WO1981002835A1

WO1981002835A1 - Hollow fiber-type body-fluid treating device

Info

Publication number: WO1981002835A1
Application number: PCT/JP1980/000069
Authority: WO
Inventors: Y Toyota; Y Sakai; T Nakagawa
Original assignee: Toray Industries; Y Toyota; Y Sakai; T Nakagawa
Priority date: 1980-04-10
Filing date: 1980-04-10
Publication date: 1981-10-15

Abstract

A hollow fiber-type device for treating body fluids such as blood or abdominal fluid, which contains flow paths of semipermeable hollow fibers interrupted by a fluid-collecting compartment in which the fluid is mixed to once remove a concentration polarization layer formed within said hollow fibers, thereby improving filtration performance. The filtration performance can be further improved by changing the cross-sectional area of flow paths across the fluid-collecting compartment.

Description

Details

Title of invention

Hollow iron type body fluid treatment equipment

Technical field

The present invention relates to a device for treating body fluids such as blood, plasma or ascites.

In particular, the present invention is directed to flowing a bodily fluid through a hollow portion of a hollow iron stitch made of a semi-permeable membrane, passing the bodily fluid through the semi-permeable membrane, or simultaneously performing filtration and dialysis. Also, the present invention relates to an improved hollow fiber type body fluid treatment apparatus for performing separation, purification or concentration of body fluid.

Background technology ''

In recent years, there have been remarkable advances in the technology for separating, purifying, or concentrating bodily fluids using semi-permeable membranes, including artificial kidneys.

As an example of body fluid purification, blood overload is particularly effective because it does not cause a rapid decrease in blood pressure, nausea, vomiting, headache, chest pain, abdominal pain, cramps, or discomfort compared to hemodialysis therapy. It is spreading. However, conventional blood filtration devices have insufficient filtration performance] 9, and the development of more sophisticated devices is required. Similarly, in blood permeation therapy in which blood transfusion and dialysis are performed at the same time, it is necessary to develop a device that has an excellent tightness.

In normal blood pressure therapy, blood flow Higher flow rates of more than 10 / min per minute have been required, but in practice such

In general, a device with an overflow rate of 70 to 80 minutes is used.

In the first place, it is said that in the treatment of blood and other body fluids, solutes such as proteins generate a concentration-polarized layer on the membrane, and the permeation performance is reduced. For this phenomenon, the following measures have been taken for flat membrane type blood transfusion devices. Flat membrane type hemodialyzers are usually used as shown in Fig. 1. Hospall's technical material (Hemofiltration, (1977)) Thus, if the blood layer 2 is divided and used with the forceps 4 as shown in Fig. 2, the performance is improved. In the usage shown in Fig. 1, blood flows from the upstream rubber blood port 5 to the blood layer 2 between the semipermeable membranes 1 and 2, as indicated by the arrows indicating the blood flow. After being processed there, it is collected at downstream blood port 3 and returned to the body. In the usage shown in Fig. 2, since a part of the blood port 3 is closed with the forceps 4, the blood is first X, X 'and then Y, Y', as indicated by the arrows. Z, in the above-in the order of Z ^1, between the blood layer that make up the flow path of the lower respectively passes in series. Similarly, use one forceps 4 and change the connection of the liquid boat 3 so that blood passes in series between the two blood layers constituting the upper and lower channels. You can do it. Split like this ο?.:? Ι It is said that the improvement in performance when used is due to the fact that the concentration-polarized layer becomes thinner due to a further increase in the blood flow rate and to an increase in the transmembrane pressure.

However, even if such measures are taken, the flow rate of the flat membrane type is insufficient for only 70 to 8 minutes under standard clinical use conditions. In addition, the extracorporeal circulating blood volume is large in the case of the flat membrane type transfusion device, which is generally avoided in size.)), But when used for the purpose of treatment, the burden on the patient is large. It is a disadvantage. On the other hand, many studies have been conducted on hollow fiber type blood filtration devices because they have the potential to be smaller and have less burden on patients than flat membrane types. However, there is a drawback that the drop in the overpass performance due to the formation of the concentration polarization layer is more remarkable than that of the flat membrane type overpass device, and its practical use has been delayed. This problem has widened the excess area with ordinary ^ over devices! ), 泸高泸 3 3 3 3 3 3 3 3 3 3 3 3 が、 3 3 、、、 3 、、、、血液血液血液血液血液血液血液.

