JPH07255834A - Blood pump - Google Patents

Abstract

PURPOSE:To provide a light and small blood pump by which a difference in a blood sending-out quantity between left and right blood pumps can be automatically adjusted and the possibility of damaging organism tissue or blood is precluded. CONSTITUTION:A blood pump has casings 110 and 120, diaphragms arranged in the casings 110 and 120, blood chambers 11 and 12 which are partitioned by the diaphragms and send out blood and driving chambers 21 and 22 having driving means. The diaphragms are composed of blood side diaphragms 13 and 14 situated on the blood chamber 11 and 12 side and driving side diaphragms 23 and 24 situated on the driving chamber 21 and 22 side. Buffer chambers 35 and 36 are interposed between both, and the buffer chambers 35 and 36 are gas-permeably connected to gas shock absorbing parts 31 and 32.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a blood pump used for a total replacement type artificial heart or an auxiliary heart.

[0002]

2. Description of the Related Art As one of the treatment methods for irreversible heart disease patients, a blood pump that attaches a dysfunctional heart as it is, sucks blood from the bottom of the atrium or ventricle, and delivers the blood to an artery A method using an assisted artificial heart that assists the natural heart until the function of the natural heart is restored, or a heart replacement method that removes all the heart and replaces it with a total replacement artificial heart have been proposed. The following devices have been conventionally used as the artificial heart.

First, as shown in FIG. 14, in the artificial heart device 9, the left and right casings 110, 120, the left and right diaphragms 93, 94 respectively disposed in the casings 110, 120, and the diaphragm 93, Left and right blood chambers 91 and 92 partitioned by 94, and left and right drive chambers 910 and 920 having drive means are provided. The drive means is the pump 2 that intermittently delivers the silicone oil that is the drive fluid 200 to the drive chambers 910 and 920.

Reference numerals 15 and 16 denote blood 10 respectively.
This is an inflow port for allowing 0 to flow into the left and right blood chambers 91 and 92. Further, reference numerals 17 and 18 are delivery ports 17 and 18 for delivering the blood 100. Further, artificial valves 150 to 180 for preventing backflow of the blood 100 are provided in the respective ports 15 to 18. Also,
Reference numerals 25 and 26 are drive tubes for delivering the drive fluid 200 from the pump 2 to the drive chambers 910 and 920.

Next, the artificial heart device 9 drives the blood 100 as shown below. First, the pump 2 moves the driving fluid 200 from the left driving chamber 910 to the right driving chamber 920. Along with this, the diaphragm 9 of the left blood chamber 91
3 moves to the right and causes blood 100 to flow into the left blood chamber 91. On the other hand, the diaphragm 94 of the right blood chamber 92 causes the blood 100 to be delivered from the right blood chamber 92.

Thereafter, the pump 2 moves the driving fluid 200 in the opposite direction. As a result, blood 1 is stored in the right blood chamber 92.
00 flows in, and on the contrary, blood 100 in the left blood chamber 91 is sent out. By repeating the above operation, the artificial heart device 9 can drive the blood 100 in the same manner as the natural heart.

In the artificial heart device 9, one pump 2 reverses the flow of the driving fluid 200 at regular intervals. Therefore, the left and right diaphragms 93, 94 can be driven by the single pump 2. Also,
The structure is simple. Therefore, the artificial heart device 9 is small and can be easily installed in a limited space.

[0008]

By the way, as shown in FIG. 15, in the circulatory system of the human body, the heart 80 is the left atrium 81.
1 and a left ventricle 812, and a right atrium 82
1 and a right ventricle 822 including a right ventricle 822. The right heart system 82 has a role of sending venous blood that has circulated throughout the body and returned to the heart 80 again to the lungs, and the left heart system 81 has a role of sending blood sent from the lungs to the whole body as arterial blood. . In the drawings, reference numeral 83 is an aorta, reference numeral 84 is a vena cava, reference numerals 86 and 87 are pulmonary arteries, and reference numerals 870 and 860 are pulmonary veins. The arrows in each blood vessel indicate the blood flow.

