JP2888609B2 - Blood assist circulator - Google Patents

Description

Description: TECHNICAL FIELD The present invention relates to a blood-assisted circulator used for assisting cardiopulmonary function.

[Prior Art] Conventionally, methods of assisting blood circulation include a method using an arteriovenous bypass, a method using an assisted artificial heart, and an intra-aortic balloon pumping method (IABP method).

The method using an assisted artificial heart has the highest blood assisting and circulating effect, but requires the chest to be opened, the burden on the patient is large, and the operation is complicated. In addition, although the IABP method is easy to operate, blood is sent by inflation and deflation of a balloon inserted into the aorta, so that the amount that can be sent is small, and the assisting circulation effect is low. In this regard, the arteriovenous bypass method has a lower assisted circulation effect than the ventricular assist device, but does not require a thoracotomy, has less burden on the patient, and has a higher assisted circulation effect than the IABP method. ing.

The blood assisting circulator used for the arteriovenous bypass method includes a blood removal side blood tube, a blood pump, an artificial lung, and a blood removal side catheter having a blood removal side catheter which is inserted from a femoral vein and has a distal end placed in the right atrium. At least a blood tube is provided. Furthermore, as a blood pump,
A constant pressure pump (eg, a centrifugal pump) or a roller pump is used.

[Problems to be Solved by the Invention] However, the roller pump used in the above-described blood assisted circulatory device sends blood by squeezing a blood tube, and requires a blood reservoir in front of the pump. In addition, blood must be removed from the patient by a head, and a high flow rate cannot be obtained with a blood removal amount due to the head, so that the auxiliary circulation cannot be performed at a high flow rate.

On the other hand, in a blood assisting circulator using a centrifugal pump that is a constant-pressure pump, blood is sent by centrifugal force of the pump, so there is no need to provide a blood storage tank, and there is no need to remove blood by a head, and The auxiliary circulation circuit may be a closed circuit. For this reason, the auxiliary circulation of blood can be performed completely at a high flow rate. However, since the constant pressure pump sends blood at a substantially constant flow rate, it cannot provide pulsation unlike a roller pump. Patients in need of blood assisted circulation have inadequate cardiac function, as evidenced by their intended use.

Thus, the assisted circulation assists the heart function, particularly the cardiopulmonary function, partially circulates blood outside the body, and performs oxygenation of the blood to assist the cardiopulmonary function. In addition, the blood flow itself is reduced in such patients, and the present inventor considered that it is preferable to assist blood circulation to the coronary arteries surrounding the heart if possible.

Therefore, an object of the present invention is to provide a blood assisted circulating apparatus using an arteriovenous bypass method, and by using a constant pressure pump as a pump, a high flow rate and safe blood assisted circulation can be performed. An object of the present invention is to provide a blood-assisted circulator which gives a pulsation to a blood flow to be sent and can positively send blood to a coronary artery and can further reduce the burden on cardiac function.

[Means for Solving the Problems] What achieves the above object of the present invention is a blood removal side blood tube, a blood supply side blood tube, and a structure between the blood removal side blood tube and the blood supply side blood tube. A blood assist circuit having a constant pressure pump and an artificial lung provided in the heartbeat detector,
A blood-assisted circulator having a blood flow control means attached to the blood-assisted circulatory circuit downstream of the constant-pressure pump and operating in response to a heartbeat detection signal of the heartbeat detector.

And it is preferable that the flow control means is attached to the blood supply side blood tube. Further, it is preferable that the flow rate control means opens and closes the blood assist circuit in response to a heartbeat detection signal of the heartbeat detector. Further, it is preferable that the flow control means operates in synchronization with a heartbeat detection signal of the heartbeat detector. Further, the blood assisting and circulating device may include an intra-aortic balloon catheter, and balloon control means for inflating and deflating the balloon of the intra-aortic balloon catheter in response to a heartbeat detection signal of the heartbeat detector. preferable. Preferably, the balloon control means operates in synchronization with a heartbeat detection signal of the heartbeat detector.

The blood assisted circulator of the present invention will be described in detail with reference to the embodiments shown in the drawings.

The blood assisting circulator 1 of the present invention includes a blood removal side blood tube 5, a blood supply side blood tube 6, and a blood removal side blood tube 5.
Attached to the blood assist circuit having the constant pressure pump 2 and the artificial lung 3 provided between the blood pump 6 and the blood supply side blood tube 6, the heartbeat detector 7, and the constant pressure pump 2 or a blood assist circuit located downstream thereof. And a blood flow control means 4 which operates in response to a heartbeat detection signal from the heartbeat detector 7.

