the air sac, so that the joint of the air sac and the inner wall of the aorta 10 when the air sac expands is not affected, and the auxiliary blood pumping effect of the combined sac 1 is increased.

In a preferred embodiment, the distal end of the middle sac tube 22 extends to and is connected with the distal end of the middle sac 12, a plurality of middle sac tube perforations 221 are arranged on the tube wall of the middle sac tube 22 at intervals corresponding to the part of the middle sac 12, and the density and/or the pore size of the middle sac tube perforations 221 become smaller from the distal end to the proximal end; the far end of the outer bag tube 23 extends to the far end of the outer bag 13 and is connected with the far end, the part of the tube wall of the outer bag tube 23 corresponding to the outer bag 13 is provided with outer bag tube perforations 231, and the density and/or the aperture of the outer bag tube perforations 231 are gradually reduced from the far end to the near end. The design enables the self expansion and contraction processes of the middle bag 12 and the outer bag 13 to sequentially expand or contract from the far end to the near end, and further increases the auxiliary blood pumping effect of the combined bag 1.

As a preferred embodiment, each individual balloon is sized to inflate to occlude aortic blood flow 10 and deflate to a size that does not interfere with aortic blood flow 10. This design may further increase the auxiliary pumping effect of the combined bag 1.

As a preferred embodiment, the length of the combined bag 1 ranges from 5cm to 25cm, preferably about 20cm, the combined bag 1 is close to the inner diameter of an aorta 10 by 3cm when the outer diameter is expanded, the combined bag can discharge more than 100ml of blood in one contraction and relaxation process, and the blood discharge amount is more than 70ml of the normal stroke amount of a heart 20, so the combined bag is also suitable for a patient with 20 arrest of the heart, and when the heart 20 is arrested, the combined bag 1 expands and contracts to promote the blood discharge of the heart 20 and deliver the blood to the whole body, and the combined bag can also meet the requirement of a human body, so that the patient can survive with high quality without symptoms.

In a preferred embodiment, the aortic heart pump assist device further comprises a sensor connected to the controller, the sensor being capable of monitoring the pulsatile rhythm of the heart 20 in real time and sending data (such as an electrocardiogram waveform) to the controller, thereby enabling the controller to control the operation of the extracorporeal pump 5 in accordance with the pulsatile rhythm of the heart 20. The sensors belong to the mature prior art and are omitted in the drawings.

In a preferred embodiment, the controller is provided with a parameter setting module, the normal beating rhythm of the heart 20 can be preset through the parameter setting module, and when the sensor monitors that the heart 20 stops beating, the controller can control the operation of the extracorporeal pump 5 according to the preset normal beating rhythm of the heart 20. The design enables the controller to assist the heart 20 to maintain normal pumping function according to the normal beating rhythm of the human heart 20 when the user's heart 20 stops jumping, preventing danger. The parameter setting module belongs to the mature prior art and is omitted in the attached drawings.

As a preferred embodiment, the aortic heart pump assist apparatus further comprises a fixing stent system for positioning the combined capsule 1 in the aorta 10, the fixing stent system comprises a stent main body 3, a distal net 31 and a proximal net 32, the stent main body 3 is a spiral wire with elastic expansion function so as to be capable of elastically expanding and supporting on the inner wall of the aorta 10 in a natural state, and the combined capsule 1 therein can be fixed by the distal net 31 and the proximal net 32 connected thereto, and the fixing stent system does not obstruct the flow of blood in the aorta 10.

As a preferred embodiment, the stent system further comprises a centering wire 4, the centering wire 4 passing through the center of the stent body 3 and connected to the distal mesh 31, and each of the individual catheters attached to and extending along the centering wire 4. The combined bag 1 can be positioned on the central axis of the stent main body 3 through the central positioning metal wire 4, so that the combined bag 1 is ensured to be positioned in the center of the aorta 10, and the expansion and contraction of the combined bag 1 can play a better blood pumping effect; and the end of the central positioning wire 4 is connected with the far end of the stent main body, so that the stent main body and the combined capsule 1 in the stent main body can be positioned and prevented from moving towards the root of the aorta 10.

As a preferred embodiment, as shown in fig. 4, the extracorporeal pump 5 includes a pump housing 51, three independent chambers 52 are arranged at intervals in the pump housing 51, each independent chamber 52 is respectively communicated with each independent conduit one by one, the corresponding independent chamber 52, independent conduit, independent soft bag form a closed space and the inside is filled with gas, an electromagnetic driving mechanism 53 is arranged between any two adjacent independent chambers 52, each electromagnetic driving mechanism 53 includes a permanent magnet 531 fixedly arranged, electromagnets 532 movably arranged at both sides of the permanent magnet 531 and capable of reciprocating relative to the permanent magnet 531 (the electromagnetic driving mechanism 53 further includes a power supply, an electric wire, etc., and is omitted in the drawing), the two electromagnets 532 are respectively connected with the side walls of the independent chambers 52 at both sides, and the controller can control the energizing time and direction of each electromagnet 532, so that the electromagnet 532 drives the electromagnet 532 to drive the corresponding independent chamber by the magnetic force generated between the electromagnet 532 and the corresponding permanent magnet 531 The side walls of the individual chambers 52 are reciprocated to contract or expand the individual chambers 52, and when the individual chambers 52 are contracted, the gas therein is extruded into the corresponding individual bladders through the corresponding individual tubes to be expanded; when the individual chambers 52 are inflated, the individual bladders are deflated by withdrawing gas from the respective individual bladders through the respective individual conduits. The external pump in the patent is provided with three independent chambers which are respectively communicated with three independent soft bags (namely an inner bag, a middle bag and an outer bag), and utilizes an electromagnetic driving mechanism, so that the expansion or contraction sequence of the inner bag, the middle bag and the outer bag can be flexibly controlled; and the extracorporeal pump has compact and small structure, is convenient to carry, is convenient for a user to use for a long time at any time and any place, and can solve the problems of heavy equipment, inconvenience in carrying and long-term use at any time and any place in the prior art. The external pump in this patent belongs to an independent technical scheme, can be used in other technical field.