However, in the human circulatory system, the left heart system 81
There is a part called a bronchial circulation 89 which is sent out from the bronchus and returns directly to the left heart system 81 without passing through the right heart system 82. Therefore, the left heart system 81 in the natural heart is
The amount of blood flowing in and out is 5 to 10 as compared with the right heart system 82.
There are many%.

However, in the artificial heart device 9,
Due to its structure, the volumes of the left and right blood chambers 91, 92 and the inflow and outflow amounts of blood are equal. Therefore, blood is collected in the left blood chamber 91
When the left diaphragm 93 is moved until the blood is completely exhausted from the left blood chamber 91,
Since the amount of blood flowing into the right blood chamber 92 from the whole body is smaller than that on the left side, blood is excessively sucked into the right blood chamber 92. As a result, hemolysis and damage occur in the blood and tissues of the right heart system. Further, since the afterload of the left blood chamber 91 is higher than that of the right blood chamber 92, backflow is likely to occur when the artificial valves 150 and 170 are opened and closed. In this case, due to the above-mentioned backflow, the blood delivery amount in the left blood chamber 91 is rather reduced.

Therefore, attempts have been made to solve the above problems by adding the following configuration to the blood pump in the artificial heart device. That is, one has a shunt hole of an appropriate diameter between the right atrium and the left atrium,
This is a method in which part of the blood delivered from the right blood chamber is returned to the right atrium after pulmonary circulation. Further, as a means different from the above method, there is a method of reducing the volume of the right blood chamber and, as a result, sending the driving fluid that is in excess of the right driving chamber to the artificial left atrium provided on the left atrium side.

However, the difference in blood volume between the left and right is large depending on individuals, and depends on, for example, the circulating blood volume of the whole body and the weight of each individual. Therefore, the diameter of the shunt hole must be adjustable for each individual. However, it is very difficult to actually adjust the diameter. Further, since the shunt hole is provided in the living tissue, the peripheral tissue grows in a relatively short time and blocks the shunt hole.

Further, when the artificial left atrium is provided, the flow paths of the driving fluid and blood become complicated. As a result, the structure of the blood pump may be complicated and large. This is inconvenient because the artificial heart device is installed in a limited space.

In view of the above problems, the present invention is capable of automatically adjusting the difference in the amount of blood delivered between the left and right blood pumps, and is lightweight and small in size that does not cause damage to living tissue or blood. A pump is provided.

[0015]

According to the present invention, there is provided a blood having a casing, a diaphragm arranged in the casing, a blood chamber partitioned by the diaphragm for delivering blood, and a driving chamber having a driving means. In the pump, the diaphragm is composed of a blood side diaphragm located on the blood chamber side and a drive side diaphragm located on the drive chamber side, and a buffer chamber is provided between the two, and the buffer chamber is The blood pump is characterized in that it is connected to the gas buffer section so that it can be ventilated.

What is most noticeable in the present invention is that a buffer chamber is provided between the blood side diaphragm and the driving side diaphragm, and the buffer chamber is connected to the gas buffer section so as to be ventilated. It is that you are. The buffer chamber is preferably filled with air or an inert gas such as nitrogen or helium. The blood pump described above is a diaphragm type. However, the buffer chamber of the present invention can be provided for tube-type and suck-type blood pumps, which will be described later.

Next, as the gas buffer section, for example, a flexible variable volume container capable of changing volume, a fixed volume container without volume change, or the atmosphere itself is used. That is,
The flexible variable volume container is, for example, a bag-shaped container such as a compliance chamber which is made of resin, rubber or the like and has no resistance to changes in volume. In the variable volume container, it is preferable to fill the same amount of gas as the maximum volume of the buffer chamber in advance.

In the variable volume container, a fixed volume of gas reciprocates between the buffer chamber and the variable volume container. Thereby, as will be described later, the operation of the blood side diaphragm and the operation of the drive side diaphragm can be made independent, and it is possible to cope with the difference between the left and right blood volumes. With the above configuration, it is possible to obtain a completely implantable blood pump that can be embedded in the body including the gas buffer section. Therefore, an artificial heart that does not hinder the behavior of the patient can be manufactured.