For this reason, the blood assisting circulator 1 of the present invention can intermittently change the flow rate of the blood flow generated by driving the constant pressure pump 2 by using the flow rate control means 4, thereby pulsating the blood flow. Can be given. Further, since the flow control means 4 operates in response to the heartbeat detection signal of the heartbeat detector, it can apply a pulsation corresponding to the heartbeat detection signal to the blood flow. Thus, blood can be reliably sent to the coronary artery during operation of the assisting circulator, and the heart function of the patient can be efficiently assisted.

Therefore, the blood assisting circulator of the present invention will be described with reference to the embodiment shown in FIG.

The blood assisting circulating apparatus 1 of this embodiment includes a blood assisting circuit including a blood removal side blood tube 5, a blood sending side blood tube 6, a constant pressure pump 2, and an artificial lung 3, a heart rate detector 7, and a heart rate detector. And a blood flow control means 4 which operates in response to the heartbeat detection signal from the controller 7.

Constant pressure pump 2 used in blood assisted circulator 1 of the present invention
Is for sending a fluid at a constant pressure. As the constant pressure pump, a centrifugal pump, a turbine pump, a screw pump, or the like can be used.

The oxygenator 3 may be any type of oxygenator, preferably a model oxygenator, and particularly preferably a model oxygenator.
It is a hollow fiber model artificial lung.

As the hollow fiber model artificial lung, a housing, a gas exchange hollow fiber membrane which is a member for blood treatment inserted in the housing, and a partition wall for fixing both ends of the hollow fiber membrane bundle to both ends of the housing in a liquid-tight manner. And a gas, which is a blood processing fluid, which is provided near the both ends of the housing and communicates with a space (oxygen chamber) formed by the outer surface of the hollow fiber membrane that is the blood processing member, the inner surface of the housing, and the partition wall. A device having an inlet and a gas outlet, and a blood inlet port having a blood inlet and a blood outlet port having a blood outlet attached to both ends of the housing can be suitably used. As the hollow fiber bundle housed in the cylindrical housing, the gas exchange hollow fiber membrane is 10,000 to 60,000.
A bundle of about this number is used, and the hollow fiber membrane for gas exchange is a porous membrane and has a large number of micropores penetrating therethrough. As a hollow fiber membrane for gas exchange, an inner diameter of 100
~ 1000μm, preferably 100 ~ 300μm, wall thickness 5 ~ 80μ
m, preferably 10 to 60 μm, porosity of 20 to 80%, preferably 30 to 60%, and fine pores having a pore diameter of about 0.01 to 5 μm, preferably about 0.01 to 1 μm are suitably used. Further, it is not limited to the hollow fiber membrane, and may be a flat membrane. As the material of the gas exchange hollow fiber membrane, a polymer material such as polypropylene, polyethylene, polytetrafluoroethylene, polysulfone, polyacrylonitrile, and cellulose acetate can be used, preferably a hydrophobic polymer, and particularly preferably, It is a polyolefin-based resin, more preferably polypropylene, and preferably polypropylene having fine pores formed by a stretching method or a phase separation method.

The blood removal side blood tube 5 has a blood removal catheter 10 at the distal end side.
And the other end is connected to the constant pressure pump 2. Further, the distal end of the blood tube 6 on the blood sending side is connected to the oxygenator 3, and a blood sending catheter 11 is attached to the rear end.

For the blood removal side blood tube 5 and the blood supply side blood tube 6, for example, a tube made of a transparent synthetic resin having transparency such as vinyl chloride resin or silicone rubber can be suitably used.

Further, a flow meter may be attached to any of the blood tubes. When a constant pressure pump, particularly a centrifugal pump, is used, it is difficult to check the flow rate from the rotation speed of the pump, and it is preferable to provide the flow rate check. As the flow meter, one that can measure the flow rate of blood flowing inside the blood vessel without directly contacting the blood is preferable,
For example, an ultrasonic flowmeter is preferably used.

Then, in the blood assisting and circulating apparatus 1 of the present invention, the flow control timing by the flow control means 4 is configured to be performed in accordance with the heartbeat detection signal of the heartbeat detector 7,
In particular, it is preferable that the flow control means 4 operates in synchronization with the heartbeat detection signal of the heartbeat detector 7.

