JP2557150B2 - Heart-lung machine - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a heart-lung machine mainly used for open heart surgery, and more specifically, it can be set near a patient and has a blood filling amount in an extracorporeal blood circulation circuit and blood accompanying extracorporeal circulation. The present invention relates to an artificial heart-lung machine capable of minimizing the amount of hemolysis.

[0002]

2. Description of the Related Art Conventionally, an artificial heart-lung machine which substitutes the heart function and the lung function of a patient during the open-heart surgery has been required. The blood processing apparatuses described in JP-A-2-41172 and JP-A-2-95378 have been proposed. The centrifugal pump incorporated in the blood processing apparatus described in the publication can rotate an impeller in a pump chamber having an inlet and an outlet to deliver the blood supplied into the pump chamber to an artificial lung. ing.

However, if the conventional well-known centrifugal pump is directly applied to the artificial heart-lung machine, the following problems remain. For example, as shown in FIG. 19, an impeller including a cylindrical pedestal 201 having a conical upper end surface and a plurality of blades 202 radially provided on the outer peripheral surface thereof is provided in the space of the housing 200. When a centrifugal pump having a structure in which blood flows like a blood flow 204 in the drawing when the shaft 203 is rotated by a motor (not shown) is directly applied to an artificial heart-lung machine, this blood pump produces a vortex 205 near the outer periphery of the pedestal 201. It is generated and exerts a very large stress on the blood cells, so that the blood cells are destroyed and hemolysis occurs.

Further, as shown in FIG. 20, the housing 2
The pedestal 20 that is substantially conical in its entirety in the space 06
7 and a plurality of plate-shaped blades 20 radially provided on the curved surface from a position separated from the apex of the pedestal 207 by a certain distance.
When the shaft 209 is rotated by a motor (not shown), blood flows in the blood flow 21 in the figure.
When the centrifugal pump having a structure like 0 is directly applied to the heart-lung machine, the bottom surface of the pedestal 207 has an area enough to cover almost the entire inner bottom surface of the housing 206 housing the pedestal 207. Although no eddy current is seen as in the blood pump shown in FIG.
The occurrence of hemolysis cannot be effectively suppressed to a satisfactory level, and the blood ejection efficiency is not sufficient. Furthermore, since the blade 208 is a curved plate (as viewed from above), there is a problem that it is difficult to manufacture the blade 208 when it is integrally formed with the pedestal 207.

The present invention has been made to improve the above circumstances. That is, the object of the present invention is small and can be easily set beside the patient, and the blood filling amount of the extracorporeal blood circulation circuit can be minimized.
Moreover, it is an object of the present invention to provide an artificial heart-lung machine that can minimize the amount of hemolyzed blood in the extracorporeal circulation.

[0006]

The present invention according to claim 1 for achieving the above object comprises a gas permeable hollow fiber bundle in a case having a blood inlet and a blood outlet. The artificial lung and an impeller having a plurality of blades on the curved surface of the substantially conical pedestal, which are erected substantially radially from a position spaced apart from the apex of the pedestal by a fixed distance, are provided inside the housing, and the bottom surface of the pedestal is The housing is formed into a circular shape having a diameter of 30 to 55 mm, which covers almost the entire inner bottom surface of the housing, and the plurality of blades are straight plates each having an entrance angle of 20 to 50 degrees. The ratio (L / H) of the length L along the curved surface to the height H parallel to the rotation axis of the impeller at the radial tip of the radially arranged blades is 2.5 to 6.0. The blood is supplied between the hollow fibers. And a centrifugal pump for an artificial heart-lung machine and characterized by being configured integrally.

As a preferred mode of the artificial heart-lung machine, in the artificial heart-lung machine according to claim 1, the blood introducing port is provided on the outer peripheral surface of the case, and the blood introducing port serves as a blood introducing tube. An artificial heart-lung machine which projects to the outside and has the centrifugal pump attached to the blood introduction tube can be mentioned (claim 2). As another preferred aspect of the artificial heart-lung machine, in the artificial heart-lung machine according to claim 1, the case is a hollow fiber bundled so as to form an annular shape in a plane orthogonal to the axial center of the hollow fiber bundle. An example of an artificial heart-lung machine in which a bundle is housed, a blood inlet is provided on the inner peripheral surface of the case, and the centrifugal pump is attached to the blood inlet in the inner space area of the annular case (claim Item 3).

As another preferred embodiment of the artificial heart-lung machine, in the artificial heart-lung machine according to claim 3, there is an artificial heart-lung machine in which a heat exchanger is provided in an inner space region of the annular case. (Claim 4).
As another preferred embodiment of the artificial heart-lung machine, the artificial heart-lung machine according to claim 1, wherein the end face portion of the hollow fiber bundle is provided with a blood outlet and a centrifugal pump is housed in the case. A device can be mentioned (Claim 5).

As another preferred embodiment of the artificial heart-lung machine, in the artificial heart-lung machine according to claim 1, a centrifugal pump is attached to the outer peripheral surface of the case, and the case is directly connected from the centrifugal pump through the blood inlet. An artificial heart-lung machine in which blood is introduced into the hollow fiber bundle can be mentioned (claim 6). As another preferred aspect of the present invention, the artificial heart-lung machine according to claim 1 further including a blood reservoir and a heat exchanger can be cited (claim 7).

As another preferred embodiment of the present invention, the centrifugal pump having a diameter (R; unit: mm) of the pedestal and the ratio (L / H) satisfying the following relationship is provided: The artificial heart-lung machine of the present invention can be mentioned (Claim 8). 30 ≦ R ≦ 55, 2.5 ≦ L / H ≦ 6, L / H ≧ 0.133R-2.33, L / H ≦ 0.133R + 0.51 As another preferred embodiment of the present invention, the substantially conical shape The artificial heart-lung machine according to claim 1 may be provided with a centrifugal pump whose base has a blood circulation hole penetrating from its upper surface to its lower surface (claim 9).

[0011]

In the artificial heart-lung machine, oxygen gas is supplied to the hollow fiber bundle in the artificial lung. Since the artificial lung and the centrifugal pump are integrally formed, blood is introduced into the case through the blood inlet by the centrifugal pump, and the blood flows in the hollow fiber bundle or flows in the hollow fiber bundle. When the blood is discharged from the case by the centrifugal pump through the blood discharge port, the gas of the blood is exchanged through the hollow fiber bundle, and the oxygen concentration in the blood is increased. In this case, since the artificial lung and the centrifugal pump are integrally configured, the complexity of connecting the artificial lung and the blood pump with the tube as in the conventional case is eliminated, and the inside of the tube connecting the artificial lung and the centrifugal pump is eliminated. It is possible to eliminate the amount of blood filled in the container.

