CN204972438U - Elasticity haematodocha and pneumatic bellow drive formula artificial heart pump for artificial heart - Google Patents

Abstract

<b>The utility model discloses an elastic blood bag for an artificial heart and an airbag-driven artificial heart pump. The airbag-driven artificial heart pump adopts an elastic blood bag for an artificial heart with a simple structure and is easy to manufacture. Two pacifier-shaped protrusions facing inward and outward on the elastic blood sac, with a hole in the middle, replace the artificial heart valve with extremely complex structure, realize one-way suction and one-way discharge, and then pass through only one trachea The air bag driving mechanism in the body drives the elastic blood sac to work alternately between the diastolic working state and the contracting working state, so as to realize the process of absorbing and discharging liquid alternately, and can output pulsed blood flow similar to the natural heart. Nicely mimics the working process of the natural heart. At the same time, the elastic blood sac is made of elastic and stretchable material, and its interior is streamlined, which will not damage the cells in the blood and is not easy to form thrombus. It can well replace the work of the natural heart of humans or vertebrates. </b>

Description

Elastic blood bag for artificial heart and balloon-driven artificial heart pump

technical field

The utility model relates to an elastic blood bag for an artificial heart and an air bag-driven artificial heart pump.

Background technique

Heart disease is the second leading cause of human death. When the human heart loses part or all of its function due to disease and injury and cannot maintain the normal circulation of the whole body, a mechanical device made of artificial materials can be transplanted to temporarily or permanently replace the heart function partially or completely to promote blood circulation, so that the device is Artificial heart, which is also an effective means to solve end-stage heart disease in addition to heart transplantation, has largely solved the problem that heart transplantation cannot be performed in time due to insufficient donors.

At present, the artificial heart mainly uses two blood pumps with different principles, namely, the pulse volume pump based on the artificial heart valve, and the continuous pump that pumps blood without interruption. However, these two artificial heart pumps still have problems of one kind or another, and cannot simulate the role and function of the natural heart well.

The working mode of the pulsating volumetric blood pump is very similar to the natural animal heart. Its key component is the artificial heart valve, which is a one-way valve that controls the blood flow of the heart. Its structure is closely related to the performance of the artificial heart. , which was first used clinically in 1960, after years of research, it has successively experienced mechanical valves, biological tissue valves, and interventional valves. However, artificial heart valves are extremely complex, expensive to manufacture and prone to blood clots, known as thrombi, forming in moving parts.

For example, Chinese Patent Publication No. 1093005, titled "Integrated Capsular Artificial Heart-Lung Pump", in this kind of artificial heart-lung pump, the blood storage bag is installed in the pump and inserted into the chest cavity of the human body. Blood clots form, and artificial heart valves are not easy to manufacture. The Chinese Patent No. 99126700.1, titled "Pneumatic and Electric Integrated Blood Pump, Pneumatic and Electric Integrated Artificial Heart" provides a gas and electric integrated artificial heart. However, its internal structure is complicated, and it is basically impossible to manufacture, and Implementation costs are high. Another example is Chinese Patent Publication No. 103656770, titled "Artificial Heart Blood Pump Driven Based on Miniature Cylinder", which also has the same problem, and the miniature cylinder needs to connect two trachea to the outside of the body in the chest cavity of the human body, which is very easy to cause user's fatigue. discomfort.

Due to the technical bottleneck of artificial heart valves in pulsed volumetric blood pumps, most of the recently developed artificial hearts tend to use continuous pumps that pump blood without interruption. For example, Chinese Patent Publication No. 102019002A, titled "An Implantable Hollow Miniature Axial Blood Pump", and Chinese Patent Publication No. 10237598, titled "Compact Axial Flow Magnetic Levitation Artificial Heart Pump" Among them, both of them use an axial flow pump. Although it can damage the cells in the blood less than the gear pump and the vane pump, the high-speed operation of its components still destroys the cells in the blood. , and because the axial flow pump is a continuous pump, it cannot simulate the working process of the natural heart, so it can be said that it is a selective error in the direction of technology.