For this reason, the heartbeat detector 7 is, for example, shown in FIGS.
As shown in the figure, a heart rate detection unit 7a and a flow rate control unit control unit 7b that outputs an open signal and a close signal of the flow rate control unit 4 based on the heart rate detection signal detected by the heart rate detection unit 7a are provided. ing. Further, in this embodiment, the flow rate control means control section 7b includes a closing signal calculating section 7c that outputs a closing signal and an opening signal calculating section 7d that outputs an opening signal.

More specifically, a P wave, an R wave, and a T wave can be confirmed from an electrocardiogram waveform that is an electrical analysis of a heartbeat. However, it is the R wave having the highest electric output that can be easily extracted electrically, and the relationship between the movement of the heart and each of the above waves is that the aortic valve opens near the P wave and the T wave It is said that the aortic valve closes in the vicinity. That is, blood flow in the heart begins near the P-wave and T
Ending near the wave, blood does not flow from T wave to P wave. The R wave is generated later than the P wave. When performing simple blood assisted circulation, blood circulation may be performed independently of the movement of the heart, but in consideration of actively sending assisted blood to the coronary arteries, corresponding to the movement of the heart, It is preferred that the blood be sent near the aortic ostium of the heart.

That is, if blood can be sent to the vicinity of the aortic ostium of the heart while the aortic valve is closed, the sent blood does not flow to the heart side, so that the blood can be reliably sent to the coronary artery. Conversely, if the aortic valve is open, that is, if blood is being generated by the heart and blood is not sent by the assisting circulation, no burden is placed on the left ventricle. Therefore, the opening and closing of the blood tube 6 by the flow control means 4 is preferably closed near the P-wave where the aortic valve opens, and preferably opened near the T-wave where the aortic valve closes.

Therefore, the occlusion signal calculation unit 7c in the flow control unit control unit 7b in this embodiment outputs an occlusion signal to the flow control unit 4 substantially corresponding to the P wave of the heart, and the open signal calculation unit 7d
Is configured to output an opening signal to the flow control means 4 substantially corresponding to the T wave of the heart.

Then, the release signal calculation unit 7d uses the heartbeat detection unit 7a to
The wave may be detected and output, but as described above,
Since the detection by the heartbeat detecting unit 7a is most reliable in detecting the R wave, it is preferable to calculate a T wave (pseudo T wave) based on the R wave. Specifically, since the interval from the R wave to the T wave does not change much even when the heart rate fluctuates, R
By outputting a signal (pseudo T-wave signal) delayed by a predetermined time from the wave detection as an opening signal, the flow control means 4 can be opened almost in accordance with the aortic valve occlusion.

In addition, the occlusion signal calculation unit 7c may detect the P wave by the heartbeat detection unit 7a and output it, but as described above, the detection by the heartbeat detection unit 7a is the most reliable detection of the R wave. Therefore, it is preferable to calculate the P wave based on the R wave.
Specifically, the interval from the R wave to the P wave changes due to the fluctuation of the heart rate. Therefore, an average value is calculated from the generation times and intervals of a predetermined number (for example, the latest five times) of R waves, the generation period of the R waves is always calculated, and the calculated period and the pseudo T wave (open signal) are calculated. By calculating a pseudo P-wave that is appropriately delayed from the generation timing of the pseudo T-wave and outputting it as a closing signal, the flow control means 4 can be closed almost in accordance with the opening of the aortic valve.

The opening and closing of the flow control means 4 does not necessarily have to be the same as the heart rate, and may be opened once every heart rate, for example, once to eight times.

The flow control means 4 changes the flow rate in the blood circuit of the blood assisting circulator 1 to change the blood collection sent from the constant pressure pump 2 with time, thereby giving a pulsation to the blood flow. . The flow control means 4 intermittently changes the cross-sectional area of the blood tube 6 to which the flow control means is attached. Specifically, the blood tube 6 can be intermittently pressed from the outside, A clamp capable of closing the blood tube 6 is used. As the clamp, a rotary solenoid, a solenoid valve or the like is preferably used.

Further, the flow control means 4 may be provided downstream of the constant pressure pump 2 and may be attached to the blood tube 15 connecting the constant pressure pump 2 and the oxygenator 3 instead of the blood supply side blood tube 6. It may be directly attached to the constant pressure pump 2 or the artificial lung 3.

