JPH119685A - Blood purifying device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To prevent protein etc. from being adhered to a hollow thread film and to improve dialization filtering efficiency by permitting a dializing liquid pulsating current to flow in the dializing liquid flow path of a hollow thread film-type dializer. SOLUTION: A dializing liquid flow control means 17 is connected to the hollow thread film dializer 1 by tubes 18 and 19 and a dializing liquid supplying means 20 is arranged in the midst of the tubes 18 and 19. The dializing liquid supply means 20 is formed by double-type pumps, a cycle in a dializing liquid flow entrance 36 generates the dializing liquid pulsating current of 0.05-120 sec. and the liquid is supplied in opposite directions by a same flowrate to the tubes 18 and 19. When the cycle is equal to below 0.05 sec., dialization filtering efficiency is reduced. At the time of being more thanl 120 sec., the adhesion preventing effect of protein, etc., is not safficiently obtained. Thus, the pulsating current is made to flow so that the adhesion of protein, etc., is effectively prevented.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

[0001] The present invention relates to a blood purification apparatus used in blood purification therapy. More specifically, the present invention relates to a hollow fiber membrane-type blood purification device that can effectively prevent a decrease in filtration efficiency due to attachment of proteins and platelets.

[0002]

2. Description of the Related Art In the development of artificial organs, the problems of antithrombotic properties and biocompatibility have been addressed as the most important issues. Blood purification devices used for blood purification therapy also suffer from reduced performance due to blood components adhering to the member surface, especially diafiltration ability due to the adhesion of red blood cells, white blood cells, platelets and proteins among blood components to dialysis membranes, etc. Is still a major challenge.

Conventionally, in order to prevent platelets and proteins from adhering to a dialysis membrane in a blood purification apparatus, development of a synthetic polymer membrane having high antithrombotic properties, surface modification of the membrane, and the like have been performed. There are drawbacks such as clogging of the pores of the membrane caused by water removal filtration cannot be prevented, and the production cost is high. Therefore, there is a limit in such a material approach.

[0004]

SUMMARY OF THE INVENTION The present invention has been made in view of the above-mentioned problems of the prior art, and has as its object to prevent adhesion of proteins and platelets to the hollow fiber membrane and to prevent the hollow fiber membrane from adhering. It is an object of the present invention to provide a blood purification apparatus capable of preventing a decrease in diafiltration efficiency.

Another object of the present invention is to provide a blood purification apparatus capable of preventing a reduction in diafiltration efficiency over a long period of time.

It is still another object of the present invention to provide a blood purification apparatus which can use an existing hollow fiber membrane type dialyzer as it is and can prevent a decrease in diafiltration efficiency at low cost.

[0007]

Means for Solving the Problems As a result of intensive studies on a blood purification apparatus, the present inventors have found that a pulsating dialysate is allowed to flow through a hollow fiber membrane type dialyzer to thereby remove protein from the hollow fiber membrane. The present inventors have found that the adhesion of the like is effectively prevented and completed the present invention.

[0008] That is, the present invention provides a hollow fiber membrane type dialyzer in which a blood flow path and a dialysate flow path are formed with a hollow fiber membrane interposed therebetween so that the dialysate flow is passed through the dialysate flow path. A blood purification apparatus characterized by the following.

The present invention also provides a hollow fiber membrane type dialyzer having a blood flow path and a dialysate flow path formed with a hollow fiber membrane therebetween, and a dialysate flow control means connected to the dialysate flow path. The dialysate flow control means is the blood purification device, wherein the dialysate flow is passed through the dialysate flow path.

The present invention is also the blood purification apparatus, wherein the dialysate flow control means has a dialysate liquid sending means for generating a pulsating flow.

The present invention is also the above blood purification apparatus, wherein the dialysate flow control means has a dialysate liquid sending means and a pulsating flow generating means.

The present invention is also the blood purification apparatus, wherein the dialysate pulsating flow has a cycle at the inlet of the dialysate flow path of 0.05 to 120 seconds.

The present invention is also the blood purifying apparatus, wherein the dialysate pulsating flow has a pressure fluctuation range of 30 to 500 mmHg at a flow rate of 500 ml / min at the dialysate flow channel inlet.

[0014]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described below in detail with reference to the drawings.

FIG. 1 is a circuit diagram schematically showing one embodiment of the blood purification apparatus of the present invention. As shown in FIG. 1, the blood purification apparatus 10 includes a blood removal line 11A, a hollow fiber membrane dialyzer 1, a blood return line 11B, and dialysate flow control means 17.