Contents of the invention

The purpose of the utility model is to overcome the disadvantages of the prior art, and provide an elastic blood bag for an artificial heart with a simple structure, convenient manufacture, and the ability to realize one-way liquid absorption and one-way liquid discharge.

In order to achieve the above-mentioned purpose, the technical scheme adopted by the utility model is: an elastic blood bag for artificial heart, comprising a bag-shaped body with a closed inner cavity made of stretchable material, the end of the bag-shaped body has A first protrusion recessed into the closed inner cavity, a second protrusion protruding outward from the closed inner cavity, a first liquid flow hole is opened on the first protrusion, and a first liquid flow hole is opened on the second protrusion. A second liquid flow hole is opened on the protrusion, and the capsule body has a diastolic working state when it is laterally pulled and a contraction working state when it is laterally compressed. When the capsule body is in a diastolic working state, the The first liquid flow hole is opened to communicate with the closed inner cavity to form a liquid suction one-way valve, and the second liquid flow hole is closed; when the bladder is in a contracted working state, the first liquid flow The hole is closed, and the second liquid flow hole is opened to communicate with the closed inner cavity to form a liquid discharge one-way valve.

Preferably, both the first protrusion and the second protrusion are nipple-shaped.

Preferably, the first liquid flow hole is a streamlined horn hole whose diameter gradually decreases from outside to inside, and the second liquid flow hole is a streamlined horn hole whose diameter gradually decreases from inside to outside.

Preferably, a liquid supply part with a liquid supply chamber is provided on the outer side of the first protrusion on the capsule body, and when the capsule body is in a dilated working state, the liquid supply chamber passes through the first protrusion. A liquid flow hole communicates with the closed inner cavity; the bladder is located on the outside of the second protrusion and is provided with a drain portion with a drain chamber. When the bladder is in a contracted working state , the liquid discharge chamber communicates with the closed inner chamber through the second liquid flow hole.

Further preferably, both the liquid supply part and the liquid discharge part are streamlined.

Another purpose of this utility model is to overcome the shortcomings of the prior art, and provide a pulse-supply volumetric artificial heart pump driven by an air bag with the above-mentioned elastic blood bag for the artificial heart.

For achieving the above object, the technical scheme that the utility model adopts is:

An artificial heart pump driven by an air bag, the artificial heart pump includes two elastic blood sacs, an air bag-type drive mechanism for driving the expansion and contraction of the two elastic blood sacs, each of the elastic blood sacs includes a flexible A bladder made of material with a closed lumen, the end of the bladder has a first protrusion that is recessed into the closed lumen, and a first protrusion that protrudes outward from the closed lumen. Two protrusions, the first protrusion is provided with a first liquid flow hole, the second protrusion is provided with a second liquid flow hole, and the bladder is located on the outside of the first protrusion. There is a liquid supply part with a liquid supply chamber, and a liquid discharge part with a liquid discharge chamber is provided on the outside of the second protrusion on the bladder, and the elastic blood sac has a dilated working state and a contracted working state, When the sac is pulled laterally, the elastic blood sac is in a dilated working state, and the first liquid flow hole is opened so that the liquid supply chamber communicates with the closed inner chamber to form a liquid suction one-way valve , blood enters the closed inner cavity of the elastic blood sac from the liquid supply chamber, and the second liquid flow hole is closed; when the sac is laterally pressed, the elastic blood sac is in a contracted working state, The first liquid flow hole is closed, and the second liquid flow hole is opened so that the liquid discharge chamber communicates with the closed inner cavity to form a liquid discharge one-way valve, and blood enters from the closed inner cavity of the elastic blood bag the drain chamber,

The airbag-type driving mechanism includes an airbag arranged between the two elastic blood sacs and capable of expanding and contracting in its radial direction. , the other side of the bladder is fixed, and the airbag driving mechanism further includes an air supply device for inflating or vacuuming the inner cavity of the airbag to expand or shrink the volume of the airbag.