Furthermore, it is preferable that the blood assisted circulation device 1 of the present invention can perform blood circulation without using an anticoagulant. For this purpose, it is preferable to fix the antithrombotic material to the blood contact surface in the blood assist circuit, particularly to the blood contact surfaces of the artificial lung 3 and the blood tube 6. Examples of the antithrombotic material include heparin, polyalkylsulfone, ethylcellulose, acrylate-based polymer, methacrylate-based polymer (for example, poly-HEMA [polyhydroxyethyl methacrylate]), hydrophobic segment and hydrophilic segment. A block or graft copolymer having both (eg, HEMA-styrene-HEMA block copolymer, HEMA-M
Block copolymer of MA [methyl methacrylate], HE
MA-LMA [uralyl methacrylate] block copolymer, PVP [polyvinyl pyrrolidone] -MMA block copolymer, HEMA-MMA / AA [acrylic acid] block copolymer, and furthermore, this block copolymer Blend polymers in which a polymer having an amino group is mixed), and a fluorine-containing resin. Preferably, HEMA-styrene-
A block copolymer of HEMA, a block copolymer of HEMA-MMA [methyl methacrylate], a block copolymer of HEMA-MMA / AA [acrylic acid] and the like are preferable. Then, it is preferable that the blood contact surface is coated with a hydrophilic resin other than the above-mentioned heparin, and then heparin is further fixed thereon. In this case, in order to fix heparin on the surface of the hydrophilic resin, the hydrophilic resin includes a hydroxyl group, an amino group, a carboxyl group, an epoxy group, an isocyanate group, an epoxy group, a thiocyanate group, an acid chloride group, an aldehyde group and Having any of the carbon-carbon double bonds,
Alternatively, it is preferable to have a group that can be easily converted to these groups. Particularly preferably, a blend polymer obtained by mixing a polymer having an amino group with the hydrophilic resin is used. As the polymer having an amino group,
Polyamines, especially PEI [polyethynimine], are preferred.

Heparin fixation, after coating the hydrophilic resin on the blood contact surface of the blood assisted circulation circuit, after contacting the surface with an aqueous solution of heparin, glutaraldehyde, terephthalaldehyde, aldehydes such as formaldehyde,
By contacting with a fixing agent such as diphenylmethane diisocyanate, 2,4-tolylene diisocyanate, carbodiimide-modified diphenylmethane diisocyanate, epichlorohydrin, 1,4-butanediol diglycidyl ether, polyethylene glycol diglycidyl ether, the hydrophilic resin described above can be used. It can be fixed by covalent bonding.

Next, the blood assisting circulator of the embodiment shown in FIG. 2 will be described.

The blood assisting circulator 20 of this embodiment includes a blood removal side blood tube 5, a blood supply side blood tube 6, and a constant pressure pump 2 provided between the blood removal side blood tube 5 and the blood supply side blood tube 6. A blood-assisted circulatory circuit having an artificial lung 3, a heartbeat detector 7, a blood flow control means 4 attached to the blood-assisted circulatory circuit and operating in response to a heartbeat detection signal from the heartbeat detector 7, It has an intra-aortic balloon catheter 12 and balloon control means 13 for inflating and deflating a balloon 14 of the intra-aortic balloon catheter 12 in response to a heartbeat detection signal of the heartbeat detector 7.

Therefore, the blood assisted circulating apparatus 1 of the present invention can intermittently change the flow rate of the blood flow generated by driving the constant pressure pump 2 by using the flow control means 4 and the intra-aortic balloon catheter 12, It can pulsate the blood flow. Further, the flow control means 4
Since it operates in response to the heartbeat detection signal of the heartbeat detector, a pulse corresponding to the heartbeat detection signal can be given to the blood flow. Blood can be sent reliably,
Further, since the balloon of the intra-aortic balloon catheter can be inflated and deflated in response to the heartbeat detection signal, by selecting the timing of inflation and deflation, blood can be more reliably supplied to the coronary artery during operation of the assisting circulator. It can be sent to help the patient's heart function efficiently.

The difference between the blood-assisted circulator 20 of this embodiment and the blood-assisted circulator 1 of the embodiment shown in FIG. 1 is that the device 20 of this embodiment has the heartbeat of the intra-aortic balloon catheter 12 and the heartbeat detector 7. Balloon control means for inflating and deflating the balloon 14 of the intra-aortic balloon catheter 12 in response to the detection signal
13 and the other configuration is the same as that of the blood assisting circulator 1 of the embodiment shown in FIG.

The intra-aortic balloon catheter 12 is formed so as to be indwellable in the aorta, and has a pumping balloon 14
have. As the intra-aortic balloon catheter 12, a known catheter can be used.