The current measures are to develop a highly permeable membrane and to expand the membrane area as much as possible, but no blood permeation device with satisfactory performance has been obtained. For example, Akiba et Les port (Autumn 'HaTakashita: artificial organs, ^{9 0} 2, (1 9 7 8)), the increase of the effective length of the hollow fiber was rather long, the number of hollow鐡維However, even if the i9 is increased in transmembrane area, the permeation performance will improve It clarifies the matter.

The present inventors have intensively conducted experiments and studies from the viewpoint of what shape the hollow fiber type blood filtration device should have in order to avoid a decrease in performance due to the formation of the concentration polarization layer. As a result, it has been confirmed that a device having high transmissivity, which could not be realized by the conventional device, can be manufactured with the following shapes, and the present invention has been achieved. In order to facilitate understanding, the explanation has been made by taking blood permeation processing as an example, but the generation of concentration-polarized layers by proteins and cellular components causes other body fluids whose permeation performance to be reduced. Even in overprocessing, the present invention exhibits effectiveness.

An object of the present invention is to provide a hollow fiber body fluid treatment device having high filtration performance. Furthermore, the present invention is a compact in which all hollow sickles are housed in a single box, and the amount of fluid extracted from the patient's body can be relatively small. The purpose is to provide a fibrous body fluid treatment device. Disclosure of departure

The present invention is based on a large number of hollow fibers composed of a semipermeable membrane in a single box.] A plurality of hollow fiber groups composed of a plurality of hollow fibers are arranged almost in parallel, and each hollow fiber is The present invention relates to a hollow iron-type body fluid treatment apparatus in which the groups are separated from each other via a collecting chamber, and the hollow section of the hollow loose fiber group and the collecting chamber are separated from the liquid chamber by a partition member. .

The present invention also relates to the above-mentioned improved hollow fiber type body fluid. In the processing equipment, the average flow velocity in each flow path was kept as constant as possible by changing the total cross-sectional area of each hollow part for each group of hollow fibers, and the performance was further improved. A hollow fiber type body fluid treatment device is also provided.

Further, the present invention relates to the improved hollow fiber type body fluid treatment apparatus described above, and in particular, has a structure in which only one collecting chamber is provided and a group of two hollow fibers comprises one bundle. This is to provide an apparatus that is extremely easy to manufacture and has no drawbacks such as short-circuiting of the liquid to be treated.o-Brief description of drawings

Fig.1 shows a diagram of a flat membrane type hemodialysis machine. The figure and its general usage are shown. Figure 2 shows an improved method for using a flat membrane type blood analyzer as a blood filter. Fig. 3 is a front sectional view showing a two-fluid type body fluid treatment device using a hollow fiber according to the present invention. Fig.4 is a side cross-sectional view of Fig.3 A A

FIG. 3 is a side cross-sectional view of FIG. Fig. Ό is a front sectional view of the three-fluid type body fluid treatment device according to the present invention.)

The EE cross sections in Figs. 7 and 8 are shown. Fig.7 is a side cross-sectional view of Fig. CC, and Fig.8 is a side view of Fig.0. Fig.9 is an explanatory diagram showing a disturbance of hollow Take維in body fluid treatment device 3 the channel type which indicates at Fi _g .0.

Fig. 10 shows the two-channel type body fluid treatment device shown in Fig. 3.

Ο:

H no It is explanatory drawing which shows the disorder of the hollow fiber inside. Fig. 1 is a front sectional view of a two-fluid type bodily fluid treatment device manufactured from two bundles of hollow fibers according to the present invention. Fig.

2 is a cross-sectional view taken along the side FF of Fig. 11 and Fig. 1 δ is a cross-sectional view taken along the side GG of Fig. 11. Fig. 14 shows a front cross-sectional view of the coaxial two-channel type body fluid treatment device according to the present invention, Fig. 15 shows a side HH cross-sectional view of Fig. 14, and Fig. FIG. 14 is a side cross-sectional view of FIG.

BEST MODE FOR CARRYING OUT THE INVENTION

As described above, the bodily fluid treatment device is not sufficiently transitory to generate a concentration-polarized layer. In the case of a flat membrane type filtration device, the flow rate of the liquid to be treated is increased by using the method shown in Fig. -Can be done. However, a similar effect can be expected with a hollow-dake type bodily fluid treatment device, as described in the report by Akiba et al. Mentioned above. This is because, when comparing the flow path between the hollow fiber and the flat membrane, the hollow fiber is inherently more susceptible to interference due to the formation of the concentration polarization layer.