The blood removal line 11A comprises a tube 12, a blood supply pump 13 and a defoaming chamber 14 installed in the middle of the tube 12, and one end of the blood removal line 11A is connected to a needle tube. And the other end is connected to the blood flow path inlet 34 of the hollow fiber membrane type dialyzer 1. As the pump 13, a roller pump is preferably used.

The blood return line 11B is connected to a tube 15
And one end of a blood return line 11B is connected to a blood flow path outlet 35 of the hollow fiber membrane type dialyzer 1; The end is connected to the patient's vein via a needle tube.

As shown in FIG. 2, a hollow fiber membrane type dialyzer 1 has a cylindrical main body 31 and headers 32 connected and fixed to both ends thereof in a liquid-tight manner by covers 38 and 39, respectively. And a housing 3 made of various hard resins composed of At the top of the header 32, a blood flow path inlet 34 is formed to protrude, and at the top of the header 33, a blood flow path outlet 35 is formed to protrude. A dialysate flow path inlet 36 is formed on the side of the cylindrical body 31 on the header 33 side, and a dialysate flow path outlet 37 is formed on the side of the cylindrical body 31 on the header 32 side. Have been.

A bundle 4 of hollow fiber membranes 41 made of polysulfone or the like is accommodated in the housing 3 over substantially the entire length thereof. The number of hollow fiber membranes 41 constituting the bundle 4 is 100 to
About 70000 pieces, effective film area is 100 cm ^{2 to} 6.0
m ² , and both ends of each hollow fiber membrane 41 are made of a potting material such as polyurethane at the end of the tubular main body 31 in a state where the end opening of the hollow fiber membrane 41 is not closed. It is liquid-tightly supported and fixed by the partition walls 51 and 52.

A blood inflow chamber 61 is formed in a space surrounded by the header 32 and the partition wall 51, and a blood outflow chamber 62 is formed in a space surrounded by the header 33 and the partition wall 52. A blood flow path 6 is formed in the inner cavity of each hollow fiber membrane 41 and communicates with the blood inflow chamber 61 and the blood outflow chamber 62, respectively. In a space surrounded by the cylindrical main body 31 of the housing 3 and the partition walls 51 and 52, the gap between the bundle 4 of the hollow fiber membranes 41 and the inner peripheral surface of the cylindrical main body 31 and the adjacent hollow fiber membranes 41 A dialysate flow path 7 is formed in the gap. The upstream side of the dialysate flow path 7 communicates with the dialysate flow path inlet 36, and the downstream side communicates with the dialysate flow path outlet 37.

In the middle of the dialysate flow path 7, a constriction 71 made of a dialysate swellable material is provided to reduce the cross-sectional area of the flow path, and the pressure of the dialysate flowing through the dialysate flow path 7 is reduced. Part 7
On the upstream side 72 of the dialysate, the pressure is higher than the blood pressure at the corresponding portion of the blood flow channel 6, and on the downstream side 73 of the dialysate from the constriction 71, the pressure is lower than the blood pressure at the corresponding portion of the blood flow channel 6. You may comprise. in this case,
The blood flowing through the blood flow channel 6 is first subjected to dialysis (diffusion of solute) and ultrafiltration (dewatering) through each hollow fiber membrane 41 on the downstream side 73 of the dialysate, and then to the upstream side 72 of the dialysate.
In the above, ultrafiltration (replacement fluid) in the reverse direction from the dialysate side to the blood side is performed through each hollow fiber membrane 41, and a large amount of blood and dialysate can be replaced.

In FIG. 1, one end of a dialysate flow control means 17 is provided at one end of the dialysate flow channel inlet 3 of the hollow fiber membrane type dialyzer 1.
6 and a tube 19 having one end connected to the dialysate flow path outlet 37 of the hollow fiber membrane dialyzer 1.
And dialysate feeding means 20 installed in the middle of the tube 18 and the tube 19.

The dialysate feeding means 20 is a dual pump for feeding a dialysate pulsating flow into the tubes 18 and 19 at the same flow rate and in opposite directions, respectively, and converts the rotational motion of the motor into the reciprocating motion of the plunger. The check valve mechanism alternately receives and discharges dialysate and dialysate drainage. The configuration of the dialysate liquid supply means 20 is not particularly limited as long as it is a liquid supply means that generates a pulsating flow. In addition to the above-described structure, the liquid supply means by a pump tube such as a roller pump, and the liquid supply means by reciprocation of a cylinder And a means for feeding a liquid by crushing or expanding a soft container at a constant cycle, such as an accumulator.