Preferably, both the first protrusion and the second protrusion are nipple-shaped, the first liquid flow hole is a streamlined horn hole whose diameter gradually decreases from outside to inside, and the second liquid flow hole is formed by Streamlined horn hole with gradually smaller diameter from inside to outside.

Preferably, pressure plates are respectively fixedly connected to both radial sides of the airbag, and the outer end surface of the pressure plate is an arc surface consistent with the contour of the side end surface of the bladder, and the outer end surface of the pressure plate is in line with the outer end surface of the pressure plate. The side end surfaces of the capsule are fixedly bonded together.

Preferably, the closed lumens of the two capsules respectively constitute the left ventricle and the right ventricle of the artificial heart, and correspondingly, the liquid supply chambers of the two liquid supply parts respectively constitute the left atrium of the artificial heart with the right atrium.

Preferably, the air supply device includes a vacuum generating cylinder and a trachea connected to the inside and outside of the chest cavity of a human or animal. The air pipe, the vacuum generating cylinder and the air bag are reversingly controlled by a solenoid valve to realize inflation and vacuuming.

Due to the application of the above-mentioned technical solutions, the utility model has the following advantages compared with the prior art: the utility model is an airbag-driven artificial heart pump, wherein an elastic blood sac for an artificial heart with a simple structure and convenient manufacture is adopted, with On the elastic blood sac, two pacifier-shaped protrusions facing inward and outward, with a hole in the middle, replace the artificial heart valve with an extremely complex structure, and realize one-way liquid suction and one-way discharge, and then pass through only one trachea. The air bag-type drive mechanism inserted into the body drives the elastic blood sac to expand and contract, making it alternately switch between the diastolic working state and the contracting working state, so as to realize the process of absorbing and discharging liquid alternately, and can output pulsed blood flow similar to the natural heart , to avoid the technical direction error of the continuous blood pump, and to imitate the working process of the natural heart well. At the same time, the elastic blood sac is made of elastic and stretchable material with a streamlined interior, which will not damage the cells in the blood and is not easy to form thrombus, so it can well replace the work of the natural heart of humans or vertebrates.

Description of drawings

Accompanying drawing 1, accompanying drawing 2 are an embodiment of the utility model that is used for single ventricle, wherein accompanying drawing 1 is the schematic diagram when the cystic body of elastic blood sac is in diastolic working state; Accompanying drawing 2 is the saccular shape of elastic blood sac Schematic diagram of the body in contraction working state;

Accompanying drawing 3, accompanying drawing 4 are an embodiment that the utility model is used for double ventricle, and wherein, accompanying drawing 3 is the schematic diagram when the artificial heart pump of the present utility model is in diastolic working state; Accompanying drawing 4 is the artificial heart pump of the present utility model Schematic diagram of the heart pump in its systolic working state.

Among them: 100, elastic blood sac; 1, cystic body; 10, closed inner cavity; 11, first protrusion; 12, first liquid flow hole; 13, second protrusion; 14, second liquid flow hole; 2. Liquid supply part; 21. Liquid supply cavity; 22. Liquid supply port; 3. Liquid discharge part; 31. Liquid discharge cavity; 32. Liquid discharge port;

200. Airbag type driving mechanism; 4. Airbag; 5. Press plate; 6. Vacuum generating cylinder; 7. Two-position three-way reversing valve; 8. Two-position four-way reversing valve.

detailed description

The technical solution of the present utility model will be further elaborated below in conjunction with the accompanying drawings and specific embodiments.