As will be described in detail below, the present inventors set up a collecting chamber for changing the flow direction of the liquid to be treated in the middle of the flow path of the liquid to be treated. J: The hollow fiber type body fluid treatment device with the drastically improved transient performance C:.: F, AT Came out.

5, FIG. 4 and FIG. 5, the bundle 10 of hollow fibers is divided into two groups of hollow fibers in the two-channel type body fluid treatment apparatus according to the present invention, and each hollow fiber is treated with a hollow fiber. The hollow part of the fiber group constitutes the first channel 15 and the second channel 14.

The partition members 20 and 21 fix the bundle 10 of hollow iron fibers, and divide the collective room 1 ^ into a liquid-tight room 24.

Further, a hollow portion of a group of hollow fibers constituting the first flow path 15 and the second flow path 14 is open toward the collecting chamber 1 1. Although the spacer 22 is not always necessary, it is convenient to divide the bundle of hollow fibers 10 into two groups of hollow stitches and fix them with the partition member 2.'0. The outer lid 27 forms a liquid-to-be-treated chamber 12 and a liquid-to-be-treated discharge chamber 18, and the outer lid 28 forms a collecting chamber 1 ό. The container 29 is a container for holding the bundle of hollow fibers 10 and forms the liquid chamber 24 _{c. When} this device is used as a filtration device, the processing liquid is treated liquid inlet nozzle 11 1 The liquid to be treated flows into / from the treated liquid introduction chamber 12, the first flow path 1 S, the collecting chamber 10, the second flow path 14, and the treated liquid discharge chamber 18 to / from the treated liquid outlet. Spills out of chisel 19. During that time, the liquid to be treated is compressed in the first flow path 13 and the second flow path 14. The liquid passed through the bore of the hollow fiber semi-permeable membrane collects in the liquid chamber 24 and is discharged from the liquid discharge nozzle 25 or 26. During normal use, use only one of the liquid ejection nozzles 25 or 2 、, for example,

O PI

WIPO You can leave the tap 3 2 in place. Normally, one discharge nozzle is sufficient as a supercharger. However, when cleaning the device before use, two discharge nozzles are easy to clean. Also, if this device is used as a hemodialysis filter, one of the drainage nozzles] 5 Add dialysate and mix it! ) The dialysis treatment can be performed at the same time as the high-performance treatment as described above.

Figures 6, 7, and 8 show the three-channel type body fluid treatment device according to the present invention. This device is manufactured by bundles of three hollow fibers 8, 9, 10] 9. Hollow fiber bundles 8, 9, and 10 are a group of hollow fibers, and the hollow portion constitutes a first flow path 15, a second flow path 14, and a third flow path 15 respectively. . The liquid to be processed flows into the processing liquid inlet nozzle 11, and the liquid to be processed is introduced into the chamber 12, the first flow path 13, the collecting chamber 16, the second flow path 14, and the collecting chamber 17. The 5th channel

The liquid to be treated and the output nozzle 19 flow sequentially through the liquid discharge chamber 5 and the liquid to be treated 18. Among them, the liquid to be treated is excessively concentrated in the first flow path 13, the second flow path 14, and the third flow path 15, and the waste liquid is collected in the waste liquid chamber 24] 9 Discharge nozzle 25 or 20] 7 Discharged-In the case of a 5-channel type device, there are two collecting chambers, collecting chambers 1ό and 17. '

When comparing the two-channel device in Fig. 5 with the three-channel device in Fig. 0, the two-channel device is preferred. The reason is the ease of manufacturing the device. F

When fabricating a road-type device, it is preferable to use a short circuit as shown in Fig. 9 if there are turbulent hollow fibers 30 in the hollow steel bundle 10. Therefore, when fabricating a device with three channels, it is necessary to distinguish the bundles of hollow fibers 8, 9, and 10 for each channel. In the case of a two-channel device (collection chamber force: only one), even if there is a disturbed hollow fiber 50 as shown in Fig. 10, it is preferable because it is not a short circuit.

The devices shown in Fig. 11, Fig. 12 and Fig. 15 show the two-fluid type bodily fluid treatment device made of two bundles of hollow fibers according to the present invention. The present apparatus is particularly suitable for simultaneous filtration and dialysis of a body fluid—an embodiment of the present invention suitable as a dialysis apparatus. In this embodiment, a group force of two bundles of hollow fibers is used.