In the centrifugal pump used in this artificial heart-lung machine, since the bottom surface of the conical pedestal covers almost the entire inner bottom surface of the housing, no vortex flow of blood occurs and therefore stress applied to blood is small. . Further, in the centrifugal pump, the pedestal has a substantially conical shape, and the straight plate as the blade is erected on this curved surface, so that the blood flow is smooth, and the blood flowing in the centrifugal pump has, for example, a shearing force or a shear force. Generation of hemolysis is effectively suppressed because the stress due to the vortex is small and the bottom surface of the pedestal is formed into a substantially circular shape with a diameter of 30 to 55 mm.

Furthermore, in the centrifugal pump of the heart-lung machine according to the present invention, the angle formed by the tangent of the circle connecting the distal ends of the blood inflow side and the tangent of the blade on the blood inflow side, that is, the inlet angle β is 20 to 50 degrees. Therefore, the occurrence of hemolysis can be suppressed while maintaining good pump discharge efficiency.

The following examples can be given as examples of a mode in which the artificial lung and the centrifugal pump are integrally incorporated. That is,
The hollow fiber bundle is housed inside the cylindrical case, and the hollow fiber bundle is fixed inside the cylindrical case with resin inside both ends of the cylindrical case, and thus the hollow fiber bundle is housed inside the cylindrical case. Is provided with an oxygen gas inlet at one end thereof, and the other end of the cylindrical case is provided with a mixed gas outlet for discharging a mixed gas containing carbon dioxide mixed by exchanging gas with oxygen gas, Further, an artificial lung section provided with a blood introduction tube and a blood discharge tube projecting to the outside of the cylindrical case in each of the vicinity of the end on the outer peripheral surface of the cylindrical case, and a centrifugal pump section attached to the blood introduction tube. An embodiment may be mentioned. In such an embodiment, the artificial lung can be replaced by a conventional dialyzer or the like, and the device configuration can be simplified.

On the other hand, the case accommodates hollow fiber bundles which are bundled so as to have a circular shape in a cross section orthogonal to the axial center of the hollow fiber bundle, and a blood inlet is provided on the inner peripheral surface of the case. As the centrifugal pump is attached to the blood inlet in the inner space area of the annular case,
When the artificial heart-lung machine is configured, since the centrifugal pump is housed in the inner space area of the case, the overall shape is simplified and the usability is improved. Moreover, since a flow of blood is formed from the inside to the outside of the ring of the hollow fiber bundle bundled in a ring, the efficiency of gas exchange is significantly improved.

Further, if the heat exchanger is mounted in the inner space region of the case, the temperature control of blood becomes easy. When the configuration according to claim 5 is adopted so that the centrifugal pump is housed in the case while providing the blood discharge port on the end face portion of the hollow fiber bundle, the overall shape of the artificial heart-lung machine is also obtained by this configuration. It will be simple.

A centrifugal pump is mounted on the outer peripheral surface of the case, and the blood is directly introduced from the centrifugal pump into the hollow fiber bundle in the case through the blood inlet.
In the artificial heart-lung machine configured as described in claim 6, since the centrifugal pump is provided outside the case that houses the hollow fiber bundle, a centrifugal pump of a scale that is not restricted by the size of the case can be provided. Can be arbitrarily adjusted.

In any of the heart-lung machines according to the present invention, the blood taken out from the patient flows through the circulating blood circuit, passes through the artificial lung from the centrifugal pump, or after passing through the centrifugal pump from the artificial lung, and then through the circulating blood circuit. It flows and is collected in the patient's body.

In any of the above-mentioned modes, the flow of blood in a blood circuit using this artificial heart-lung machine is shown in FIG. 18, for example, and an artificial blood flow is shown in a blood circulation circuit 82 connected to a human heart 81. An artificial heart-lung machine in which a lung 83 and a centrifugal pump 84 are integrally combined and, for example, a blood reservoir 85 and a heat exchanger 86 are attached, and blood circulates between these devices and the heart 81 as indicated by an arrow. The centrifugal pump 84 is preferably connected to a drive shaft of a motor built in the controller 88 via a flexible shaft 87 as shown in FIG.

In still another embodiment of the present invention, the blood reservoir, an artificial lung having a gas permeable hollow fiber bundle in a case having a blood inlet and a blood outlet, and blood between the hollow fibers. An artificial heart-lung machine in which a centrifugal pump for supplying heat and a heat exchanger for heating blood are integrally incorporated can be given. In the artificial heart-lung machine, it is possible to reduce the area occupied by the blood reservoir, the blood pump, the blood warming device, and the blood tube connecting these, which were conventionally lined up on the side of the patient under operation. become. Therefore, the degree of freedom of the operator during the operation is increased. Further, the blood tube that had been crawled on the floor and other departments disappears, and at least only the blood tube that connects the artificial heart-lung machine of the present invention and the blood vessel of the patient is required, so that the filling blood amount of the blood circuit can be reduced accordingly. become. When the blood reservoir, the heat exchanger, the centrifugal pump, and the artificial lung are arranged in this manner in this manner, there is no unit having a pressure loss upstream of the blood reservoir in the blood flow, and thus it is easy to carry out drop blood removal. There are advantages. Since the heated blood is sent to the oxygenator after it has been heated by the heat exchanger, the oxygen-enriched blood in the oxygenator is heated by the heat exchanger so that air bubbles are generated. Will be reduced. By sending blood to the oxygenator by the centrifugal pump, conversely, the impact of the negative pressure on the blood in the oxygenator when the blood is sucked from the oxygenator by the centrifugal pump is reduced.

According to the present invention, since the small centrifugal pump and the specific lung are integrally combined with each other, it is possible to eliminate the harmful effects of the roller pump. Moreover, since the artificial heart-lung machine of the present invention is small, it can be easily set near the patient.

[0022]

Next, the present invention will be described based on embodiments with reference to the drawings.

FIG. 1 shows an artificial heart-lung machine according to an embodiment of the present invention. The heart-lung machine shown in FIG. 1 is configured by integrally combining the centrifugal pump 1 and the artificial lung 16 shown in FIG. 2 as main components. 2, 1 is a centrifugal pump, 1a is a blood inlet, 1b is a blood outlet, 1c is a housing, 11 is a space for accommodating an impeller, 12 is an inlet port for blood, 13 is an outlet port for blood, and 15 is Conical base, 14 blades made of straight plate, 7 shaft, 8 bearing, 9 V ring, 10a O
It is a ring.