Balloon control means 13 for inflating and deflating balloon 14
Is connected to a connector provided at the proximal end of the intra-aortic balloon catheter 12, so that fluid (eg, gas) can be injected and inhaled into the balloon 14 from the proximal end of the balloon catheter 12. Is composed of
The injection and inhalation of this fluid causes the balloon 14 to inflate and
The contraction is performed.

The inflation / deflation timing of the balloon 14 by the balloon control means 13 corresponds to the heartbeat detection signal of the heartbeat detector 7. Specifically, the inflation / deflation timing of the balloon 14 by the balloon control means 13 preferably operates in synchronization with the heartbeat detection signal of the heartbeat detector 7.

As described above, in the embodiment shown in FIG. 3, the heartbeat detector 7 outputs the release signal of the flow control means 4 based on the heartbeat detection unit 7a and the heartbeat detection signal detected by the heartbeat detection unit 7a. And a flow control means control section 7b for outputting a blockage signal. Further, the flow rate control means control section 7b includes a closing signal calculating section 7c that outputs a closing signal and an opening signal calculating section 7d that outputs an opening signal.

The open signal calculation unit 7d is configured to output a signal (pseudo T wave signal) delayed by a predetermined time from the detection of the R wave as an open signal. That is, the occlusion signal is output substantially in accordance with the occlusion of the aortic valve.

Further, the blockage signal calculation unit 7c calculates the average value from the generation times and intervals of a predetermined number (for example, the latest five times) of the R waves, constantly calculates the generation period of the R waves, and calculates the calculated period and the pseudo period. It is configured to calculate a pseudo P-wave that is appropriately delayed from the pseudo T-wave based on the generation timing of the T-wave (open signal) and output a blockage signal. That is, the occlusion signal is output substantially in accordance with the opening of the aortic valve.

If the blood in the auxiliary circulation can be sent to the vicinity of the aortic ostium of the heart while the aortic valve is closed, the sent blood does not flow to the heart side, so the blood can be reliably sent to the coronary artery. Further, if the balloon of the intra-aortic balloon catheter 12 is further inflated on the downstream side during this time, blood in the auxiliary circulation can be more reliably sent to the coronary artery without particularly burdening the degraded left ventricle. Can be. Conversely, if the balloon is deflated when the aortic valve is open, that is, when the blood flow is generated by the heart, the flow of blood by the heart is not obstructed.

Then, the balloon control means 13 injects gas into the balloon catheter 12 with the release signal (pseudo T-wave signal) output from the release signal calculation unit 7d of the heartbeat detector 7 to inflate the balloon 14 and inflate the balloon 14. It is preferable that the balloon 14 be deflated by an occlusion signal (pseudo P-wave signal) from the occlusion signal calculator 7c. The balloon 14 does not need to be inflated the same number as the heart rate. For example, the open signal (pseudo T-wave signal) output from the open signal calculation unit 7d is input several times, for example, 1 to 8 times. You may make it expand once each time it is done.

Further, as in the embodiment shown in FIGS. 4 and 5, the heartbeat detector 7 and the balloon control means 13 may be integrally provided.

[Operation] The operation of the blood assisted circulator of the present invention will be described with reference to FIGS. 4 and 5.

First, as shown in FIG. 4, the blood removal catheter 10 of the blood assist circuit is inserted from the femoral vein, placed in the vicinity of the right atrium, and the blood feeding catheter 11 is placed in the vicinity of the aortic ostium of the heart.
The constant pressure pump 2 is operated to perform blood assisted circulation. The blood removed from the blood removal catheter 10 passes through the blood removal side tube 5 and is sent to the oxygenator 3 by the constant-pressure pump 2, where oxygenation of the blood and removal of carbon dioxide are performed. Thereafter, the blood passes through the blood feeding tube 6 and the blood feeding catheter 11 and flows into the aortic ostium. In the auxiliary circulation device 20, a flow control means 4 is attached to the blood feeding tube 6, and the flow control means 4 has a heartbeat detection function,
It is electrically connected to a control device 22 having an open / close signal output function of the flow control means and a balloon control function of the intra-aortic balloon catheter.

