JPS58190449A - Hollow yarn type blood dialyser - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION This invention relates to a hemodialysis machine. More specifically, the present invention relates to a hemodialyzer that can efficiently perform dialysis using two or more types of hollow fiber dialysis having different semipermeability.

Hemodialysis has been used for the treatment of chronic renal failure for a long time, but in recent years, hemofiltration (so-called hemofiltration) and filtration dialysis (hemofiltration), which overcome the weaknesses of conventional hemodialysis, have been used.
So-called hemodiafiltration) has also come to be used in combination.

In general, it is more efficient to remove substances with relatively low molecular weights, such as urea and creatinine, from the blood of patients suffering from chronic renal failure through dialysis, and as the molecular weight increases, they diffuse more! It is said that it is more efficient to remove it by filtration because the box deteriorates.

In hemodialysis, blood is passed on one side of a semipermeable membrane and dialysate is placed on the other side, and substances are exchanged between the two fluids via the membrane to remove waste products from the blood and maintain the appropriate electrolyte concentration in the blood. It also filters out excess water in the body. (Hereinafter, the water device that filters and removes water from the patient's body is referred to as the amount of water removed.) In general hemodialysis, the amount of water removed in one treatment is /-jl, and in hemofiltration, it is l! Treatment methods include removing water from the body and returning fresh replacement fluid 10-COX to the body.

As semipermeable membranes used in hemodialysis, cellulose membranes, which have excellent dialysis properties for solutes, especially low-molecular-weight substances, are often used. However, regenerated cellulose membranes generally have poor water permeability and are not suitable for hemofiltration.

On the other hand, in porous membranes made of synthetic polymers, the pore size of the twinkling pores (
Some membranes have a relatively large pore size (hereinafter referred to as "bore size") and therefore have excellent water permeability, making them suitable for use in hemofiltration membranes.On the other hand, they generally have poor solute permeability and are often unsatisfactory as dialysis membranes.

In addition, dialyzers that combine membranes with excellent dialysis and membranes with excellent filtration and take advantage of the characteristics of both membranes have been considered or proposed, but none have enough advantages to be put to practical use. There is no dialyzer with a combination of different membranes.

The purpose of the present invention is to have a new effect that combines the advantages of hemodialysis and hemofiltration, and to be able to dialyze not only low-molecular waste products but also so-called middle-molecular waste products and high-molecular waste products.
Furthermore, hemodialysis.

It is an object of the present invention to provide a dialyzer that can be used not only for hemodiafiltration and hemofiltration, but also causes less blood damage.

The purpose of the present invention is to load a hollow fiber made of a semipermeable membrane into a nurse, fix both ends of the hollow fiber to a case with a solidifying liquid, and place blood cells inside the hollow fiber and dialyze the blood cells outside the hollow fiber (■). In a hemodialyzer, in which hemodialysis is performed by flowing a liquid, and the hollow fibers are composed of at least one or more types of hollow fibers with different semipermeability, the hollow fibers are separated by type and loaded into a case. This is achieved by using a hollow fiber hemodialyzer characterized in that the boundaries where the threads meet are separated by partitions that do not permeate water and have openings near both ends.

Further, in the hollow fiber hemodialyzer described above, it is preferable that the cross section of the case is approximately circular.

Furthermore, it is preferable to arrange hollow fibers of different semipermeability in concentric circles and divide each type of spring using a dividing member having openings near both ends thereof.

Furthermore, it is preferable if both ends of the partitioning material are not submerged in the solidifying liquid so that the partitioning material can be substantially opened.

On the other hand, it is even better if the hollow fibers of the larger type of molecular fractionation lid of the semipermeable membrane are arranged in the center and the hollow fibers with smaller molecular weight fractionation are arranged on the outside.

The details of the present invention will be explained in detail with reference to the accompanying drawings.