FIG. 3 is a circuit diagram schematically showing another embodiment of the dialysate flow control means in the blood purification apparatus of the present invention. As shown in the figure, the dialysate flow control means 81 has a dialysate liquid sending means 82 and a pulsating flow generating means 83 separately. The pulsating flow generating means 83 is connected to the tube 1 between the dialysate feeding means 82 and the dialysate channel inlet 36.
A tube 84 is branched from a part of the tube 8, and a soft container 85 is provided at an end of the tube 84.
6 by alternately opening and closing valves 89A and 89B communicating with the high-pressure chamber 87 and the low-pressure chamber 88, etc., so that the soft container 85 is crushed or swelled at a predetermined cycle, thereby sucking and discharging the dialysate and discharging the pulse. It generates a flow.

FIG. 4 schematically shows another configuration of the pulsating flow generating means in FIG. The pulsating flow generating means 91 includes a cylinder 92 and a piston 93 connected to an end of the tube 84. That is, the pulsating flow generating means 91 causes the piston 93 to reciprocate inside the cylinder 92 via the piston rod 94 eccentrically and rotatably locked to the rotating plate 95 by rotation of a motor (not shown). This causes the dialysate to be sucked and discharged to generate a pulsating flow.

As described above, the pulsating flow generating means in the present invention is not particularly limited as long as a pulsating flow is generated. A branch circuit is provided in the section, and a pulsating flow is generated by forward and reverse rotations of a pump connected to the end of the branch circuit. A container that generates a pulsating flow by crushing or inflating a container at a constant cycle is exemplified.

In the present invention, the period of the dialysate pulsating flow at the dialysate channel inlet 36 is preferably 0.05 to 120 seconds, and more preferably 0.5 to 10 seconds. If the period of the dialysate pulsating flow is less than 0.05 seconds, the filtrate filtered from the blood returns to the blood side by back filtration, and the same solution is again filtered, so that the diafiltration efficiency is reduced. It is not preferable because the back-filtration is not sufficiently repeated and the effect of preventing platelets and proteins from adhering cannot be sufficiently obtained.

The pressure fluctuation width of the dialysate pulsating flow at the dialysate flow path inlet 36 at a flow rate of 500 ml / min is 30.
It is desirably from mmHg to 500 mmHg, and preferably from 40 to 300 mmHg. When the pressure fluctuation width of the dialysate pulsatile flow is less than 30 mmHg, the normal filtration and the reverse filtration are not sufficiently repeated, and the effect of preventing platelet and protein adhesion is not sufficiently obtained. When the pressure fluctuation width exceeds 500 mmHg, the pressure resistance of the dialysis membrane is exceeded. It is not preferable because a leak occurs.

The dialysate flow control means 17 includes a bypass tube 21 having both ends connected to a tube 19 so as to bypass the double pump 20, and a water removal pump 22 provided in the middle of the bypass tube 21. May be provided. In this case, the water removal pump 22 preferably has a configuration in which the rotational movement of the motor is converted into the reciprocating movement of the plunger, and the dialysate in the cylinder is sent in a certain direction.

Next, the operation of the blood purification apparatus 10 according to the present invention will be described with reference to FIGS. 1 and 2.
After flowing through the chamber 1A and once stored in the chamber 14 and defoamed, it flows into the hollow fiber membrane dialyzer 1 from the blood channel inlet 34. The blood flowing out from the blood flow path outlet 35 flows through the blood return line 11B, is temporarily stored in the chamber 16, is defoamed, and is returned to the patient.

The dialysate supplied from a dialysate reservoir (not shown) by the operation of the dual pump 20 flows in a pulsating flow in the tube 18, and flows through the dialysate channel inlet 36 through a hollow fiber membrane dialyzer. 1 is introduced into the housing 3. With the introduction of the dialysate pulsating flow, normal filtration and reverse filtration are repeated with the blood via each hollow fiber membrane 41 as described later, and thereafter, the dialysate is discharged from the dialysate channel outlet 37. The discharged dialysate is transferred via the tube 19 and collected. At this time, when the water removing bomb 22 is operated at a predetermined rotation speed, the amount of the dialysate supplied to the hollow fiber membrane dialyzer 1 and the amount of the dialysate recovered from the hollow fiber membrane dialyzer 1 are reduced. There is a difference corresponding to 22 discharge amounts,
This amount is the amount of water removed from the blood passing through the hollow fiber membrane type dialyzer 1. Therefore, the rotation speed (discharge amount) of the water removal pump 22
By adjusting the amount of water, the amount of water removal can be adjusted.