Referring to Fig. 1 and Fig. 2, it shows an embodiment of an elastic blood bag 100 used in a single ventricle. The elastic blood sac 100 includes a sac body 1 made of stretchable material with a closed lumen 10, the end of the sac body 1 has a first protrusion 11 recessed into the closed lumen 10. The second protrusion 13 that protrudes outward from the closed inner cavity 10, the first protrusion 11 is provided with a first liquid flow hole 12, and the second protrusion 13 is provided with a second liquid flow hole 14, wherein the bladder 1 The upper first protrusion 11 and the second protrusion 13 are respectively disposed on two ends of the capsule body 1 . When the sac 1 is subjected to lateral tension, its internal volume expands, and the so-called "negative pressure" will be generated inside the sac 1, that is, the elastic blood sac 100 is subjected to the environmental pressure, as shown by the arrow in Figure 1. Under the action of this pressure, the second liquid flow hole 14 at the second protrusion 13 protruding outward is closed, while the first liquid flow hole 12 at the first protrusion 11 protruding inward is opened, and the blood flow is caused by The outside flows into the inside of the bladder 1 . When the bladder 1 is subjected to lateral pressure, its internal volume shrinks, and the internal pressure of the bladder 1 will be greater than the pressure of the external environment. The internal pressure distribution is shown by the arrow in Figure 2. Under the action of this pressure, the inner convex The first liquid flow hole 12 at the protruding first protrusion 11 is closed, and the second liquid flow hole 14 at the outwardly protruding second protrusion 13 is opened, so that blood flows from the inside of the bladder 1 to the outside.

Referring to FIG. 3 and FIG. 4 , a balloon-driven biventricular artificial heart pump is shown. The artificial heart pump mainly includes two elastic blood bags 100 and a balloon-type driving mechanism 200 for driving the elastic blood bags 100 to expand and contract.

As shown in Fig. 3 and Fig. 4, these two elastic blood sacs 100 all include a sac body 1 with a closed inner cavity 10 made of stretchable material, and the end of the sac body 1 has a closed inner cavity The first protrusion 11 recessed in 10, the second protrusion 13 protruding outward from the closed inner cavity 10, the first protrusion 11 is provided with a first liquid flow hole 12, and the second protrusion 13 is provided with a The second flow hole 14. When the capsule body 1 is subjected to lateral tension, the capsule body 1 expands to cause the internal volume to expand, and the first liquid flow hole 12 can be opened to communicate with the closed inner cavity 10, while the second liquid flow hole 14 is closed at this time ; When the capsule body 1 is subjected to lateral pressure, the capsule body 1 contracts to cause the internal volume to shrink, the first flow hole 12 is closed, and at this time the second flow hole 14 is opened to communicate with the closed inner cavity 10 .

Referring to Fig. 3 and Fig. 4, a liquid supply part 2 with a liquid supply cavity 21 is provided on the capsule body 1 outside the first protrusion 11, and a liquid supply part 2 with a liquid supply chamber 21 is provided on the capsule body 1 outside the second protrusion 13. The drain unit 3 is provided with a drain chamber 31 . The liquid supply part 2 has a liquid supply port 22 communicated with the liquid supply chamber 21 , and the liquid discharge part 3 has a liquid discharge port 32 communicated with the liquid discharge chamber 31 .

The elastic blood sac 100 has a dilated working state and a contracted working state. When the sac 1 is stretched and stretched laterally, the elastic blood sac 100 is in the relaxed working state and the internal volume expands. At this time, the first fluid flow hole 12 opens and The liquid supply chamber 21 communicates with the closed inner cavity 10 through the first liquid flow hole 12, and the second liquid flow hole 14 is closed, at this time, the liquid flow can enter the liquid supply chamber 21 from the liquid supply port 22 and then pass through the first liquid flow The hole 12 enters the closed inner cavity 10 of the capsule body 1 to realize liquid supply; when the capsule body 1 is compressed and contracted laterally, the elastic blood sac 100 is in the working state of contraction and the internal volume is reduced, at this time the first liquid The flow hole 12 is closed, and the second liquid flow hole 14 is opened so that the liquid discharge chamber 31 communicates with the closed inner cavity 10 through the second liquid flow hole 14. At this time, the liquid flow can pass through the second liquid flow hole 14 from the closed inner cavity 10 Enter the liquid discharge cavity 31, and then discharge through the liquid discharge port 32 to realize liquid discharge.