— According to 31] 9 [^] The dialysate is separated and flows in countercurrent to the liquid to be treated, so that the dialysis efficiency can be improved at the same time.

The bodily fluid treatment device made of one bundle of hollow fibers shown in Fig. 3 is easier and cheaper to manufacture than the device made of two bundles of hollow fibers shown in Fig. 11. I like it because I can

In the apparatus according to the present invention, the number of hollow fibers contained in the housing 29 varies depending on the application, and although it is not particularly limited, it is generally 20 to 90.

5 G 0 0 0 0 lines-preferably 500 to 2 0 G 0 0 lines.

One ο: .ί? Ι _, ^ ΑΤΙΰ The meeting room in the present invention plays the following role. Explaining with the apparatus in Fig. 3, when the liquid to be treated is concentrated in the first flow path 13, a concentration-polarized layer is formed near the membrane surface by a solute such as a protein. Since the concentration unevenness due to the formation of the concentration polarization layer is eliminated by the mixing effect in the collecting chamber 1, the liquid to be treated is homogenized. Due to this mixing effect, the filtration performance of the second passage 14 is improved, and the filtration performance per unit area of the entire filtration device is also improved. When the outer lid 28 was made of a transparent material using the device shown in Fig. 3, and the flow in the 1-millimeter chamber was observed, the appearance of the mixing was clearly seen.

The volume of the collecting room is not particularly limited as long as it is within a range where the mixing effect can be achieved, but the following is usually preferable. That is, let Ρ be the volume of the hollow portion of the semipermeable portion of the hollow portion of the group of upstream hollow fibers communicating with the individual collecting chambers, and let the volume of the collecting chamber differ from the volume of the collecting chamber. When the total volume of the hollow portions of the group of hollow fibers on the upstream and downstream sides, which are covered by the partition material of the collecting chamber and the volume of the impermeable portion, is defined as I. It is preferable to use 0.10 <0 1 ⁾ 0.70. It is even more preferable that 0.10 <IΡ0.40.

If I 小さい is less than 10, the mixing is insufficient and the effect of eliminating the concentration unevenness due to the formation of the concentration polarization layer is small. In addition, if the

〇 :. ':? ι It is not preferable because the amount of the liquid to be treated is large.

Therefore, it is preferable that J9 is smaller than 0.40 in a normal size transmission device. It is preferable that the I / P is small even in a small-sized transmission device, but the range is slightly wider and the upper limit is 0.70.

Next, the hollow fiber constituting the flow path has a different force depending on the purpose, and has a pore size of 0.002 to δ μ Ο pore in terms of the pore size obtained from the Hagen-Poiseuile formula force. Hollow steel membrane is suitable. In particular, in the case of a blood transfusion device used for blood transfusion therapy, the bore size is from 0.02 to 0.002.

0.05 ", which is preferably a hollow woven membrane that is substantially impervious to bovine serum albumin, and is intended to separate blood components and plasma. For this purpose, hollow fiber membranes with a bore size of 0.04 to 3 are preferred.

Similarly, the inner diameter of the hollow fiber is preferably in the range of 100 to 700 ^, but is particularly preferably in the range of 150 to 400. If the inner diameter is too small, the shearing force applied to the liquid to be treated is too large, which is preferable. On the other hand, if the inner diameter is too large, it is not preferable that the amount of the liquid to be treated is increased with respect to the excess area. Also, it is not preferable because the device becomes larger.

The material of the hollow fiber is not particularly limited, but is not limited to polymethylmethacrylate, polyacrylonitrile, polyethylene glycol, and polyamide. , Tria-fe chi-no-k-no-ra

C '.- IPI,'vh'O". It is desirable that the material be a material having good water permeability, such as polyethylene, ethylene glycol alcohol copolymer.

Although the improvement in the filtration performance of the hollow fiber type body fluid treatment apparatus was found by the above-described invention, the following invention is a method for further improving the filtration performance.