Next, the fixed volume container is a can-shaped container such as a hard shell damper. In the fixed volume container, the amount of gas enclosed in the combined volume of the buffer chamber and fixed volume container is constant. Therefore, when the amount of blood flowing into the blood chamber decreases and the volume of the buffer chamber increases, the pressure in the buffer chamber slightly tilts to the negative pressure side. As a result, in this configuration, a large amount of blood can be drawn into the blood chamber. Therefore, there is an advantage that a large amount of blood can be set. Also,
Also with this configuration, a completely implantable blood pump can be obtained.

Next, the gas buffer section can be opened to the atmosphere. In this case, the tube is pulled out from the buffer chamber to the outside of the body, and for example, a breathable sterilization box is provided at the tip of the tube. Then, gas flows in or out from the tip of the tube as the buffer chamber expands and contracts. In this case, by monitoring the inflow and outflow gas amounts from outside the body, the operating state of the blood pump can be checked from the outside and the state of the living body can be constantly checked.

Next, as the drive means, for example, a pump for intermittently delivering the drive fluid to the drive chamber or a motor for mechanically driving the drive device is used. When the pump is used as the driving means, for example, the driving means and the blood pump may be installed separately, and the space between them may be connected by a tube or the like filled with the driving fluid. By using a flexible material for the tube or the like, the driving means can be provided separately from the blood pump in a space such as the abdomen where there is a space. Further, as the above-mentioned pump, there are a friction pump, an axial flow type pump, a switching valve type pump and the like. The driving fluid used is silicone oil, perfluorocarbon, hydrocarbon,
There is water etc.

Next, the blood chamber has, for example, a tube type or a sack type. As described later, the tube-type and sac-type blood pumps are provided with a drive chamber filled with a drive fluid in a casing, and further a blood chamber inside the drive chamber. (FIGS. 12 and 13). Also in the above structure, two types of diaphragms and buffer chambers are provided at the boundary between the drive chamber and the blood chamber.

Next, for example, there are two casings on the left and right, the drive means is disposed between them, and each casing has the blood side diaphragm and the drive side diaphragm. In this case, it is used as a total replacement artificial heart.
Further, for example, the number of casings may be one. In this case, it is used as an auxiliary artificial heart.

That is, the present invention also relates to a total replacement type artificial heart used when the natural heart is completely removed,
It can also be applied in assisted artificial hearts used in assisting a weakened natural heart until it recovers.

Next, it is preferable that the blood side diaphragm and the driving side diaphragm are composed of a plurality of laminated sheets. That is, for each of the above diaphragms,
There are a thin flexible film and a single layer made of one kind of material, a plurality of layers made of one or more kinds of materials, and the like. In the case of a single layer, the structure is simple and the fabrication is easy. In the case of multiple layers, the individual film thickness can be made thinner, so the movement of the diaphragm is improved, and even if the diaphragm is damaged, the gas in the buffer chamber is not immediately mixed with the blood, which is highly safe. Polyurethane, polyvinyl chloride, etc. are used as the material of each diaphragm.

[0026]

In the blood pump of the present invention, the buffer chamber is provided between the blood side diaphragm on the blood chamber side and the drive side diaphragm on the drive chamber side, and the buffer chamber is the gas buffer section. It is connected so that it can be ventilated, and its volume is variable. The driving diaphragm is driven by the driving means. However, because of the variable volume buffer chamber, the blood-side diaphragm is driven independently of the drive-side diaphragm by the pressure of the blood flowing into the blood chamber, that is, the atrial pressure during blood delivery.

Therefore, when blood flows into the blood chamber,
The expanded buffer chamber occupies the volume not required by the blood chamber in the space secured in the casing as a result of the movement of the driving diaphragm (see FIGS. 5 to 8).