In this way, that is, the first protrusion 11 provided with the first liquid flow hole 12 constitutes a liquid suction one-way valve, while the second protrusion 13 provided with the second liquid flow hole 14 constitutes a liquid discharge one-way valve. On each elastic blood sac 100 , the closed cavity 10 of the sac 1 constitutes the ventricle of the artificial heart, and the liquid supply cavity 21 of the liquid supply part 2 constitutes the atrium.

In the above-mentioned embodiment, both the first protrusion 11 and the second protrusion 13 are nipple-shaped, the first liquid flow hole 12 is a streamlined trumpet hole whose diameter gradually becomes smaller from the outside to the inside, and the second liquid flow hole 14 is from the inside to the inside. Streamlined trumpet hole with gradually smaller outer diameter, so that when the bladder 1 is subjected to lateral tension, the first protrusion 11 is pulled to open the first liquid flow hole 12, and the second protrusion 13 is pulled The second liquid flow hole 14 is closed; when the bladder 1 is subjected to lateral pressure, the first protrusion 11 is pressed to close the first liquid flow hole 12, and the second protrusion 13 is pressed to make the first liquid flow hole 12 closed. The second liquid flow hole 14 is opened. Both the liquid supply part 2 and the liquid discharge part 3 are arranged in a streamlined shape. During specific arrangement, the capsule body 1 is integrally provided with the liquid supply part 2 and the liquid discharge part 3 , and the liquid supply part 2 and the liquid discharge part 3 are located at the same end of the capsule body 1 .

The elastic blood sac 100 is made of elastic and stretchable material, which will not damage the cells in the blood during the working process, is not easy to form thrombus in the human body or animal body, and can imitate the liquid flow of the natural cardiac output pulse.

Referring to Fig. 3 and Fig. 4, the air bag driving mechanism 200 includes an air bag 4 arranged between two elastic blood bags 100 and capable of expanding and contracting in its radial direction. One side of the body 1 is fixedly connected, and the other side of the capsule body 1 is fixedly arranged. Here, the two radial sides of the airbag 4 are respectively fixedly connected with a pressure plate 5, the outer end surface of the pressure plate 5 is an arc surface consistent with the profile of the side end surface of the bladder 1, and the outer end surface of the pressure plate 5 is in line with the shape of the bladder. The side end faces of the body 1 are fixedly glued together. In this way, when the airbag 4 stretches in the radial direction, it can pull the bladder 1 or press the bladder 1 laterally, so that the bladder 1 expands or shrinks to expand or shrink its internal volume.

The two elastic blood sacs 100 are respectively similar to the left and right parts of the natural heart of a human or a vertebrate, and the closed inner cavities of the two sacs 1 constitute the left ventricle and the right ventricle of the artificial heart respectively. Correspondingly, the two fluid supply The liquid supply chambers 21 of the part 2 respectively constitute the left atrium and the right atrium of the artificial heart.

The airbag driving mechanism 200 also includes an air supply device for inflating or evacuating the inner chamber of the airbag 4 so as to expand or shrink the volume of the airbag 4 so as to expand and contract the airbag 4 in the radial direction. The air supply device includes a vacuum generating cylinder 6, a trachea (not shown in the figure) connected to the inside and outside of a person or animal, and the air pipe, vacuum generating cylinder 6 and air bag 4 are controlled by an electromagnetic reversing valve to realize the inflation of the inner cavity of the air bag 4 with pumping.