The above description is only a preferred embodiment of the application and is illustrative of the principles of the technology employed. It will be appreciated by those skilled in the art that the scope of the invention herein disclosed is not limited to the particular combination of features described above, but also encompasses other arrangements formed by any combination of the above features or their equivalents without departing from the inventive concept. For example, the above features may be replaced with (but not limited to) features having similar functions disclosed in the present application.

Claims

1. An aortic heart pump assist device, comprising:

the combined capsule is placed in an aorta when in use, and comprises at least three independent soft capsules which are connected in series in sequence, wherein the inner capsule is positioned at the far end, the outer capsule is positioned at the near end, and the middle capsule is positioned between the inner capsule and the outer capsule;

the combined catheter comprises a plurality of independent catheters which are in one-to-one correspondence with the independent soft capsules, wherein an inner capsule tube is introduced into the inner capsule, an outer capsule tube is introduced into the outer capsule, and a middle capsule tube is introduced into the middle capsule;

the external pump is connected with each independent conduit and can fill or extract fluid into or from the corresponding independent soft bag through each independent conduit, and the fluid is gas or liquid;

and the controller is connected with the external pump and is used for controlling the external pump to sequentially fill the fluid into the internal bladder tube, the middle bladder tube and the external bladder tube during diastole so as to sequentially expand the combined bladder from the far end to the near end, and sequentially pump the fluid through the internal bladder tube, the middle bladder tube and the external bladder tube during systole so as to sequentially contract the combined bladder from the far end to the near end.

2. The aortic heart pump assist device of claim 1 wherein the combination catheter is inserted from a proximal end of the combination balloon with the inner balloon tube passing through the outer balloon tube and the middle balloon tube in sequence and extending into the inner balloon, the middle balloon tube passing through the outer balloon tube and extending into the corresponding middle balloon, the outer balloon tube extending into the outer balloon.

3. The aortic heart pump assist device as claimed in claim 2, wherein the distal end of at least one of the independent catheters extends to and connects with the distal end of the corresponding independent balloon, and the tube wall of the independent catheter is provided with a plurality of perforations at intervals corresponding to the independent balloon, and the density and/or pore size of the perforations become smaller from the distal end to the proximal end.

4. The aortic heart pump assist device of claim 1 wherein the number of the middle bladders is one and the length of the middle bladder is greater than the inner bladder and the outer bladder.

5. The aortic heart pump assist device of claim 1 wherein the inner balloon and the outer balloon are sized to occlude aortic blood flow when inflated and each of the independent balloons are sized to not obstruct aortic blood flow when deflated.

6. The aortic heart pump assist device of claim 1 further comprising a sensor connected to the controller, the sensor capable of monitoring heart beat rhythm in real time and sending data to the controller, thereby enabling the controller to control operation of the extracorporeal pump according to the heart beat rhythm.

7. The aortic heart pump assist device of claim 6, wherein the controller is provided with a parameter setting module, a heart normal pulsation rhythm can be preset through the parameter setting module, and when the sensor detects the cardiac arrest, the controller can control the operation of the extracorporeal pump according to the preset heart normal pulsation rhythm.

8. The aortic heart pump assist device as claimed in claim 1, further comprising a fixing stent system for positioning the combined sac in the aorta, wherein the fixing stent system comprises a stent main body, a distal net and a proximal net, the stent main body is a spiral wire with elastic expansion function so as to be capable of elastically expanding and supporting on the inner wall of the aorta in a natural state, and the combined sac therein can be fixed by the distal net and the proximal net connected thereto.

9. The aortic heart pump assist device of claim 8 wherein the fixed stent system further comprises a centering wire that passes through the center of the stent body and is attached to the distal mesh, each of the individual catheters depending from and extending with the attachment centering wire.

10. The aortic heart pump assist device according to claim 1, wherein the extracorporeal pump comprises a pump housing, at least three independent chambers are arranged at intervals in the pump housing, each independent chamber is respectively communicated with each independent conduit in a one-to-one correspondence manner, the corresponding independent chamber, independent conduit and independent soft bag form a closed space, the inside of the closed space is filled with the fluid, an electromagnetic driving mechanism is arranged between any two adjacent independent chambers, each electromagnetic driving mechanism comprises a permanent magnet which is fixedly arranged and electromagnets which are movably arranged at two sides of the permanent magnet and can reciprocate relative to the permanent magnet, the two electromagnets are respectively connected with the side walls of the independent chambers at two sides, the energizing time and direction of each electromagnet can be controlled by the controller, so that the electromagnets are driven by magnetic force generated between the electromagnets and the corresponding permanent magnets to drive the side walls of the corresponding independent chambers to reciprocate so as to contract or expand the independent chambers, and then the fluid is filled into or pumped out of the corresponding independent soft balloon through the corresponding independent catheter so as to expand or contract the corresponding independent soft balloon.