Therefore, like the conventional blood pump, it is possible to prevent the drive-side diaphragm from pushing an empty blood chamber, or the drive-side diaphragm continuing to pull it after all the blood flows into the blood chamber. . In addition, the inflow and outflow of blood into the blood chamber is automatically adjusted according to the conditions on the living body side such as atrial pressure. As described above, since the inflow of blood is performed by the atrial pressure or the like, there is no possibility of applying a negative pressure or the like that may damage the living tissue or blood.

As described above, according to the present invention, it is possible to automatically adjust the difference in the amount of blood delivery between the left and right blood pumps, and there is no risk of damaging living tissue or blood.
It is possible to provide a lightweight and small blood pump.

[0030]

【Example】

Example 1 A blood pump according to an example of the present invention will be described with reference to FIGS.
Will be explained. As shown in FIG. 1, the blood pump 1 of this example has left and right casings 110 and 120, a diaphragm arranged in the casings 110 and 120, and left and right blood for delivering blood 100 partitioned by the diaphragm. Chambers 11 and 12, and pump 2 as a driving means
And the left and right drive chambers 21 and 22 connected to each other.

The above-mentioned diaphragm is located on the left and right blood chambers 11 and 12 and on the left and right blood diaphragms 1.
3, 14 and the left and right drive side diaphragms 23, 24 located on the left and right drive chambers 21, 22 side. The blood side diaphragms 13 and 14 and the drive side diaphragms 23 and 2
The left and right buffer chambers 35 and 36 are provided between the two. The buffer chambers 35 and 36 are connected to the left and right gas buffer portions 31 and 32 via gas tubes 33 and 34 so that they can be ventilated. Reference numeral 300 is air moving in the buffer chambers 35 and 36 and the gas buffer units 31 and 32.

Next, the left and right blood chambers 11, 12 are provided with inflow ports 15, 16 connected to each vein or each atrium and delivery ports 17, 18 connected to each artery, and each port is provided. Check valve 1 for preventing backflow of blood 100
50, 160, 170, 180 are built in. Next, the pump 2 intermittently delivers the silicone oil, which is the driving fluid 200, to the left and right drive chambers 21, 22. For this reason, the left and right drive tubes 25, 26 are connected to the pump 2 and the left and right drive chambers. It is provided between 21 and 22.

Further, the left and right gas buffer portions 31, 32 of this example
2 is a flexible compliant chamber 37 whose volume can be changed as shown in FIG. The compliant chamber 37 is made of a material that does not exert a resistance against a change in volume, and is like a paper balloon. Then, the compliance chamber 37 changes from the chain line 371 to the chain line 37 depending on the driving state of the diaphragm.
The volume is changed to the state shown in 2. The maximum volume of the compliance chamber 37 is 100 cc.

Next, as shown in FIG. 3, a friction pump 28 is used as the pump 2. The friction pump 28
Is filled with the driving fluid 200, and a case 285 provided with two outlets 281 and 282 for delivering the same.
And an impeller 283 provided in the case 285 and connected to a motor (not shown). The delivery ports 281 and 282 are connected to the drive tubes 25 and 26 shown in FIG. 1, respectively.

In the friction pump 28,
The driving fluid 200 trapped between the blades 2830 of the rotating impeller 283 is delivered from the outlets 281 and 282 according to the rotation direction of the impeller 283. The rotation direction is usually 60 to 60 minutes per minute, like the pulse of the heart.
70 times, switching to right and left. In addition to the friction type, the pump 2 may be an axial flow type, a switching valve type pump, or the like.

Next, as shown in FIG. 4, when the blood pump 1 is provided in the human body 8, the left and right casings 110 and 120 are housed in the space where the natural heart is removed. Further, the pump 2 and the gas buffer units 31 and 32 extend the drive tubes 25 and 26 and the gas tubes 33 and 34, and all are housed in the abdomen.

Next, the operation of the blood pump 1 of this example will be described with reference to FIGS. Blood pump 1
Repeats the cycle shown in the following FIGS. In addition,
The direction of movement of each diaphragm in each figure is indicated by an arrow. First, FIG. 5 shows the blood 1 in the left blood chamber 11 again.
The inflow of 00 is about to start.