As shown in FIG. 3 and FIG. 4 , the electromagnetic reversing valve here includes a two-position three-way reversing valve 7 and a two-position four-way reversing valve 8 . As shown in Figure 3, when the two-position three-way reversing valve 7 is in the right position and the two-position four-way reversing valve 8 is in the left position, the compressed gas pushes the piston rod of the vacuum generating cylinder 6 to move to one end of the rodless chamber, and the Negative pressure is generated in the front end chamber of the piston rod due to volume expansion, and the gas in the inner chamber of the airbag 4 enters the front end chamber of the piston rod of the vacuum generating cylinder 6 through the two-position three-way reversing valve 7, so that the airbag also generates negative pressure and is in contraction state, thereby pulling the two pressure plates 5 to move toward the center at the same time, the capsule body 1 of the elastic blood sac 100 is stretched by the lateral pulling force, causing the internal volume to expand. At this time, the second liquid flow hole 14 is closed, and the first The liquid flow hole 12 is opened, and the external liquid flow enters the liquid supply chamber 21 through the liquid supply port 22 and then enters the closed inner cavity 10 of the bladder 1 through the first liquid flow hole 12; then, the two-position three-way reversing valve 7 and the two-position five-way reversing valve 8 to work in reverse, the two-position three-way reversing valve 7 is switched to the left position and the two-position four-way reversing valve 8 is switched to the right position, as shown in Figure 4, the compressed gas enters the vacuum The rodless chamber of the cylinder 6 drives the piston rod to move to the side of the rod chamber, and the front end chamber of the piston rod communicates with the atmosphere; at the same time, the compressed gas enters the inner chamber of the airbag 4 through the two-position three-way reversing valve 7, so that the airbag 4, the inner volume expands and expands, so that the two pressure plates 5 move outward at the same time, exerting lateral pressure on the sac 1 and making the elastic blood sac 100 switch to the contracted working state, the first liquid flow hole 12 is closed, and the second flow hole 12 is closed. The second liquid flow hole 14 is opened, and the liquid in the closed cavity 10 of the capsule body 1 enters the liquid discharge chamber 31 through the second liquid flow hole 14 and is discharged through the liquid discharge port 32 to supply blood to the body. Then, the two-position three-way reversing valve 7 and the two-position five-way reversing valve 8 are switched to work again, and the elastic blood sac 100 is converted into the diastolic working state again, so that the two elastic blood sacs 100 of the artificial heart pump are working in the diastolic state. The state and the contraction working state are alternately changed, so as to realize the alternate and continuous work of liquid suction and liquid discharge.

To sum up, the balloon-driven artificial heart pump of the present utility model adopts an elastic blood bag 100 for an artificial heart with a simple structure and is easy to manufacture. The two pacifier-shaped protrusions of the two pacifiers replace the artificial heart valve with extremely complicated structure to realize one-way liquid suction and one-way liquid discharge, and then drive the elastic blood bag 100 to work through the air bag-type driving mechanism with only one trachea leading into the body, so that It alternates between the diastolic working state and the systolic working state, thereby alternately realizing the process of suction and discharge, and can output a pulsed blood flow similar to a natural heart, avoiding the technical direction error of a continuous blood pump, very good It closely mimics the working process of the natural heart. At the same time, the elastic blood sac 100 is made of elastic and stretchable material, and its interior is streamlined. It will not damage the cells in the blood and is not easy to form thrombus. It can well replace the work of the natural heart of humans or vertebrates.

The above-mentioned embodiments are only to illustrate the technical concept and characteristics of the present utility model, and its purpose is to enable those familiar with this technology to understand the content of the present utility model and implement it accordingly, and not to limit the protection scope of the present utility model. All equivalent changes or modifications made according to the spirit of the utility model shall fall within the protection scope of the utility model.