A pedestal 15 is provided in the space 11 of the housing 1c.
When an impeller composed of a blade 14 and a blade 14 is rotatably housed and is rotated by a motor (not shown) via the shaft 7, blood flows into the space 11 from the inlet port 12,
It is configured to be discharged from the outlet port 13.
As shown in FIG. 3, the impeller has a structure in which a plurality of blades 14 are erected substantially radially on a curved surface of a base 15 having a substantially conical shape, and each blade 14 has a constant distance d from the top of the base 15. Is formed from a position distant from the base 15 to the vicinity of the outer peripheral edge of the base 15 .

The impeller may be made of any material as long as it is lightweight, has sufficient strength, and reduces hemolysis. Preferable examples thereof include plastics such as polycarbonate resin, hard vinyl chloride resin and polypropylene, and among them, polycarbonate resin is particularly preferable.

It is preferable that the pedestal 15 and the blades 14 are integrally molded using such plastic. It should be noted that even if it is called plastic, an acrylic resin or the like that is often used in conventional blood pumps is not preferable because it may crack. In the present invention, the bottom surface of the pedestal 15 is substantially circular with a diameter of 30 to 55 mm, and it covers almost the entire inner bottom surface of the housing 1. When the bottom surface of the pedestal 15 is formed in a substantially circular shape within the above range, hemolysis is usually 0.1 g / 100 liters or less, and sometimes 0.05 g.
/ 100 liters or less can be suppressed.

If the diameter of the bottom surface of the pedestal 15 is less than 30 mm, hemolysis is likely to occur.
Hemolysis is about 9 g / 100 liters. Also, pedestal 1
When the diameter of the bottom surface of No. 5 exceeds 55 mm, the priming amount becomes large, which is not preferable. As shown in FIG. 2, the apex angle α of the pedestal 15 having a substantially conical shape is preferably 120 to 160 degrees. This is because if the apex angle α is less than 120 degrees, the pump efficiency becomes poor, and if it exceeds 160 degrees, an unnecessary vortex flow is likely to occur when blood flows in.

The suitable blade 14 of the present invention satisfies the following conditions. First, the blade 14 is not a curved plate but a straight plate (straight plate). Like this one
If 4 is formed of a straight plate, the flow of blood will be smooth and less hemolysis will occur, and unlike the case of a curved plate, it can be easily integrally molded with the pedestal 15 .

The blades 14 are preferably formed on the curved surface of the pedestal 15 at equal intervals, and the number of blades is not particularly limited as long as it is plural, but normally about 6 blades are preferable. Next, as shown in FIG. 3, the blade 14 has a blood inflow side 14a.
Tangent to the circle (broken line) connecting the tips of the blood and the blood inflow side 14a
The angle formed by the tangent line of, that is, the entrance angle β is 20 to 50
Degree, preferably in the range of 20 to 30 degrees.

When β is in this range, the occurrence of hemolysis can be suppressed while maintaining good pump discharge efficiency. When β is less than 20 degrees, the pump efficiency is deteriorated, which is not preferable, and when β exceeds 50 degrees, the amount of hemolysis is increased, which is also not preferable.

Furthermore, as shown in FIG. 5, the blade 14 has a length L along the curved surface of the pedestal 15 and a height H parallel to the rotation axis of the impeller at the radial tip of the blade arranged radially. The ratio L / H must be in the range 2.5-6. When this condition is satisfied, the centrifugal pump in the heart-lung machine of the present invention can maintain good discharge efficiency. On the other hand, if L / H is less than 2.5, the amount of hemolysis will increase, and if it exceeds 6 the pump efficiency will deteriorate, so
Neither is preferred.

In the more preferable blade 14, the diameter (R; unit is mm) of the pedestal and the ratio (L / H) satisfy the following relationship. The blades 14 satisfying the following relationships have good discharge efficiency of the pump and can prevent hemolysis. 30 ≦ R ≦ 55, 2.5 ≦ L / H ≦ 6, L / H ≧ 0.133R−2.33, L / H ≦ 0.133R + 0.51.

In the present invention, it is also preferable to satisfy the following conditions in addition to the above-mentioned conditions. First, regarding the blade 14,
In order to reduce hemolysis without giving a large shearing force to the blood flow, as shown in FIG. 4, the tip of the blood inflow side 14a forms a semicircle (when viewed from the direction perpendicular to the paper surface) in a semicircle (thickness T
If so, it is better that the radius T / 2) is formed to be round, and the blood outflow side 14b is also gradually loosened from the vicinity of the tip on the one side B where the blood flow strongly contacts when the impeller rotates in the A direction. It is better to be curved and have a rounded tip.

Next, in the heart-lung machine of the present invention,
It is preferable to make this device as compact as possible. To downsize the heart-lung machine, it is better to downsize the centrifugal pump. Therefore, for example, if it is desired to obtain a small centrifugal pump having a maximum blood flow of about 10 liters / minute, the blood inlet port 3 has a diameter C of about 10 mm, the outlet port 13 has a diameter D of 4 to 8 mm, and the pedestal 15 has a diameter of about 10 mm. Height h is 6 to 12 mm, gap l between the blade 14 and the inner wall of the housing 1 (L in lower case)
Is 0.8 to 1.5 mm, and the inclination angle γ of the inner wall of the housing is preferably about 30 degrees.

In the present invention, the centrifugal pump is not limited to the above embodiment. For example, the pedestal 15 may be provided with any number of blood circulation holes penetrating from the upper surface to the lower surface thereof. FIG. 6 shows a pedestal 15 provided with two blood circulation holes 15a, 15a as an example thereof.

In FIG. 1, the housing 1 may be divided into an upper housing 1d and a lower housing 1e, and the upper housing 1d may be used as a cap so that the housings can be detachably combined. Further, as a sealing method, an oil seal, a mechanical seal, or a modification of these can be adopted in addition to the V ring 9 and the O ring 10a.

The shaft 7 of the centrifugal pump 1 is shown in FIG.
As shown in, it is connected to the control console 2 via a flexible shaft. That is, as shown in FIG. 1, 2 is a control console in which a motor 3 is built in a housing 4, and the control console 2 is connected to a centrifugal pump 1 via a flexible shaft 5 as described below.

That is, one end of the flexible shaft 5 is connected to the shaft 7 of the centrifugal pump 1, and the other end of the flexible shaft 5 is connected to the rotary shaft 6 of the motor 3 in the control console 2. As the flexible shaft 5, a flexible shaft having flexibility is used so that the axial direction can be freely changed.