In the above state, the pump 2 first starts to transfer the driving fluid 200 from the left driving chamber 21 to the right driving chamber 22. Along with this, the left blood side diaphragm 13 and the left drive side diaphragm 23 also start to move to the right. Further, the check valve 150 is opened by the left atrium pressure, and the blood 100 flows in from the left atrium.

On the other hand, the right blood chamber 12 is in a state where the filling of the blood 100 in an amount corresponding to the right atrial pressure is completed. And
The right blood side diaphragm 14 and the right drive side diaphragm 24, which have begun to move by the transfer of the driving fluid 200, start the delivery of the blood 100 in the same manner as in the left blood chamber of FIG. 7 described later.

FIG. 6 shows a state in which the blood 100 has further flown into the left blood chamber 11 as compared with FIG. However, since the blood inflow is still small, the left blood diaphragm 13
The amount of movement to the right of is not so large. However, the left drive-side diaphragm 23 follows the transfer amount of the drive fluid 200 and moves largely to the right.

Therefore, the movement difference between the two diaphragms is compensated for by the air 300 flowing into the left buffer chamber 35 from the left gas buffer 31 and increasing the volume of the buffer chamber 35. On the other hand, in the right drive chamber 22, the right blood side diaphragm 14 is pushed by the right drive side diaphragm 24, and the blood 100 in the right blood chamber 12 is delivered like the left blood chamber 11 of FIG. 8 described later.

FIG. 7 shows the right blood chamber 12 from the state of FIG.
Similarly to the left blood chamber 11 in FIG. 5, the inflow of the blood 100 by the right atrial pressure starts, and the blood 1
00 represents a state in which it is about to be sent out. That is,
The left blood chamber 11 is completely filled with blood 100 in an amount corresponding to the left atrial pressure.

At this time, the pump 2 starts to transfer the driving fluid 200 from the right driving chamber 22 to the left driving chamber 21 again. The left drive-side diaphragm 23 starts moving to the left, and the left buffer chamber 35 reduces its volume,
The air 300 therein is started to be delivered to the left gas buffer 31.

Eventually, the air 300 in the left buffer chamber 35
Most of the gas is sent to the left gas buffer 31, and the left drive-side diaphragm 23 and the left blood-side diaphragm 13 come into contact with each other.
At this time, the check valve 150 of the left inlet 15 is closed, and the check valve 170 of the left outlet 17 is opened.

FIG. 8 shows a state in which blood 100 is being delivered from the left blood chamber 11. That is, the driving fluid 100
The left drive-side diaphragm 23 moves both the left blood-side diaphragm 13 to the left side according to the transfer amount of the blood 100
Is being sent. After the blood 100 in the left blood chamber 11 is completely discharged, the state of FIG. 5 is restored. On the other hand, right blood chamber 1
2, the blood 100 is the same as the left blood chamber 11 in FIG.
Is being carried out. As is also known from the above, the blood delivery and inflow states of the right blood chamber 12 are the same except that they are in time opposite phase to the left blood chamber 11 described above.

Next, the function and effect of this example will be described. In the blood pump of this example, since there is a variable volume buffer chamber between the blood diaphragm and the driving diaphragm, the driving states of both diaphragms are independent. That is, the drive-side diaphragm is driven by the drive fluid, and the blood-side diaphragm is driven by the inflowing atrial pressure of blood.

That is, the amount of blood flowing into the blood chamber is controlled by the condition on the living body side called the atrial pressure. Therefore, there is no possibility of applying a negative pressure or the like that damages the living tissue or blood. In addition, it is compact and lightweight because it does not require a device to secure the blood volume difference.

The driving means in this example is a driving fluid transferred by a pump. Therefore, it is possible to easily install the casing and the pump in different places. Therefore, according to this example, it is possible to automatically adjust the difference in the blood delivery amount between the left and right blood pumps, and to provide a lightweight and small blood pump that does not cause damage to living tissue or blood. You can Although this example has been described with respect to the blood pump applied to the total replacement artificial heart, the present invention can also be applied to the auxiliary artificial heart used when assisting the natural heart until the weakened natural heart is recovered.