Claims (10)

1. an artificial heart elasticity haematodocha, it is characterized in that: comprise the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, contraction duty when diastole duty when described cystidium has a side direction tension and side loaded, when described cystidium is in diastole duty, described first liquid flow hole is opened and is connected with described closed inner chamber and forms imbibition check valve, described second liquid flow hole closes, when described cystidium be in shrink duty time, described first liquid flow hole closes, and described second liquid flow hole is opened and is connected with described closed inner chamber and forms discharge opeing check valve.

2. artificial heart elasticity haematodocha according to claim 1, is characterized in that: described first projection and described second projection are all in nipple-like.

3. artificial heart elasticity haematodocha according to claim 1 and 2, is characterized in that: described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, the streamlined bellmouth orifice that described second liquid flow hole diminishes gradually in diameter from inside to outside.

4. artificial heart elasticity haematodocha according to claim 1, it is characterized in that: the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, when described cystidium is in diastole duty, the described sap cavity that supplies is connected with described closed inner chamber by described first liquid flow hole; The outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, and when described cystidium is in contraction duty, described exhaust chamber is connected with described closed inner chamber by described second liquid flow hole.

5. artificial heart elasticity haematodocha according to claim 4, is characterized in that: described feed flow portion, described discharge opeing portion are all in streamlined.

6. an air bag driving artificial heart pump, it is characterized in that: described artificial heart pump comprises two elasticity haematodocha, for the gasbag-type driving mechanism driving two described elasticity haematodocha flexible, each described elasticity haematodocha includes the cystidium with closed inner chamber be made up of retractable material, the end of described cystidium has the first projection recessed in described closed inner chamber, from the second projection that described closed inner chamber is outwardly, described first projection offers the first liquid flow hole, described second projection offers the second liquid flow hole, the outside described cystidium being positioned at described first projection is provided with the feed flow portion possessed for sap cavity, the outside described cystidium being positioned at described second projection is provided with the discharge opeing portion possessing exhaust chamber, described elasticity haematodocha has diastole duty and shrinks duty, when described cystidium side direction tension, described elasticity haematodocha is in diastole duty, described first liquid flow hole is opened and is made described being connected with described closed inner chamber for sap cavity form imbibition check valve, blood is by the described closed inner chamber entering described elasticity haematodocha for sap cavity, described second liquid flow hole closes, when described cystidium side loaded, described elasticity haematodocha is in contraction duty, described first liquid flow hole closes, described second liquid flow hole is opened and described exhaust chamber is connected with described closed inner chamber form discharge opeing check valve, blood enters described exhaust chamber by the closed inner chamber of described elasticity haematodocha

Described gasbag-type driving mechanism comprises to be located between two described elasticity haematodocha and can along the air bag of self radial expansion, the radial two ends of described air bag are fixedly connected with the side of two described cystidiums respectively, the opposite side of described cystidium is fixedly installed, and described gasbag-type driving mechanism also comprises the feeder expanding for inflation in the inner chamber to described air bag or evacuation to make described bag volume or reduce.

7. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: described first projection and described second projection are all in nipple-like, described first liquid flow hole is the streamlined bellmouth orifice that ecto-entad diameter diminishes gradually, the streamlined bellmouth orifice that described second liquid flow hole diminishes gradually in diameter from inside to outside.

8. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: the radial both sides of described air bag have been permanently connected pressing plate respectively, the end face outside of described pressing plate is in the cambered surface consistent with the side end face appearance profile of described cystidium, and the outer face of described pressing plate and the side end face of described cystidium bond together regularly.

9. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: the closed inner chamber of two described cystidiums forms left ventricle and the right ventricle of described artificial heart respectively, accordingly, the left atrium and the right atrium that form described artificial heart for sap cavity respectively in two described feed flow portions.

10. a kind of air bag driving artificial heart pump according to claim 6, it is characterized in that: described feeder comprises the trachea inside and outside vacuum generation cylinder, connection human or animal thoracic cavity, realizes inflation and evacuation between described trachea, described vacuum generation cylinder and air bag by electromagnetic valve commutation control.