On the other hand, inside the housing 3, blood flowing into the blood inflow chamber 61 from the blood flow path inlet 34 is
After flowing through the blood flow path 6, it is collected in the blood outflow chamber 62 and flows out from the blood flow path outlet 35, while the dialysate flow path inlet 36
The pulsating flow of dialysate flowing from the dialysis fluid flows in the dialysate flow path 7 in a direction opposite to the blood flow (counter flow), and flows out of the dialysate flow path outlet 37. At this time, since the dialysate flowing through the dialysate flow path 7 forms a pulsating flow, the hollow fiber membrane 41 is subjected to normal filtration, that is, filtration from the blood side to the dialysate side, and reverse filtration (reverse rinsing). That is, by repeating the filtration from the dialysate side to the blood side, it is possible to prevent platelets and proteins from adhering to the hollow fiber membrane 41.

[0033]

The present invention will be described in more detail with reference to the following examples.

Example 1 A dialyser comprising a polysulfone hollow fiber membrane having an inner diameter of 200 μm (effective membrane area: 0.6 m ² ,
A blood purification apparatus similar to that of FIG. 3 having the pulsating flow generating means shown in FIG. The cycle of the dialysate pulsating flow in the blood purification apparatus is 2 s, and the dialysate flow path inlet pressure of the dialyzer at the time of 500 ml / min dialysate feeding is 30 mmHg to 7 mm.
0 mmHg, and the pressure fluctuation width was 40 mmHg.

[Comparative Example 1] A blood purification apparatus was manufactured in the same manner as in Example 1, except that a device for generating a pulsating flow by reciprocating motion of the cylinder was not installed.

[Test Example 1] Dog extracorporeal circulation experiment A mongrel dog (weight: 31.8 ± 3.7 kg (n = 6)) was
Seractal 1mg / kg, Atropine sulfate 0.05m
g / kg was injected intramuscularly. Anesthesia: ketamine 40mg / kg /
The administration was maintained intravenously at hr. To make the difference in residual blood clearer, the amount of heparin was set to 150 U / min 10 minutes before the start of circulation.
kg, 50 U / kg after 30 minutes, 50 U / kg after 2 hours and a half
kg was administered intravenously. For extracorporeal circulation, blood was returned by inserting a cannula from the carotid artery (or femoral artery), leading it through a blood circuit to a dialyzer, and inserting a cannula into the jugular vein (or femoral vein). The cannula was filled with 1 U / ml of heparinized saline and the priming volume was reduced to about 60 by eliminating the chamber to reduce the filling volume of the blood circuit.
ml. After priming and washing of the blood circuit and the dialyzer with physiological saline, the flow rate on the blood side was set to 100 ml / min. The dialysate used was Kinderly No. 2 (Fuso Pharmaceutical Co., Ltd.) according to a conventional method. 500m flow rate into dialyzer
The dialysate was fed at 1 / min, and the filtration flow rate was set so that the amount of infusion was removed (5-7 ml / min) in order to keep the hematocrit constant, and circulation was performed for 4 hours. During the circulation, the pressure at the inlet and outlet of the blood channel of the dialyzer was measured. To measure the pressure, use a pressure gauge (PG-200
-102GH-3P, manufactured by Copal Electronics Co., Ltd.). After circulating for 4 hours, the number of residual blood when rinsed with physiological saline for 5 minutes was evaluated. The results are shown in FIG.

[0037]

[Table 1]

As shown in FIG. 5, the change over time of the pressure loss in the blood flow path of the dialyzer was lower in Example 1 than in Comparative Example 1. This is because the back-filtration due to the pulsating flow occurred.
It is presumed that platelets and proteins hardly adhered to the membrane, making it difficult for thrombus to form. Table 1 also shows that Example 1 had a lower residual blood count than Comparative Example 1, and prevented the platelets and proteins from adhering to the dialysis membrane due to the pulsating flow, making it difficult for blood to coagulate in the hollow fiber. Was.

Example 2 A blood purification apparatus was prepared in the same manner as in Example 1 except that a polysulfone hollow fiber membrane having an effective membrane area of 1.5 m ² was used. The period of the dialysate pulsating flow in the blood purification device is 2 s,
The dialysate flow channel inlet pressure of the dialyzer at the time of 0 ml / min dialysate feed was 50 mmHg to 90 mmHg, and the pressure fluctuation range was 40 mmHg. FIG. 6 shows a dialysis fluid pressure fluctuation diagram of the blood purification apparatus.