FIG. 1 is an example of a sectional view of a dialyzer embodying the present invention. FIG. 2 is a cross-sectional view of the dialyzer shown in FIG. 1 taken along plane AA. In FIG. 1, hollow fibers j and 7 are provided with membranes exhibiting the same semipermeability, and hollow fiber 6 is provided with a membrane having a different semipermeability from hollow fibers j and 7. A dividing member 21 is provided at the boundary where the hollow fibers t and j are in contact with each other. The section 21 has openings, 23 and lλ3, near its ends. here,
It is important that the dialysate cannot move from one space of the partitioning member 21 to the other space from any part other than the openings 23 and /3.

Now, the blood flows in from the boat/, is distributed by the header, flows into a number of hollow fibers t, z, 7, etc., and flows into the outlet header 1.
The dialysate collected from the dialysate boat IOa, which is collected in the dialyzer 0λ, flows in from the outlet boat IO′l, and is discharged from the dialysate boat ≠, is distributed throughout the hollow fiber outer circumferential space through the dialysate header 101.

Meanwhile, the dialysate is also distributed through the opening /23 into the area delimited by the dividing member 2/, flows through the hollow fiber peripheral space /c to the opening n, and collects in the dialysate header l.

On the other hand, the dialysate flowing outside the dividing member 21 passes through the hollow fiber outer peripheral space /1 and 13t and collects in the dialysis header t. Here, it is desirable that the dialysate flowing through the space /l or 13 not be mixed with the dialysate flowing through the space l until it reaches the dialysate header t. For this reason, it is preferable that the partitioning material 2/ is made of a material that itself does not permeate water, such as vinyl chloride, polyethylene, polystyrene, or the like. The inflow and dispersion of the dialysate into the area divided by the partition material 1 can be adjusted by increasing or decreasing the size of the openings 1 and 3 in the partition material, and the number of openings is determined by adjusting the number of openings so that the dialysate flows into the area 7. It is preferable that there are q or more openings on one side so that the fluid flows evenly within the partitioning material 2, but they do not necessarily have to be holes, and may be several groove-shaped openings along the circumference of the dividing material 2/, and the shape of the openings is You can choose freely according to your purpose.

On the other hand, when hollow fibers with different semipermeability are classified according to the molecular weight of solute molecules that can pass through the pancreas (i.e., molecular weight cutoff), the type of hollow fiber with a small cutoff molecular weight is placed outside the dividing material λl, It is desirable that the hollow fibers with larger molecular weights be placed inside the dividing material.

During dialysis, blood is dialyzed through the membrane while flowing through the hollow fibers from / to 10/, and on the outside of the dividing material λl mainly contains low-molecular waste products, while inside the dividing material λl it is mainly subjected to ultrafiltration. and waste products with large molecular weights are dialyzed.

Since the dialysis resistance of substances with a large molecular weight is mainly membrane permeation resistance, the dialysis efficiency of large molecular waste products is not greatly affected even if blood is ultrafiltered in large numbers inside the dividing member λl.

On the other hand, a membrane with a small molecular weight cut-off is placed on the outside of the dividing material 2/, but in dialysis of low-molecular substances, so-called membrane resistance is rate-determining, so ultrafiltration of blood is suppressed in this area. It is necessary to maintain the average concentration of low-molecular waste products in the dialysate so that it does not become unintentionally high, and to increase the flow of the dialysate to lower membrane resistance. For this purpose, it is easy to set the openings /23 and 23 such that more dialysate flows in the outer area of the partition j/ than in the inner area of the partition 21; It is also possible to provide small openings in 23 and lug 3 that are not substantially inflow of dialysate into the area inside 21 and are simply necessary for draining P fluid. In this case, since it is necessary to relatively increase the amount of blood flowing through the hollow fibers inside the dividing member 21, baffles of μl and /4t/ may be provided in one part of the header.