In the above structure, when the motor 3 rotates, the rotational force is transmitted to the centrifugal pump 1 via the flexible shaft 5, and the centrifugal pump 1 operates. On the contrary, when the rotation of the motor 3 is stopped, the centrifugal pump 1 also stops operating via the flexible shaft 5. On the other hand, in FIG. 1, reference numeral 16 denotes an artificial lung integrally combined with a centrifugal pump, in which a hollow fiber bundle 18 made of a thermoplastic resin is loaded in a tubular casing 17 having both ends having a larger diameter than the other portions. Has been done.

Reference numerals 19a and 19b denote a pair of supports for fixing both ends of the hollow fiber bundle 18 to both ends of the tubular casing 17, and 20a and 20b are caps attached to both ends of the tubular casing 17. On the peripheral side surface of the cylindrical casing 17, a warmer 10 for keeping blood near the body temperature is attached.

The blood discharge port 1b of the centrifugal pump 1 is provided on the peripheral side of the cylindrical casing 17 and near one end thereof.
Is connected, and a blood discharge port 21a is formed to project near the other end. The supports 19a and 19b are made of synthetic resin and have a disk shape with a thickness substantially the same as that of the cylindrical casing 17, and both ends of the hollow fiber bundle 18 are solidified together, and a blood flow path and a gas flow path are formed. To distinguish. The open end of the hollow fiber bundle 18 is exposed on the outer surface of the supports 19a and 19b.

An oxygen gas inlet 22b is provided in the cap 20a.
Is formed in a protruding manner, and the cap 20b has a mixed gas discharge port 2 for discharging a mixed gas of oxygen gas and carbon dioxide gas.
2a is formed so as to project. As shown by the arrow in FIG. 1, the blood passes through the blood discharge port 1b of the centrifugal pump 1, passes through the hollow fiber bundle 18, and is discharged from the blood discharge port 21a.

Further, the oxygen gas enters the cap 20a from the oxygen gas inlet 22b as shown by the arrow, flows inside each hollow fiber in the hollow fiber bundle 18 in the direction opposite to the blood, and the mixed gas exhaust port is formed. It is discharged as a mixed gas from 22a. Carbon dioxide in blood flowing outside the hollow fiber is exchanged with oxygen gas inside through the wall of the hollow fiber.

In the artificial heart-lung machine according to the above-mentioned embodiment, since the artificial lung 16 and the centrifugal pump 1 as the centrifugal pump are integrally combined, the device itself is extremely miniaturized.
It is lightweight and can be easily set on the patient's bedside. And since it is not necessary to connect each of the main components of the heart-lung machine with a tube made of vinyl chloride resin, the burden on the operator is remarkably reduced, and unlike the roller pump, the centrifugal pump 1 causes almost no hemolysis. Since the centrifugal pump 1 and the heart-lung machine 16 are not connected by reciprocating the tube, the effect of significantly reducing the blood filling amount of the extracorporeal blood circulation circuit can be achieved.

However, the present invention is not limited to the above embodiment. As another preferred embodiment of the present invention, the artificial heart-lung machine shown in FIGS. 7 to 16 can be adopted. First, FIG.
The heart-lung machine shown in FIG. 8 has a bottomed inner cylindrical body 24 inserted into a cylindrical casing 23 having both openings closed except for a part thereof so as to share the central axis of the casing. And has a closed space 23a between the inner wall of the tubular casing 23 and the outer wall of the inner tubular body 24.

The closed space 23a has an annular shape (or a donut shape) when viewed in a plane orthogonal to the central axis of the casing 23. In FIG. 7, the inner cylinder 24 is provided inside the casing 23 with the bottom portion 24a of the inner cylinder body 24 facing up and the opening 24b thereof facing down. A centrifugal pump chamber 25 is provided outside the bottom portion 24a.
Is provided. The centrifugal pump chamber 25 has blood inlets 26a on both sides thereof.
It is continuous with the closed space 23a by a. The centrifugal pump chamber 25 is also provided with a blood introduction tube 27 at the top thereof.

Inside the centrifugal pump chamber 25, a pedestal 28a having a substantially conical shape and a plurality of impellers 28b standing on the conical surface are housed. The pedestal 28a is a rotary shaft 28c that penetrates the bottom portion 24a.
Supported by. The rotary shaft of the rotary shaft 28c has a bearing 28f on the outer periphery and also has a flexible joint 28f.
The flexible shaft 28e is connected via d, and the flexible shaft 28e is connected to the rotating shaft of the motor in the control console (not shown). On the other hand, both ends of the closed space 23a are supported by the supports 29a, 2 respectively.
The hollow fiber bundle 30 fixed by 9b is filled. The hollow fiber bundle 30 has an annular horizontal cross section in FIG. 3 of the closed space 23a, and therefore the hollow fiber bundle 30 also has an annular horizontal cross section.

Small chambers 31a and 31b are formed between the supports 29a and 29b and both ends of the tubular casing 23. The small chamber 31b is provided with an oxygen gas inlet 32b, and the small chamber 31a is provided with oxygen and carbon dioxide. A mixed gas discharge port 32a for discharging the mixed gas with the gas is provided. Note that 214b
Is a blood outlet provided in the cylindrical casing near the upper portion of the support body 29a. Also in this embodiment, a centrifugal pump having the same structure as that of the embodiment shown in FIG. 1 is adopted as the centrifugal pump.

The heart-lung machine according to this embodiment operates as follows. That is, blood is sent from the blood introduction tube 27 into the pump chamber 25. Rotation of the base 28 impeller 2
8b rotates. The blood that has been sent is the blood inlet 26a
To enter the closed space 23a. In the closed space 23a, oxygen gas flows from the oxygen gas inlet 32b to the small chamber 31.
It is introduced into the small chamber 31b and passes through the hollow fiber bundle 30 from the small chamber 31b to reach the small chamber 31a. The blood sent into the closed space 23a flows between the hollow fibers. In this embodiment, blood and oxygen gas come into countercurrent contact through the hollow fibers. Gas exchange in blood takes place through the membrane of hollow fibers. That is, carbon dioxide in blood is supplied to the hollow fibers, and oxygen gas is supplied to the blood. The mixed gas containing carbon dioxide reaches the small chamber 31a and is discharged from the mixed gas discharge port 32a. The blood rich in oxygen is discharged from the blood discharge port 29b and returned to the human body.

The artificial heart-lung machine shown in FIG. 9 and FIG.
Cylindrical casing 3 with both openings closed except for a part
3 has an inner cylindrical body 34 inserted so as to share the central axis of the casing 33.
Between the inner wall of the inner cylindrical body 34 and the outer wall of the inner cylindrical body 34.
Have. The closed space 33a has an annular shape (donut shape) when viewed in a plane orthogonal to the central axis of the casing 33, and is the same as in the artificial heart-lung machine shown in FIGS. 7 and 8.