Example 3 Using a polysulfone hollow fiber membrane having an inner diameter of 200 μm (effective membrane area 1.5 m ² , confirmed that no clogging of the membrane occurs during production), an acrylonitrile fiber inner layer was used as a stenosis forming material. Dialysis fluid fiber (LANSEAL F, manufactured by Toyobo Co., Ltd.) composed of a composite fiber of styrene and an acrylate copolymer outer layer, 5 g, width 0.04
A dialyzer was prepared in which the knitted fabric of m was attached to the center of the bundle of hollow fiber membranes, and a dialysate feed pump that generates a pulsating flow was attached to the dialysate flow path inlet of the dialyzer to obtain a blood purification device. The period of the dialysate pulsating flow in the blood purification device is 2 s,
The dialysate flow channel inlet pressure of the dialyzer when the dialysate was fed at 0 ml / min was 50 mmHg to 120 mmHg, and the pressure fluctuation width was 70 mmHg. FIG. 7 shows a dialysate pressure fluctuation diagram of the blood purification apparatus. In addition, the period of the dialysate pulsating flow of only the dialysate sending pump that generates a pulsating flow is 2 s, and is 500 ml.
/ Min dialysate flow inlet pressure of the dialyzer during dialysate delivery is 2
8 mmHg to 38 mmHg, pressure fluctuation width is 10 m
mHg. The dialysate pressure fluctuation diagram in this case is shown in FIG. The pulsation cycle when a dialyser having no constriction and a dialysate pump for generating pulsation were connected to the dialysate flow path used in Example 2 was 2 s, and 500 ml / min.
The dialysate inlet pressure of the dialyzer at the time of dialysate feeding is 27 mmHg ~
The pressure was 50 mmHg, and the pressure fluctuation width was 23 mmHg. FIG. 9 shows a dialysate pressure fluctuation diagram in this case.

[Comparative Example 2] A blood purification apparatus was manufactured in the same manner as in Example 1 except that an apparatus for generating a pulsating flow by reciprocating cylinders was not used.

[Comparative Example 3]
Using the same blood purification device as in
s The dialysate flow path inlet pressure of the dialyzer was adjusted to -17 mmHg to -49 mmHg and the pressure fluctuation width was adjusted to 32 mmHg when the dialysate was fed at 500 ml / min. The dialysate pressure fluctuation diagram is shown in FIG.

[Test Example 2] 4 hour circulating dialysis experiment on bovine blood system Using the blood purification apparatus of Examples 2 and 3 and Comparative Examples 2 and 3, a blood-side flow rate of 200 ml / min and a dialysate feed flow rate of 5
A circulation dialysis experiment was performed at 00 ml / min and a filtration flow rate of 15 ml / min for 4 hours. The blood side test solution was prepared bovine blood (Ht: 30 ± 3%, TP: 6.5 ± 0.5 g /
dl) A dialysis experiment was performed by circulating a 5 L pool. Bovine blood was supplemented with HF effluent concentrate before circulation. Since the concentration of the indicator substance decreased during the dialysis experiment and the measurement of the indicator substance became difficult, an HF drainage concentrate was further added 20 minutes before the clearance measurement. The regular wait for clearance measurement is 10
Minutes. The anticoagulant was continuously injected into the bovine blood circulation, and the bovine blood was replenished at the same flow rate as the dewatering flow rate so that the hematocrit was constant. Sampling was performed at the blood side and dialysate side inlet and outlet of the dialyzer. β2-
MG was measured by latex agglutination immunoassay. The clearance was calculated by the following equation.

CL = (Q _pi × C _pi −Q _po × C _po ) / C _pi (where C is the β2-MG concentration [mg / l], CL
Is clearance [ml / min], Q is [ml / mi]
n] represents the flow rate, with the subscripts p for plasma side, i for inlet side, o
Table 2 shows the results of β2-MG clearance (n = 3).

[0045]

[Table 2]

In Examples 2 and 3, the data are higher than those in Comparative Example 1, and it can be seen that there is no deterioration in performance over time, and that platelets and proteins are prevented from adhering to the dialysis membrane. In Comparative Example 3, the dialysate-side inlet pressure was set to 10
When the pressure was not more than mmHg, the performance was reduced, the number of remaining blood increased, and no effect was observed.