In other words, in a general channel-type hollow iron-type body fluid treatment device, since the semipermeable membrane is made of hollow fiber, the cross-sectional area of the liquid-to-be-processed in the filtration part is from the upstream. It is almost constant up to the downstream. Therefore, the liquid to be treated is concentrated as it goes downstream, and the flow rate is reduced, and the performance is significantly reduced due to the formation of the concentration polarization layer. However, in the above-described multi-channel hollow iron type body fluid treatment apparatus, the cross-sectional area of the liquid to be treated is changed for each channel, and the average flow velocity of the liquid to be treated in the upstream and downstream channels is changed. Since the pressure can be made the same as much as possible, it is possible to enhance the performance on the downstream side without unnecessarily increasing the pressure loss in the flow path.

Of the group of hollow fibers that open to the individual gathering rooms, they are the gathering rooms! ) Let M be the sum of the cross-sectional areas of the hollow sections of the group of hollow steel pipes on the upstream side, and N be the sum of the cross-sectional areas of the hollow sections of the group of hollow fibers on the downstream side. If 25 <N / M <5.0, the effect of the 2 ^ road is recognized, but preferably 0.25 and N / M <1.0] ?, and more preferably. Is 0.40 <N / M <0.85.

The optimal value of the N / M ratio is based on standard use.

ΟΜΡΙ

>.-"" ー Αΐίθ " Must be determined by over-conditions. By changing the ratio Ν / Μ, the average flow velocity of the liquid to be treated in each flow path is kept as constant as possible, and the pressure loss in the entire flow path of the liquid to be treated is unnecessarily increased. Thus, the performance on the downstream side can be improved, and the overall performance can be improved. The NZM ratio can be easily changed by changing the inner diameter or the number of hollow fibers constituting the flow path.

The method of dividing the flow channel using forceps 4 as shown in Fig. 2 using the flat membrane type blood filtration device shown in Fig. 1 has been described above. Saito et al. Reported in a report (Hiroshi Saito et al .: Records of the 7th Tokyo Dialysis Conference, 1979.2.2 (published 198.000)). According to Saito et al., A forceps was used in a flat membrane type filtration device with one blood layer.

It is said that the overall flow rate is almost the same even if the ratio of the layers used in the two-split method is changed. In the opinion of the present inventors, such a result is caused by the fact that in the case of a flat membrane type blood permeation device, the membrane interval increases when pressure is applied, and it is difficult to keep the membrane interval constant. Conceivable.

On the other hand, in the case of a hollow fiber type body fluid treatment device, the volume of the hollow portion hardly changes even when pressure is applied.

It is important to make the flow rate as small as possible] and keep the average upstream and downstream velocities as constant as possible in order to improve the filtration performance. It is effective.

Fig.14, Fig.5, Fig.1ό show the coaxial two-channel type body fluid treatment device according to the present invention.] The group of hollow fibers in the outer periphery is the first channel. The group of hollow steel at the center is the second channel 14.

In addition, as another embodiment of the present apparatus, a replenisher was injected], a sample 7t j9, or a sensor for introducing a sensor of some kind of measuring instrument. Devices with nozzles in the collection room are also included.

Industrial applicability

As described above, the bodily fluid treatment device according to the present invention is particularly effective for blood transfusion therapy that requires strict size reduction. It is also particularly effective in hemodialysis therapy, which has both the advantages of blood diffusion therapy with good removal of small molecular weight substances and good blood fluid therapy with so-called removal of medium molecular weight substances. It is also effective for other therapies that want to obtain high overflow from the blood. For example, it is also effective in a therapy in which the body fluid is removed by a blood transfusion therapy corresponding to an increase in body weight first, and then the blood flow is substantially reduced to zero and only blood analysis is performed.

In addition, it is effective as a means to separate the plasma components from the blood and form components such as white blood cells and red blood cells for the purpose of obtaining a component transfusion product! ) When a harmful component is present in a plasma component or a solid component for the purpose of treatment, an attempt is made to separate the harmful component into plasma and a component to remove the component.

OM? I ν,. +-Ι iρrο It is also effective when .

Also, for example, the liquid to be treated may be a body fluid such as ascites fluid instead of blood fuzz, and may be used for removing harmful components or recovering active components. The body fluid treatment device of the present invention is also effective when trying to separate or when concentrating a body fluid containing a formed component.

Example 1.