In FIG. 9, the inner cylinder 34 is provided with the bottom portion 34a of the inner cylinder 34 facing downward. The bottom portion 34a is formed in a conical shape toward the inside of the inner cylindrical body 34, and at the tip of the conical shape, the blood introducing hole 34b is formed.
Is open. A centrifugal pump chamber 34c is provided outside the bottom portion 34a (downward in FIG. 9). The centrifugal pump chamber 34c has a blood introducing port 34d that opens in a ring shape on its side portion, and is connected to the closed space 33a by the blood introducing port 34d. Also, this inner cylinder 3
Inside the coil 4, a coil 38 through which a heat exchange medium flows is provided. A blood introducing tube 41 and a heat medium introducing port 45 are provided at an end portion of the inner cylindrical body 34 which faces the bottom portion 34a.
A heat exchange medium discharge port 46 is also provided.

On the other hand, inside the centrifugal pump chamber 34c, a pedestal 34e having a substantially conical shape and a plurality of impellers 34f standing on the conical surface are housed. The pedestal 34e is supported by a rotating shaft 34g that penetrates the bottom portion 34k of the centrifugal pump chamber 34c. The rotary shaft 34g has a bearing 34j on the outer circumference and is connected to a flexible shaft 34i via a flexible joint 34h. The flexible shaft 34i is connected to a rotary shaft of a motor in a control console (not shown).

On the other hand, in the closed space 33a, a hollow fiber bundle 35 having both ends fixed by supports 36a and 36b, respectively.
Is filled. The hollow fiber bundle 35 is provided in the closed space 3
Since the horizontal section of 3a in FIG. 5 has an annular shape,
The horizontal cross section of the hollow fiber bundle 35 is also annular. Small chambers 37a and 37b are formed between the supports 36a and 36b and both ends of the cylindrical casing 33, respectively.
An oxygen gas inlet 44 is provided at a, and a mixed gas outlet 43 of oxygen and carbon dioxide is provided at the small chamber 37b.

The heart-lung machine according to this embodiment operates as follows. That is, blood is introduced from the blood introduction tube 41 into the inner cylindrical body 34. Since the heat medium flows through the coil 38 in the inner cylinder 34, the introduced blood is heated to an appropriate temperature. The heated blood enters the centrifugal pump chamber 34c through the blood introducing hole 34b. Rotating impeller 3
4f causes the blood to enter the closed space 33a through the blood inlet 34d.

In the closed space 33a, oxygen gas is supplied from the oxygen gas inlet 44 to the small chamber 37a, and the small chamber 37a
From a to the small chamber 37b through the hollow fiber bundle 35. The blood sent into the closed space 33a flows between the hollow fibers. Also in this embodiment, a centrifugal pump having the same structure as that of the embodiment shown in FIG. 1 is adopted as the centrifugal pump.

In this embodiment, blood and oxygen gas come into countercurrent contact with each other through the hollow fiber. Gas exchange in blood takes place through the membrane of hollow fibers. That is, carbon dioxide in blood is supplied to the hollow fibers, and oxygen gas is supplied to the blood. The mixed gas containing carbon dioxide gas reaches the small chamber 37b and is discharged from the mixed gas discharge port 43. The blood rich in oxygen is discharged from the blood outlet 42,
Returned to the human body.

The heart-lung machine shown in FIGS. 11 and 12 has the same structure as the heart-lung machine shown in FIGS. 9 and 10, except that the blood reservoir 47 is attached to the heart-lung machine shown in FIGS. 9 and 10. Have. In the artificial heart-lung machine shown in FIGS. 11 and 12, the blood inlet 41 is connected to the bottom of the blood reservoir 47. Also in this embodiment, the centrifugal pump having the structure shown in FIG. 2 is adopted.

This artificial heart-lung machine has the same operation as the artificial heart-lung machine shown in FIGS. 9 and 10 except that the blood extracted from the human body is temporarily stored in the reservoir 47. However, since the blood is temporarily stored in the reservoir 47, the centrifugal pump does not run idle.

In the artificial heart-lung machine shown in FIGS . 13 and 14, the hollow fiber bundle 49 is focused in the tubular casing 48. One end of the hollow fiber bundle 49 is supported by a support body 50a having an opening 49a at the center, and the hollow fiber bundle 4
The other end of 9 is fixed by a support 50b. Support 50
A funnel-shaped partition wall 55a is attached to the opening 49a of a,
A partition plate 55b is stretched on the cross section of the casing that faces the funnel-shaped partition 55a.

In the casing 48, the partition 55a and the partition plate 55b form a centrifugal pump chamber 55. A blood outlet 54 is opened on the peripheral side surface of the casing 48 in the centrifugal pump chamber 55. Centrifugal pump room 55
A conical pedestal 55d supported by a support shaft 55c penetrating the partition wall plate 55b is disposed inside the pedestal 55d.
A plurality of impellers 55e are planted on the conical surface of d.
Also in this centrifugal pump, a pedestal having a specific diameter and blades having a specific size and shape as shown in FIG. 2 are employed.

A bearing 55g is provided on the support shaft 55c.
Is attached and the flexible joint 55f
Are connected, and have the same structure as the artificial heart-lung machine shown in FIGS. On the other hand, a small chamber 53a is formed by the support 50a and the partition wall 55a.
An oxygen gas inlet 51 is provided on the peripheral side surface of the casing 48 in 3a. On the other hand, the support 50b and the end surface of the casing 48 form a small chamber 53b. A mixed gas discharge port 52 of oxygen gas and carbon dioxide gas is provided on the peripheral side surface of the casing in the small chamber 53b. Reference numeral 56 denotes a blood inlet provided on the peripheral side surface of the casing 48 slightly above the support body 50b.

In the artificial heart-lung machine shown in FIGS. 13 and 14, blood is introduced into the casing 48 from the blood introducing port 56. The introduced blood passes between the hollow fiber bundles 49, collects in the opening 49a, and is introduced into the centrifugal pump chamber 55 through the opening 49a. In the centrifugal pump chamber 55,
Since the impeller 55e is rotating, the introduced blood is discharged from the blood discharge port 54.

On the other hand, oxygen gas is supplied from the oxygen gas inlet 51 to the small chamber 53a, and the hollow fiber bundle 49 is discharged from the small chamber 53a.
Through it, it reaches the small chamber 53b. In this artificial heart-lung machine, oxygen gas and blood come into countercurrent contact due to such a structure. Gas exchange in blood takes place through the membrane of hollow fibers. That is, carbon dioxide in blood is supplied to the hollow fibers, and oxygen gas is supplied to the blood. The mixed gas containing carbon dioxide gas reaches the small chamber 53b, and the mixed gas discharge port 52
Emitted from. The blood rich in oxygen is discharged from the blood discharge port 54 and returned to the human body.