[0047]

As described above, the blood purification apparatus of the present invention provides a dialysate in a hollow fiber membrane type dialyzer in which a blood flow path and a dialysate flow path are formed with a hollow fiber membrane interposed therebetween. By allowing the pulsating flow to flow, normal filtration and reverse filtration are repeated, preventing protein and platelets from adhering to the hollow fiber membrane, preventing a decrease in the diafiltration efficiency of the hollow fiber membrane, and having a long-term effect. Is maintained over time. Further, according to the blood purification apparatus of the present invention, since the existing hollow fiber membrane type dialyzer can be used as it is, reduction in diafiltration efficiency can be prevented at low cost without depending on the material improvement or the like.

[Brief description of the drawings]

FIG. 1 is a circuit diagram schematically showing one embodiment of the blood purification apparatus of the present invention.

FIG. 2 is a longitudinal sectional view showing an example of a hollow fiber membrane type dialyzer used in the present invention.

FIG. 3 is a circuit diagram schematically showing another embodiment of the dialysate flow control means in the blood digestion apparatus of the present invention.

FIG. 4 is a diagram schematically showing another configuration example of the pulsating flow generating means in FIG.

FIG. 5 is a graph showing the change over time in the pressure loss of the blood flow path of the dialyzer in the extracorporeal circulation experiment.

FIG. 6 is a graph showing a change in dialysate pressure of the blood purification apparatus according to the second embodiment.

FIG. 7 is a graph showing a change in dialysate pressure of the blood purification apparatus according to the third embodiment.

FIG. 8 is a graph showing dialysate pressure fluctuations caused only by a dialysate feed pump that generates a pulsating flow in Example 3.

FIG. 9 is a graph showing a dialysate pressure fluctuation of a blood purification apparatus in which a dialyser having no stenosis in a dialysate flow path and a dialysate pump for generating pulsation are connected in Example 3.

FIG. 10 is a graph showing dialysate pressure fluctuation of the blood purification device in Comparative Example 3.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Hollow fiber membrane dialyzer 10 ... Blood purification apparatus 11A ... Blood removal line 11B ... Blood return line 12 ... Tube 13 ... Pump 14 ... Chamber 15 ... Tube 16 ... Chamber 17 ... Dialysate flow control means 18, 19 ... Tube DESCRIPTION OF SYMBOLS 20 ... Double pump 21 ... Bypass tube 22 ... Water removal pump 3 ... Housing 31 ... Cylindrical main body 32, 33 ... Header 34 ... Blood channel inlet 35 ... Blood channel outlet 36 ... Dialysate channel inlet 37 ... Dialysate flow Road outlets 38, 39 Cover 4 Hollow fiber membrane bundle 41 Hollow fiber membranes 51, 52 Partition wall 6 Blood flow channel 61 Blood inflow chamber 62 Blood outflow chamber 7 Dialysate flow path 71 Stenosis 72 Dialysate upstream side 73 ... Dialysate downstream side 81 ... Dialysate flow control means 82 ... Dialysate liquid sending means 83 ... Pulse flow generating means 84 ... Tube 85 ... Soft volume 86 ... pressure vessel 87 ... high-pressure chamber 88 ... low-pressure chamber 89A, 89B ... valve 91 ... pulsating flow generation section 92 ... cylinder 93 ... piston 94 ... piston rod 95 ... rotating plate

Claims (6)

[Claims] 1. A hollow fiber membrane dialyzer in which a blood flow path and a dialysate flow path are formed with a hollow fiber membrane interposed therebetween, wherein the dialysate flow is passed through the dialysate flow path. Blood purification device. 2. A dialyzer comprising a hollow fiber membrane dialyzer having a blood flow path and a dialysate flow path formed with a hollow fiber membrane therebetween, and dialysate flow control means connected to the dialysate flow path. 2. The blood purifying apparatus according to claim 1, wherein the dialysate flow control means circulates a dialysate pulse flow through the dialysate flow path. 3. The blood purification apparatus according to claim 2, wherein said dialysate flow control means includes dialysate liquid sending means for generating a pulsating flow. 4. The blood purification apparatus according to claim 2, wherein said dialysate flow control means includes a dialysate liquid sending means and a pulsating flow generating means. 5. The blood purification apparatus according to claim 1, wherein the dialysate pulsating flow has a cycle at the dialysate channel inlet of 0.05 to 120 seconds. 6. The pulsating flow of the dialysate has a pressure fluctuation width of 30 at a flow rate of 500 ml / min at the inlet of the dialysate flow path.
The blood purification device according to any one of claims 1 to 5, wherein the pressure is from 500 to 500 mmHg.