Then, the flow control means 4 performed by the control device 22
Is closed near the P-wave where the aortic valve opens and is opened near the T-wave where the aortic valve opens, as in the embodiment shown in FIG. 3 and described above.
That is, in the state where the aortic valve 28 is on the right side of the wall as shown in FIG. 4, the flow control means 4 is opened, and blood by the auxiliary circulation is sent to the vicinity of the aortic ostium, and as shown in FIG. When the valve 28 is open, the flow control means 4 is closed. Therefore, while the aortic valve 28 is closed, blood can be sent to the vicinity of the aortic ostium of the heart, and the sent blood does not flow to the heart side, so that the blood can be reliably sent to the coronary artery. Also, conversely, when the aorta is open, that is, when blood flow is generated by the heart, blood is not sent by the auxiliary circulation,
Does not impede blood flow through the heart and does not strain the left ventricle.

If the opening and closing operation of the flow control means 4 alone is not sufficient, the intra-aortic balloon catheter is inserted into the aorta.
12 is inserted, and the balloon 14 is inflated and deflated. And
The inflation and deflation of the balloon 14 controlled by the control device 22 are as follows:
As in the above-described embodiment, the aortic valve contracts near the P-wave that opens, and is configured to expand near the T-wave where the aortic valve closes. That is, as shown in FIG. 4, when the aortic valve 28 is closed, the flow control means 4 is opened, blood is sent by the auxiliary circulation to the vicinity of the aortic ostium, and the balloon 14 is further inflated. Since the blood sent to the vicinity of the mouth does not flow to the heart side and further to the downstream side, the blood can be reliably sent to the coronary artery. Further, as shown in FIG. 5, when the aortic valve 28 is open, the flow control means 4 is closed and the balloon 14 is also deflated, so that the flow of blood by the heart is not obstructed. .

[Effect of the Invention] The blood assisting circulator of the present invention includes a blood removal side blood tube, a blood supply side blood tube, and a constant pressure pump provided between the blood removal side blood tube and the blood supply side blood tube. Since it has a blood assisted circulation circuit having an artificial lung, a heartbeat detector, and a blood flow control means attached to the blood assisted circulation circuit and operated in response to a heartbeat detection signal of the heartbeat detector, By using the flow control means,
The flow rate of the blood flow generated by driving the constant pressure pump can be intermittently changed, and pulsation can be given to the blood flow. Further, since the flow control means operates in response to the heartbeat detection signal of the heartbeat detector, it can apply a pulsation corresponding to the heartbeat detection signal to the blood flow. In addition, blood can be reliably sent to the coronary artery during operation of the assisting circulator, and the heart function of the patient can be efficiently assisted.

[Brief description of the drawings]

FIG. 1 is a schematic view of an embodiment of the blood assisted circulator of the present invention, FIG. 2 is a schematic view of another embodiment of the blood assisted circulator of the present invention, and FIG. FIGS. 4 and 5 are views showing an example of a heartbeat detector used in the assisting circulator, and are explanatory diagrams for explaining the operation of the blood assisting circulator of the present invention. 1,20 ... blood assisted circulation device, 2 ... constant pressure pump, 3 ...
Artificial lung, 4 ... Flow control means, 5 ... Blood side blood tube, 6 ... Blood side blood tube, 7 ... Heart rate detector, 7a
... Heart rate detection unit, 7b Flow rate control unit control unit, 7c Blockage signal calculation unit, 7d Open signal calculation unit, 10 Blood removal catheter, 11 Blood feeding catheter, 12 Aorta Balloon catheter,

Claims (6)

(57) [Claims] 1. A blood-assisted circulation circuit comprising a blood removal side blood tube, a blood supply side blood tube, a constant pressure pump provided between the blood removal side blood tube and the blood supply side blood tube, and an artificial lung. And a heart rate detector, and a blood flow control means attached to the blood assist circuit and operated in response to a heartbeat detection signal of the heart rate detector. 2. The blood assisting and circulating apparatus according to claim 1, wherein the flow control means is attached to the blood tube on the blood sending side. 3. The blood assisted circulator according to claim 1, wherein the flow control means opens and closes the blood assisted circulatory circuit in response to a heartbeat detection signal of the heartbeat detector. 4. The blood assisting and circulating apparatus according to claim 1, wherein said flow control means operates in synchronization with a heartbeat detection signal of said heartbeat detector. 5. The blood-assisted circulatory device according to claim 1, further comprising an intra-aortic balloon catheter, and an inflation / inflation of the balloon of the intra-aortic balloon catheter in response to a heartbeat detection signal of the heartbeat detector.
The blood assisted circulator according to any one of claims 1 to 4, further comprising a balloon control means for performing deflation. 6. The balloon control means operates in synchronization with a heartbeat detection signal of the heartbeat detector.
The blood assisted circulator according to claim 1.