The heart-lung machine shown in FIGS. 15 and 16 has an artificial lung, a centrifugal pump, and a heat exchanger integrally incorporated, like the heart-lung machine shown in FIGS. 9 and 10. That is, in the artificial lung, the hollow fiber bundle 58 is contained in the tubular casing 57, and the first small chamber 59a and the second small chamber 59b are provided between the both ends of the hollow fiber bundle 58 and the both ends of the tubular casing 57. The hollow fibers are fixed by the supports 60a and 60b to be formed, and both ends of each hollow fiber are open to the first small chamber 59a and the second small chamber 59b.

An oxygen gas inlet 61 is opened at the end surface of the casing 57 forming the inner wall of the first small chamber 59a.
A mixed gas discharge port 63 for discharging a mixed gas of oxygen gas and carbon dioxide gas is opened at the other end surface of the casing 57 forming the inner wall of the first small chamber 59a. This casing 57
A blood introduction hole 65a is opened on the circumferential side surface of the substrate at a position closer to the support 60b. A blood discharge port 62 is provided on the peripheral side surface of the casing 57 from the support 60a.

On the outer peripheral surface of the tubular casing 57, another tubular casing 64 incorporating a centrifugal pump and a heat exchanger is mounted adjacent to the tubular casing 64. The hole 65a is shared.
Also in this centrifugal pump, a pedestal having a specific diameter and blades having a specific size and shape as shown in FIG. 2 are employed. Inside one end of the tubular casing 64, a funnel-shaped partition wall 65b, a partition plate 65c stretched in the cross-sectional direction of the tubular casing 66, and the blood introduction hole 65 are provided.
A centrifugal pump chamber 65d is formed with the peripheral surface of the casing having a.

As described above, this centrifugal pump chamber 6
5d and the casing 57 communicate with each other through the blood introducing hole 65a. In this centrifugal pump chamber 65d, a pedestal 65e which is rotatably supported by a rotary shaft 65h penetrating the partition wall 65c in a watertight manner and which is formed in a conical shape is built-in. It has been planted.

On the other hand, a heat exchanger 66 is provided in the cylindrical casing 64 adjacent to the centrifugal pump chamber 65d. A bearing 65i is attached to the rotary shaft 65h. Funnel-shaped partition wall 65b in the centrifugal pump chamber 65d
Has an opening at a support body 68b stretched in the cross-sectional direction of the tubular casing 64, and another support body 68a is provided so as to face the support body 68b.
Is stretched in the cross-sectional direction.

This support 68b and the funnel-shaped partition wall 65
The fourth small chamber 67b is formed by b and the peripheral side surface of the tubular casing 64, and the third small chamber 67a is formed by the other support 68a, the end surface of the tubular casing 64, and the peripheral side surface of the tubular casing 64. . A heat exchange medium introduction port 70 is provided on the peripheral side surface of the cylindrical casing 64 in the fourth small chamber 67b, and a heat exchange medium discharge port 72 is provided on the peripheral side surface of the cylindrical casing 64 in the third small chamber 67a. ing.

A plurality of pipes 6 made of metal such as stainless steel are provided between the pair of supports 68a and 68b.
9 is suspended, and the end openings of the pipes 69 open in the small chambers 67a and 67b, respectively. Support 68a
On the peripheral side surface of the cylindrical casing 64 located between the cylindrical casing 64 and the support body 68b.
1 is provided.

In the artificial heart-lung machine shown in FIGS. 15 and 16, the pedestal 65e is rotated as in the artificial heart-lung machines shown in FIGS. Also in this centrifugal pump, a pedestal having a specific diameter and blades having a specific size and shape as shown in FIG. 2 are employed. The heat exchange medium is introduced into the fourth small chamber 67b from the heat exchange medium introducing port 70, passes through the pipe 69, and the third small chamber 67a.
And is discharged from the heat exchange medium discharge port 72. The oxygen gas is introduced into the first small chamber 59a through the oxygen gas inlet 61, passes through the fibers of the hollow fiber bundle 58, and then passes through the second small chamber 59a.
It reaches b and is discharged from the mixed gas discharge port 63.

Therefore, the blood drawn from the human body is introduced into the cylindrical casing 64 from the blood introduction port 71 and heated to an appropriate temperature by the pipe 69. The heated blood enters the centrifugal pump chamber 65d through the opening 65f,
It is introduced into the casing 57 through the blood introduction hole 65a by the impeller 65f. In the casing 57, blood is exchanged with oxygen gas passing through the hollow fibers while passing between the hollow fibers.

As a result of this gas exchange, the blood having an increased oxygen concentration is discharged from the blood discharge port 62 to the outside of the casing 57 and returned to the human body through a blood circuit (not shown). As a result of gas exchange, oxygen gas containing carbon dioxide gas is discharged from the mixed gas discharge port 63.

The artificial heart-lung machine shown in FIG. 17 has a bottomed inner portion inserted so as to share the central axis of the casing 90 in a cylindrical casing 90 in which both openings are closed except for a part thereof. It has a tubular body 91, and has a closed space 92 between the inner wall of the tubular casing 90 and the outer wall of the inner tubular body 91.

The closed space 92 has an annular shape when viewed in a plane orthogonal to the central axis of the casing 90.
In FIG. 17, the inner cylinder 91 is provided inside the casing 90 with the bottom 91a of the inner cylinder 91 facing upward and the opening 91b thereof facing downward. Bottom 91a
A centrifugal pump chamber 93 is provided outside the. The centrifugal pump chamber 93 has a blood discharge port 93a that opens in a ring shape on both sides thereof, and is connected to the closed space 92 by the blood discharge port 93a. Centrifugal pump room 93
Also has a blood inlet 93b at its top (a portion facing the bottom 91a). This blood inlet 93b
Has an opening in a bottom surface 90b of a cylindrical recess 90a whose center line is an extension of the center line of the inner cylinder 91, which is provided on the upper end surface of the cylindrical casing 90.