Embodiment 2 In this embodiment, as shown in FIG. 9, a hard shell damper 38, which is a fixed volume container without volume change, is used as a gas buffer portion of the blood pump 1. The volume of the hard shell damper 38 is 100 cc. Others are the same as in the first embodiment. Further, since the shape of the blood pump is bilaterally symmetric, details of the right blood chamber and the like will be omitted (same for the third and subsequent embodiments).

In this example, the molecular weight of the gas enclosed in the space between the buffer chamber 35 and the hard shell damper 38 does not change. Therefore, the amount of blood flowing into the blood chamber 11 decreases and the volume of the buffer chamber 35 increases. Therefore, the pressure in the buffer chamber 35 slightly tilts to the negative pressure side, so that the amount of blood flowing into the blood chamber 11 increases.
Therefore, it is possible to always set a large blood delivery amount. Others have the same effects as those of the first embodiment.

Example 3 In this example, as shown in FIG. 10, in the blood pump 1,
The tip 331 of the gas tube 33 connected to the buffer chamber 35 is extended to the outside of the human body 8 and opened to the atmosphere. Others are the same as in the first embodiment.

In this example, the gas 300 is synchronized with the expansion and contraction of the buffer chamber 35 from the tip of the gas tube 33.
Are flowed in or out. Therefore, the gas 300
The operating state of the blood pump 1 can be examined from the outside by monitoring the inflow and outflow states of blood from outside the body. Others have the same effects as those of the first embodiment.

Embodiment 4 In this embodiment, as shown in FIG. 11, a motor 29 is used as a driving means for the blood pump 1. The motor 29 has shafts 291, 29 that reciprocate left and right.
2, a pusher plate 293 for pushing and pulling the driving diaphragm 23 is provided at the end of the shaft 291. In addition, the motor 29 of the present embodiment includes the shaft 291, between the left and right casings 110 and 120.
292 are arranged inside the drive tubes 25 and 26, respectively. Others are the same as in the first embodiment.

In this example, since the diaphragm is directly and mechanically operated by the motor 29, responsiveness and efficiency are good. In addition, the other effects are similar to those of the first embodiment.

Example 5 In this example, as shown in FIG. 12, a tube-type blood pump 4 is used.
Is shown. In the tube type blood pump 4, a tubular blood chamber 41 having an inflow port 15 and a delivery port 17 is provided in a casing 410. Further, the blood chamber 41 is provided with a tubular blood side diaphragm 43 and a tubular drive side diaphragm 493, and a buffer chamber 495 is provided between them. A drive chamber 491 filled with the drive fluid 200 is provided between the drive-side diaphragm 493 and the casing 410. Others are the same as in the first embodiment.

In the blood pump 4 of this example, blood 10
In the inflow and outflow of 0, the blood side diaphragm 43 and the driving side diaphragm 493 operate similarly to the first embodiment. That is, the buffer chamber 495 expands and contracts in the casing 410 as the driving fluid 200 and the blood 100 move. Others are the same as in the first embodiment. In this example, since the tube type structure is adopted, the blood flow in the blood pump is good and the antithrombotic property is excellent. Also, in this example, the same effect as that of the first embodiment can be obtained.

Embodiment 6 This embodiment is a sack type blood pump 5 as shown in FIG. In the sac type blood pump 5, a sac-shaped blood chamber 51 having an inflow port 15 and a delivery port 17 is provided in a casing 510. The blood chamber 51 is provided with a sac-shaped blood side diaphragm 53 and a sac-shaped drive side diaphragm 593, and a buffer chamber 595 is provided therebetween. Between the drive side diaphragm 593 and the casing 510, the drive fluid 200
Is a drive chamber 591 filled with. Others are the same as in the first embodiment.