Although FIG. 2 shows the case where the cross section of the case 31 is circular, in carrying out the present invention, the cross section of the case need not be fixed to a circular shape, but an elliptical or polygonal cross section may be adopted. You can also do it. When a case cross section with a polygonal cross section is adopted, the shape of the dividing member can also be arbitrarily selected.
It is not fixed in a concentric shape like 27 in the figure. However, for practical purposes and production work, it is suitable to have a circular case and arrange the dividing members 2/2 on concentric rods, or to manufacture a 6 analyzer having uniform performance without unevenness in the flow of dialysate.

Furthermore, the dividing material 21 may be made of hard synthetic resin.
However, in order to uniformly disperse the hollow fibers inside and outside the dividing material, it is preferable to use a flexible vinyl chloride tube or polyethylene film. Particularly in embodiments in which the sections J/ are arranged concentrically in a circular case, the sections 2/ are preferably heat-shrinkable lubricant tubes. In this case, the hollow fiber bundle to be placed on the innermost side is loaded into the tube, heated to an appropriate temperature to bring the hollow fiber bundle and the tube into close contact, and then the hollow fibers to be placed on the outside are placed on the outside of the tube, and then It can be loaded into a nurse and both ends of the hollow fiber can be fixed with an assimilable liquid. When using three or more types of hollow fibers with different semipermeability, the dialysis performance can be improved by repeating the process of loading the hollow fibers into the heat-shrinkable tube, heating contraction, hollow fibers around the tube periphery, and loading them into the heating tube. You can get an excellent dialyzer□.

FIG. 3 is a cross-sectional view of another embodiment of the invention.

In this example, both ends of the dividing material 32/ are not buried in the solidifying liquid 303, and by appropriately selecting the distance between the assimilable liquid 303 and the tip of the dividing material 32/, they essentially act as openings. be able to.

It is particularly convenient to select flexible tubes as the dividing members J, 2/.

The present invention is particularly effective when performing hemodialysis for the purpose of removing large amounts of water or removing polymeric wastes. In particular, a membrane with a large molecular weight cutoff, that is, a large bore size, and a very large ultrafiltration rate is arranged inside the partitioning material 2/, and a membrane with good low molecular dialysis properties is arranged outside the partitioning material 2/. In this case, the ultraviolet E filtration of blood mainly occurs in the membrane inside the partitioning material 21, so filtration and removal of polymeric wastes are performed, and on the outside of the partitioning material 2/, an effective dialysis can be performed.

In the present invention, membranes with different semipermeability mean membranes with different molecular weight fractions or ultrafiltration rates, and do not mean any limitation on the membrane material. Therefore, semipermeable membranes made of regenerated cellulose, cellulose derivatives, polyacrylonitrile, etc. can be freely selected depending on their semipermeability.

Furthermore, in the present invention, the sectioning material having openings near both ends is not limited to one having openings only near both ends, but it is sufficient to have openings at least near both ends.

However, if a considerable opening is provided in a portion other than near both ends, for example, in the center, the effect of the present invention will be reduced depending on the size and position of the opening.

11J1L Copper ammonium ration hollow fibers (referred to as the first membrane) o, r vl and aromatic polysulfone hollow fibers (referred to as the second membrane) manufactured by West German Membrana Co., Ltd. 0. Using J &, first bundle only the second membrane and put 0.711 on the outside.
A 11-thick vinyl chloride dividing material was placed.

After that, the third membrane is arranged evenly on the outside of the partitioning material and placed in a cylindrical outer cylinder having a dialysate inlet and outlet, and the nurse and the hollow fiber are sealed liquid-tight with polyurethane adhesive at both ends of the outer cylinder. After adhesion and solidification, the hollow fiber was opened to provide an inlet and outlet for blood. Furthermore, there are widths λpeng and λpeng on the circumference near both ends of the sectioned material, respectively.
A groove with a length of 3 was provided so as to cover the entire circumference. In addition, as a result of examining the molecular weight fraction of the second membrane, the molecular weight λ”y,
The inhibition rate of ooo molecules was SO%. On the other hand, using the outer cylinder of the above example, only the first film was inserted and polylined with polyurethane as in the above example to prepare a comparative example. Vitamin B was added to the blood side of each dialyzer in the example and comparative example.
Distilled water containing -/kokoda/d1 and inulin o, /q/a1 was run for 20047 minutes, and distilled water was run through the dialysate stool for SOO-7 minutes, and P Tsunoda was j Q 11
! Solute clearance (C
L) was calculated using the following formula, and the following results were obtained.