Inside the centrifugal pump chamber 93, there is housed a substantially conical pedestal 94a and a plurality of impellers 94b standing on the conical surface. The pedestal 94a is supported by a rotary shaft 95 that penetrates the bottom portion 91a. The rotary shaft 95 has a bearing 95a on the outer periphery and is connected to a flexible shaft (not shown) via a flexible joint 95b, and the flexible shaft is connected to a rotary shaft of a motor in a control console (not shown). . On the other hand, the closed space 92 is filled with a hollow fiber bundle 97 whose both ends are fixed by supports 96a and 96b, respectively. Since the hollow fiber bundle 97 has an annular horizontal cross section in FIG. 13 of the closed space 92, the hollow fiber bundle 97 also has an annular horizontal cross section.

Small chambers 98a and 98b are formed between the supports 96a and 96b and both ends of the tubular casing 90. The small chamber 98a has an oxygen gas inlet 99a and the small chamber 98b has oxygen and carbon dioxide. A mixed gas discharge port 99b for discharging the mixed gas with the gas is provided. Note that 99c is a blood outlet provided in the tubular casing 90 near the upper portion of the support 96a. Also in this centrifugal pump,
As shown in FIG. 2, a pedestal having a specific diameter and a blade having a specific size and shape are used.

A blood reservoir with a heat exchanger is attached to the blood inlet 93b in the centrifugal pump chamber 93. That is, the blood reservoir 100 includes a large-diameter blood storage part 100a and a small-diameter heat exchanger storage part 100b provided at the bottom of the blood storage part 100a and partially inserted into the recess 90a. The upper end opening of the blood reservoir 100a is closed by a lid member 101 provided with a blood inlet 101a. A coil 102, through which a heat exchange medium flows, is housed inside the heat exchanger housing portion 100b.

The heart-lung machine according to this embodiment operates as follows. That is, the blood is introduced into the blood reservoir 100 from the blood inlet 101a. Blood reservoir 1
The blood from the blood circuit connected to the blood vessel of the patient may be stored at 00, as well as the aspirated blood generated during the operation. The blood introduced into the blood reservoir 100 is heated to a predetermined temperature in the heat exchanger housing portion 100b, and the blood is sent from the blood introducing port 93b into the centrifugal pump chamber 93.
The rotation of the pedestal 94a causes the impeller 94b to rotate. The blood that has been sent passes through the blood discharge port 93a and the closed space 92
Get in. In the closed space 92, oxygen gas is introduced into the small chamber 98a from the oxygen gas inlet 99a, and the small chamber 98a
Through the hollow fiber bundle 97 to reach the small chamber 98b. The blood sent into the closed space 92 circulates between the hollow fibers. In this embodiment, blood and oxygen gas come into countercurrent contact through the hollow fibers. Gas exchange in blood takes place through the membrane of hollow fibers. That is,
Carbon dioxide in blood is supplied to the hollow fibers, and oxygen gas is supplied to the blood. The mixed gas containing carbon dioxide reaches the small chamber 98b and is discharged from the mixed gas discharge port 99b. The oxygen-rich blood is discharged from the blood discharge port 96b and returned to the human body.

As is apparent from the above embodiments, in the present invention, since the artificial lung and the centrifugal pump are integrated, the artificial lung and the blood pump are connected by the blood tube as in the conventional case. Freed from the complexity. In the artificial heart-lung machine of the present invention, the blood pump integrated with the artificial lung is a centrifugal pump, and further, since it has a pedestal having a bottom surface of a specific size and a blade of a specific size and shape, the hemolysis phenomenon is suppressed to a significantly small level. It Further, since there is no blood tube between the centrifugal pump and the artificial lung, and since the artificial lung is brought near the bed, the blood filling amount can be reduced.

Also, the power transmission system of the centrifugal pump used in the present invention is not limited to the above-mentioned embodiment, and it is basically arbitrary, but the above-mentioned one embodiment is adopted in view of minimizing the bedside owned space. As in the example, it is preferable to connect the output shaft of the drive motor built in the control console and the rotary shaft of the centrifugal pump by a detachable flexible shaft.

The centrifugal pump may be integrally combined with the front stage of the artificial lung or the latter stage of the artificial lung. Further, the artificial lung itself is not limited to the above-mentioned embodiment, and any type that uses a hollow fiber capable of gas exchange between oxygen gas and carbon dioxide gas in blood can be used in the present invention.

Example 1 Using the blood pump of the present invention constructed as shown in FIGS. 2 to 5, a hemolysis test was conducted to measure the amount of hemolysis. The following impeller was used as the impeller of the blood pump. Impeller Material ・ ・ ・ ・ ・ ・ Polycarbonate resin Pedestal outer diameter ・ ・ ・ ・ 36mm Pedestal height ・ ・ ・ 7.5mm Blade entrance angle ・ ・ ・ 20 degrees Blade length L and blade height Ratio with H (L / H) ... 3.5 Number of blades ... 6 pieces.

The hemolysis test was carried out under the following conditions. (B) The differential pressure across the pump was kept constant at 100 mmHg. (B) The pump flow rate was measured every 1 liter / minute for 1 to 5 liters / minute. The pump flow rate range is the most used range for extracorporeal circulation by the cardiac assist device after open heart surgery. (C) During continuous operation for 5 hours, sampling is performed every 30 minutes, and the amount of free hemoglobin in plasma is measured by the SLS hemoglobin method, and the hemolysis index (IH = Index of Hemoly
sis) was calculated. In addition, I. H is the pump discharge rate 100
Represents the amount of change in free hemoglobin per liter,
The permissible amount for biological application is set to 0.1 g or less. The results are shown in FIG.

Next, the blood pump was operated and the output characteristics (pump discharge amount, differential pressure across the pump) were examined. The results are shown in FIG.

Comparative Example 1 A hemolysis test was conducted in the same manner as in Example 1 using the conventional blood pump shown in FIG. 19, and pump output characteristics were examined. The material and dimensions of the impeller are the same as in the first embodiment. The results of the hemolysis test are shown in FIG. 21, and the pump output characteristics are shown in FIG.

Comparative Example 2 Using the conventional blood pump shown in FIG. 20, a hemolysis test was conducted in the same manner as in Example 1, and the pump output characteristics were examined. The material and dimensions of the impeller are the same as in the first embodiment. The results of the hemolysis test are shown in FIG. 21 and the pump output characteristics are shown in FIG.
4 shows.

Example 2 Using the blood pump of the present invention constructed as shown in FIGS. 2 to 5, a hemolysis test was conducted to measure the amount of hemolysis. The following impeller was used as the impeller of the blood pump. Impeller material: Polycarbonate resin Pedestal outer diameter: 50 mm Pedestal height: 10 mm Blade entrance angle: 20 degrees Blade length L and blade height H Ratio (L / H) ... 5.3 Number of blades ... 6 sheets A hemolysis test was conducted in the same manner as in Example 1, and the output characteristics of the pump were examined. The results are shown in FIGS. 21 and 25 together with the results of Example 1 above.