In the blood pump 5 of this example, blood 10
The inflow and outflow of 0 are performed by driving the blood side diaphragm 53 and the driving side diaphragm 593 as in the first embodiment. Also, in this example, the same effect as that of the first embodiment can be obtained.

[Brief description of drawings]

FIG. 1 is a structural explanatory view of a blood pump according to a first embodiment.

FIG. 2 is a structural explanatory view of a gas buffer unit according to the first embodiment.

FIG. 3 is a structural explanatory view of a driving pump in the first embodiment.

FIG. 4 is an explanatory diagram of how the blood pump according to the first embodiment is mounted and used.

FIG. 5 is an explanatory diagram of the operation of the blood pump according to the first embodiment.

FIG. 6 is an operation explanatory view of the blood pump following FIG. 5.

FIG. 7 is an operation explanatory diagram of the blood pump subsequent to FIG. 6;

FIG. 8 is an operation explanatory view of the blood pump following FIG. 7.

FIG. 9 is an explanatory diagram of a hard shell damper according to the second embodiment.

FIG. 10 is an explanatory view when the gas buffer unit in the third embodiment is open to the atmosphere.

FIG. 11 is an explanatory diagram of a mechanical drive unit according to the fourth embodiment.

FIG. 12 is an explanatory diagram of a tube blood pump according to a fifth embodiment.

FIG. 13 is an explanatory diagram of a suck blood pump according to the sixth embodiment.

FIG. 14 is an explanatory diagram of a conventional artificial heart device.

FIG. 15 is an explanatory diagram of a human circulatory system.

[Explanation of symbols]

 1. ． ． Blood pump, 100. ． ． Blood, 11, 12. ． ． Blood chamber, 110, 120. ． ． Casing, 13, 14. ． ． Blood side diaphragm, 2. ． ． Pump, 200. ． ． Driving fluid, 21, 22. ． ． Drive room, 23, 24. ． ． Drive side diaphragm, 29. ． ． Motor, 300. ． ． Air, 31, 32. ． ． Gas buffer, 35, 36. ． ． Buffer chamber, 4. ． ． 4. Tube type blood pump, ． ． Suck blood pump,

 ─────────────────────────────────────────────────── ─── Continuation of front page (72) Toru Masuzawa, 5-7 Fujishirodai, Suita City, Osaka Prefecture 1-7, National Cardiovascular Center Research Institute (72) Yoshiaki Matsuo, 5-7 Fujishirodai, Suita City, Osaka Prefecture National Cardiovascular Center Research Institute

Claims (12)

[Claims] 1. A blood pump having a casing, a diaphragm arranged in the casing, a blood chamber partitioned by the diaphragm for delivering blood, and a drive chamber having a driving means, wherein the diaphragm is a diaphragm. Consists of a blood side diaphragm located on the blood chamber side and a drive side diaphragm located on the drive chamber side, and a buffer chamber is interposed between them, and the buffer chamber is vented to the gas buffer section. A blood pump characterized in that it is operably connected. 2. The gas buffer section according to claim 1,
A blood pump characterized by being a flexible volume-variable container capable of changing volume. 3. The gas buffer section according to claim 1, wherein:
A blood pump, which is a fixed volume container that does not change in volume. 4. The gas buffer according to claim 1,
A blood pump characterized by being the atmosphere. 5. The blood pump according to claim 1, wherein the drive means is a pump which intermittently delivers a drive fluid to the drive chamber. 6. The blood pump according to claim 1, wherein the driving means is a motor that mechanically drives the driving device. 7. The blood pump according to claim 1, wherein the blood chamber is a tube type. 8. The blood pump according to claim 1, wherein the blood chamber is a sack type. 9. The method according to claim 1, wherein there are two casings on the left and right sides, the drive means is disposed between them, and each casing has the blood side diaphragm and the drive side diaphragm. And a blood pump. 10. The blood pump according to claim 1, wherein the number of the casings is one. 11. The blood pump according to claim 1, wherein the blood side diaphragm is composed of a plurality of laminated sheets. 12. The blood pump according to claim 1, wherein the drive-side diaphragm is composed of a plurality of laminated sheets.