Without passing bovine serum albumin, a hollow fiber with a pore size of 0.008 μm, an inner diameter of 240 μm, and an effective length of 19 c determined by the Hagen-Poiseuille equation was used as the first fiber. A two-channel type body fluid treatment device shown in Fig. 3 was manufactured using ό500 channels for the channel and ό500 channels for the second channel. This device

I / P is 0.57, N / M is 1.0, and the total excess area is 1.86 ηΐ. A blood transfusion experiment was performed using bovine blood prepared with a hematocrit value of 20.1% and a total protein concentration of 7.Q ^ Zdl. The flow rate was 200 m / min at a flow rate of 200 m / min, and the average overpressure was 5100 mHg.

On the other hand, the excess area using 500 hollow fibers with the same bore size, the same inner diameter, and an effective length of 38 was used.

1. Using a conventional one-pass type body fluid treatment device with a collection chamber of 800 w ^2, the excess flow rate was measured under the above blood conditions and operating conditions, and the flow rate was 84 ml / min. It was hot. That is, in the two-channel type body fluid treatment apparatus of the present invention, 沪 The flow rate is 21% higher than that of a one-pass type body fluid treatment device with the same flow area.

Example 2.

Without passage of bovine serum albumin, H agen-

Pois size 0.08 μm, inner diameter 24.2 μm, effective length 19.7 hollow fibers determined by Poi seuille's equation に 500 pieces of hollow fiber in the first flow path and に 500 hollow fibers in the second flow path Fig. 4

The two-channel body fluid treatment device shown in Fig. 5 was manufactured. The IZP of this device is 0.28, NZM is 0.09, and the total

1. ό 5 m ² . A blood transfusion experiment was performed using a bovine blood solution prepared with a hematocrit value of 19.5% and a total protein concentration of 0.9 Zd1. The side blood flow was 20 QmZ, the average overpressure was 520 gHg, and the overflow was 108 minutes.

In contrast,泸過area 1. 6 5 w ² slave using a hollow fiber 1 1 0 0 0 present in the same Boasai's inside diameter, effective length - coming-type first channel type have no collecting chamber of With respect to the bodily fluid treatment device, the flow rate under the blood conditions and the use conditions was measured and found to be 8 l / min. That is, the excess flow rate in the two-pass type body fluid treatment device of the present invention is 26% higher than that of the one-pass type body fluid treatment device having the same passage area. '

In the two-fluid type body fluid treatment device shown in Fig. 3, the same pore size, inner diameter, and effective length of hollow fiber were used. ό 500 pieces When used in I / P, I / P is 0.41 and N / M is 1.44. In this case, the ^ overflow under the above blood conditions and use conditions was 102 Z minutes. In other words, in this case, although it is 19% higher than that of the conventional flow path type body fluid treatment apparatus having no collecting chamber, the 1 /? Force; 0.28, N / M described above are higher. Ό% lower than the usage condition of 0.09.

Example 5.

Do not allow bovine serum albumin to pass ^

Poise size obtained by Poiseulle's equation 0.G10, inner diameter 25 μ, effective length 19.5 cm, 500 hollow fibers in the first flow path, 500 hollow fibers in the second flow path A five-channel type body fluid treatment device shown in g.6 was manufactured using 350 pieces and 25 ″ bits for the third channel. The first channel and the second channel of this device were I / I is 0.23, N / M is 0.70, IZP is 0.25, and N / M is 0.71 between the second and third channels. The total area of the transfusion is 1-9 m.Blood using bovine blood prepared with a hematocrit value of 21% and a total protein concentration of Z0 / ά1 for this device. When the overexperiment was performed, the excess flow rate at an inlet side blood flow rate of 200 πβZ and an average overpressure of 470 Hg was ^ ^ 2 m extra.

And pairs to this, the same Boasa size b, an inner diameter, the effective length of the hollow鎵維1 1 0 Q 0 present泸過area 1.1 6 9 77i ² set chamber have not conventional flow path using Type body fluid Using this, the flow rate under the above blood conditions and use conditions was measured to be 84 minutes. That is, the amount of overflow in the three-flow-path body fluid treatment apparatus according to the present invention is 33% higher than that of the one-flow-path body fluid treatment apparatus having the same passage area.

Example 4.

Blood / J, without passing through the plate, flow through the hollow fiber with a pore size S O. όμ, inner diameter of 3700μ, and effective length of 18 using the Hagen-Pois eu i 11 e equation. Using 1700 lines for the road and 1300 lines for the second flow path, a two-flow type body fluid treatment device as shown in Fig. 3 was fabricated. In this device I / P is 0. 5 3, N / M is 0.7 6 total泸過area is 0. 0 3 W ^2. The blood flow experiment was performed using bovine blood prepared with a hematocrit value of 25% and a total protein concentration of 5 / d1. The blood flow rate at 200 ZZ min and an average overpressure of 100 挪 Hg was 47 min.