Clearance calculation formula where: CL: Clearance CB1: Solute concentration at blood side inlet CBO: Solute concentration at blood side outlet Qnt: Flow rate Q at blood side inlet? = Ultrafiltration amount Example λ As the second membrane, the same hollow fibers o and r as the first membrane of Example/
Using wl, the inner diameter is 2 and the molecular weight cutoff is l↓000. Ultrafiltration rate of water j Od / wl −h
Cellulose acetate hollow fiber of r -5a)i g0
．． 21/, first load the second membrane onto a cylindrical vinyl chloride shrink film, and heat shrink the shrink film onto charcoal (filling rate 3j~4t!%) until the hollow fibers are spaced too closely. After that, a second membrane was placed on the outside and loaded into a cylindrical nurse to form a dialyzer.

The shrink film was set so as to be short by /Qm from both ends of the polyurethane surface of the dialyzer to form an opening. On the other hand, as a comparative example, a 1W' dialyzer made of copper ammonium rayon hollow fibers was used as in Example 1. Next, bovine blood containing 1% hematocrit (
Inulin 0. / drop / d1 addition) at a rate of 200 per minute, set Kindaria to the specified #darkness on the dialysate side, and set the limit Piii
Dialysis was performed by changing the p overpressure at any time so that the p-overpressure was per hour/l, and clearance and blood damage (hemolysis) were examined. The experiment was conducted while adding separately prepared bovine serum so that the hematocrit of the bovine blood was always maintained at 2j%. (Dylysis 1ml1lljJ7υ) The results were as follows.

[Brief explanation of the drawing]

FIG. 1 is a perspective view of an embodiment of a hollow fiber dialyzer according to the present invention, and FIG. 2 is a sectional view taken along the line AA in FIG. 1. FIG. 3 is a perspective view showing another embodiment of the invention. /: Blood boat Kono: Kairobe Hiroshi: Dialysate boat 31: Koos j: Hollow fiber 32/
: Sectioning material t: Hollow fiber different from j 3λ3: Opening 21:
Sectional material patent applicant Nikkiso Co., Ltd. Shi--L

Claims (1)

[Claims] (1) A hollow fiber made of a semipermeable membrane is loaded into a case, both ends of the hollow fiber are fixed to a tooth with a solidifying liquid, and blood is placed inside the hollow fiber and dialyzed outside the hollow fiber. In a hemodialyzer that performs hemodialysis by flowing a liquid and is made up of at least two or more types of hollow fibers with different semipermeability, the hollow fibers are sorted by type and loaded into a nurse. A hollow fiber type 3 blood escape device characterized in that the boundary where different hollow fibers adjoin each other is separated by a dividing material that does not permeate water and has openings near both ends. (3) Hollow fibers according to claim 2, which are formed by arranging hollow fibers with different semipermeability in a concentric circle and dividing each type with a dividing member having openings near both ends thereof. type hemodialyzer. (≠) The hollow fiber hemodialyzer according to Claims 2 and 3, wherein the dividing member is substantially opened by not immersing both ends of the dividing member in the solidifying liquid. (j) A hollow fiber hemodialyzer according to claims 3 and 5, in which the dividing member is made of a flexible tube-like material. (6) Claims 3, μ, and 5 of the semipermeable membrane in which hollow fibers of a type with a higher molecular weight cutoff are arranged in the center and hollow fibers with a smaller molecular weight cutoff are arranged on the outside. The hollow fiber hemodialyzer described.