(Evaluation) As shown in FIG. 21, in the conventional blood pump, the hemolytic amount increases as the pump flow rate decreases, whereas in the blood pump of the present invention,
I.V. in all ranges up to 5 liters / min. H. The value of 0.1 g / 100 liters, which is an allowable value, is sufficiently achieved. The centrifugal pumps in the above-described examples show a remarkable decrease in hemolytic amount at a low flow rate of 2 liter / min or less as compared with the conventional blood pump.

As a result, it can be confirmed that the centrifugal pump in the above-described embodiment has a sufficiently reduced hemolytic amount as compared with the conventional blood pump, and can be safely used over a wide flow rate range. Further, as is clear from FIGS. 22, 23, 24, and 25, the blood pump of the present invention is superior in pump discharge efficiency to the conventional blood pump. Therefore, by integrating the centrifugal pump exemplified by the centrifugal pump shown in the above embodiment with the artificial lung,
Provided is an artificial heart-lung machine in which the amount of hemolysis is remarkably reduced, pump discharge efficiency is excellent, and gas exchange efficiency is high.

[0091]

In the artificial heart-lung machine according to the present invention, since the artificial lung and the centrifugal pump having a specific structure are integrally combined, the apparatus itself is extremely miniaturized and lightweight, and is easily set on the bedside of the patient. can do.

Since the work of connecting the artificial lung and the centrifugal pump one by one as in the conventional case is no longer required, the burden on the operator is significantly reduced.

Further, unlike a roller pump or the like, the centrifugal pump hardly causes hemolysis, and since the centrifugal pump and the artificial lung are not connected by reciprocating the tube,
It is possible to significantly reduce the blood filling amount of the extracorporeal blood circulation circuit while suppressing the hemolytic phenomenon to a significantly small level.

[Brief description of drawings]

FIG. 1 is an explanatory diagram of a heart-lung machine according to an embodiment of the present invention.

FIG. 2 is a partial sectional front view showing an example of the blood pump of the present invention.

FIG. 3 is a plan view showing an example of an impeller of the blood pump of the present invention.

FIG. 4 is a plan view showing blades of an impeller in an example of the blood pump of the present invention.

5 is a configuration diagram showing a main part of the blood pump of FIG. 1. FIG.

FIG. 6 is a front view showing a base of an impeller in another example of the blood pump of the present invention.

FIG. 7 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 8 is a schematic perspective view of a heart-lung machine according to an embodiment of the present invention.

FIG. 9 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 10 is a schematic perspective view of a heart-lung machine according to an embodiment of the present invention.

FIG. 11 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 12 is a schematic perspective view of a heart-lung machine according to an embodiment of the present invention.

FIG. 13 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 14 is a schematic perspective view of a heart-lung machine according to an embodiment of the present invention.

FIG. 15 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 16 is a schematic perspective view of a heart-lung machine according to an embodiment of the present invention.

FIG. 17 is a schematic sectional view of a heart-lung machine according to an embodiment of the present invention.

FIG. 18 is an explanatory view showing a method of using the artificial heart-lung machine of the present invention.

FIG. 19 is a cross-sectional view showing an example of a conventional blood pump.

FIG. 20 is a cross-sectional view showing another example of a conventional blood pump.

FIG. 21 is a graph showing the results of a hemolysis test using the present invention and a conventional blood pump.

FIG. 22 is a graph showing pump output characteristics of the blood pump of the present invention.

FIG. 23 is a graph showing pump output characteristics of a conventional blood pump (Comparative Example 1).

FIG. 24 is a graph showing pump output characteristics of a conventional blood pump (Comparative Example 2).

FIG. 25 is a graph showing pump output characteristics of the blood pump of the present invention.

[Description of sign]

 1 Centrifugal Pump 2 Control Console 3 Motor 5 Flexible Shaft 6 Drive Shaft 7 Rotation Shaft 16 Artificial Lung

 ─────────────────────────────────────────────────── ─── Continued Front Page (72) Inventor Tatsuya Sasaki 11-10 Atago, Morioka, Iwate

Claims (9)

(57) [Claims] 1. An artificial lung comprising a gas permeable hollow fiber bundle in a case having a blood inlet and a blood outlet, and a plurality of blades on a curved surface of a substantially conical pedestal, which are constant from the apex of the pedestal. The housing is provided with impellers that are erected substantially radially from positions separated by a distance of 30 mm, and the bottom surface of the pedestal has a diameter of 30 covering substantially the entire inner bottom surface of the housing.
The blades are formed in a circular shape of ˜55 mm, and each of the plurality of blades is composed of a straight plate having an entrance angle of 20 to 50 degrees, and has a length L along the curved surface of the blades and the radial shape. Of the blades arranged in the radial direction at the tip in the radial direction and the height H parallel to the rotation axis of the impeller (L /
H) is 2.5 to 6.0, and is constructed integrally with a centrifugal pump that supplies blood between the hollow fibers. 2. The blood introducing port is provided on an outer peripheral surface of the case, and the blood introducing port serves as a blood introducing pipe and projects outward, and the centrifugal pump is attached to the blood introducing pipe. The artificial heart-lung machine according to 1. 3. The case contains a hollow fiber bundle bundled in an annular shape on a plane orthogonal to the axial center of the hollow fiber bundle, and a blood inlet is provided on the inner peripheral surface of the annular case. The heart-lung machine according to claim 1, wherein the centrifugal pump is attached to the blood inlet in an inner space region of the annular case. 4. The heart-lung machine according to claim 3, wherein a heat exchanger is provided in an inner space region of the annular case. 5. The heart-lung machine according to claim 1, wherein a blood discharge port is provided at an end surface portion of the hollow fiber bundle, and a centrifugal pump is housed in the case. 6. The centrifugal pump is mounted on the outer peripheral surface of the case, and the blood is directly introduced from the centrifugal pump into the hollow fiber bundle in the case through the blood introducing port.
The cardiopulmonary bypass device according to. 7. The heart-lung machine according to claim 1, further comprising a blood reservoir and a heat exchanger which are integrated with each other. 8. The heart-lung machine according to claim 1, further comprising a centrifugal pump having a diameter (R; unit: mm) of the pedestal and the ratio (L / H) satisfying the following relationship. ≦ 55, 2.5 ≦ L / H ≦ 6, L / H ≧ 0.133R−2.33, L / H ≦ 0.133R + 0.51 9. The heart-lung machine according to claim 1, wherein the substantially conical pedestal includes a centrifugal pump having a blood circulation hole that penetrates from the upper surface to the lower surface.