On the other hand, conventional one-flow type bodily fluid treatment that has a 0.0 Sw ² collection chamber using 300 hollow fibers of the same pore size, inner diameter, and effective length Using the apparatus, the plasma flow rate was measured at 40 / min under the blood conditions and use conditions described above. That is, the plasma flow rate in the two-flow-path body fluid treatment device according to the present invention is 18% higher than that of the conventional body fluid treatment device.

Ο ΡΙ

Claims

SB request range

1. A plurality of hollow fiber groups composed of a large number of hollow fibers made of a semipermeable membrane in a single box are arranged almost in parallel, and each hollow fiber group passes through an assembly chamber. The hollow fiber of the hollow fiber group and the collecting chamber are separated from each other by the partition material.

2. The hollow fiber type body fluid treatment apparatus according to claim 1, wherein the number of the collection chamber is only one.

o 5. The hollow fiber type body fluid treatment device according to claim 1, wherein the number of the collection chamber is only one, and the two groups of the hollow iron fibers form one bundle.

4. Among the groups of Seki Air Fibers communicating with the individual collecting chambers, let P be the volume of the hollow part of the semipermeable part 5 of the group of hollow fibers on the upstream side. The volume of the chamber and the volume of the opaque portion of the hollow portion of the upstream and downstream hollow fiber groups communicating with the collecting chamber, which are covered by the partitioning material of the collecting chamber, are determined. The hollow fiber type liquid processing apparatus according to claim 1, wherein when the total volume is I, 0.10 <IZP and 0.70.

5. Let P be the volume of the hollow part of the semi-permeable part of the group of hollow fibers on the upstream side of the group of hollow fibers communicating with the individual collecting chambers. And 5 hollow portions of the upstream and downstream hollow fiber groups communicating with the collecting chamber, i ^ro and ΛΤΙ are covered by the partition material of the collecting chamber. The volume of the impermeable part and

2. The hollow fiber type bodily fluid treatment device according to claim 1, wherein, when I is satisfied, the following condition is satisfied: α <θ4θ.

6. The hollow fiber type bodily fluid treatment device according to claim 1, wherein the pore size of the semipermeable membrane is 0.02 to 3 μm.

7. The hollow iron according to claim 1, wherein the bore size of the semipermeable membrane is aQ02 to 0.05 ", and substantially does not pass bovine serum albumin. Weir-type liquid processing o

8. The hollow fiber type bodily fluid treatment device according to claim 1, wherein the pore size of the semipermeable membrane is 0.04 to 5 µm and substantially does not allow a cellular component to pass therethrough.

9. The hollow fiber type body fluid treatment apparatus according to claim 1, wherein the inner diameter of the hollow fiber is 100 to 700.

1 0. The inner diameter of the hollow fiber is 15 C! The hollow fiber type body fluid treatment device according to claim 1, wherein

1 1. Of the group of hollow fibers communicating with the individual collecting chambers, this is the collecting chamber.] The sum of the cross-sectional areas of the hollow sections of the group of hollow fibers on the upstream side is 5. The hollow fiber mold according to claim 1, wherein when the total sum of the cross-sectional areas of the hollow portions of the group of the hollow fibers on the downstream side is set to 'N, 0.25 く /Μ<5.0. Body fluid treatment device.

2. A group of hollow fibers that are not communicating with each individual collection room

· ['One CIAFI, M is the sum of the cross-sectional areas of the hollow sections of the group of hollow fibers on the upstream side, and M is the sum of the cross-sectional areas of the hollow sections of the group of hollow steel fibers on the downstream side. 2. The hollow fiber type bodily fluid treatment apparatus according to claim 1, wherein 0.25 <N / M <1.0 where N is N.

1 5. Out of the group of hollow fibers that communicate with the individual collecting chambers, the sum of the cross-sectional areas of the hollows of the group of hollow fibers upstream of the collecting chamber is j and the downstream of the collecting chambers is j9. The hollow fiber type bodily fluid treatment according to claim 1, wherein the sum of the cross-sectional areas of the hollow portions of the group of hollow fibers on the side is defined as N.o 0.40 <M / N <0.85. Equipment

,, ^Ν ' ^{/ ίρ} .