JPH0244226B2 - - Google Patents
Info
- Publication number
- JPH0244226B2 JPH0244226B2 JP60102773A JP10277385A JPH0244226B2 JP H0244226 B2 JPH0244226 B2 JP H0244226B2 JP 60102773 A JP60102773 A JP 60102773A JP 10277385 A JP10277385 A JP 10277385A JP H0244226 B2 JPH0244226 B2 JP H0244226B2
- Authority
- JP
- Japan
- Prior art keywords
- fins
- hollow fibers
- hollow fiber
- hollow
- present
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 239000012510 hollow fiber Substances 0.000 claims description 79
- XSQUKJJJFZCRTK-UHFFFAOYSA-N Urea Chemical compound NC(N)=O XSQUKJJJFZCRTK-UHFFFAOYSA-N 0.000 claims description 5
- 239000004202 carbamide Substances 0.000 claims description 5
- 239000012528 membrane Substances 0.000 description 18
- 239000012530 fluid Substances 0.000 description 13
- 239000008280 blood Substances 0.000 description 12
- 210000004369 blood Anatomy 0.000 description 12
- 239000000463 material Substances 0.000 description 10
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 8
- 238000000926 separation method Methods 0.000 description 6
- 238000000502 dialysis Methods 0.000 description 4
- 239000000243 solution Substances 0.000 description 4
- 238000009987 spinning Methods 0.000 description 4
- 239000002585 base Substances 0.000 description 3
- 229920002678 cellulose Polymers 0.000 description 3
- 239000000835 fiber Substances 0.000 description 3
- 238000001914 filtration Methods 0.000 description 3
- 239000007789 gas Substances 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 229920001747 Cellulose diacetate Polymers 0.000 description 2
- 239000002202 Polyethylene glycol Substances 0.000 description 2
- 239000000853 adhesive Substances 0.000 description 2
- 230000001070 adhesive effect Effects 0.000 description 2
- 239000001913 cellulose Substances 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000003792 electrolyte Substances 0.000 description 2
- 239000000203 mixture Substances 0.000 description 2
- 239000004014 plasticizer Substances 0.000 description 2
- 229920001223 polyethylene glycol Polymers 0.000 description 2
- 239000000126 substance Substances 0.000 description 2
- 239000002699 waste material Substances 0.000 description 2
- 206010003445 Ascites Diseases 0.000 description 1
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 description 1
- 208000023275 Autoimmune disease Diseases 0.000 description 1
- JOYRKODLDBILNP-UHFFFAOYSA-N Ethyl urethane Chemical compound CCOC(N)=O JOYRKODLDBILNP-UHFFFAOYSA-N 0.000 description 1
- 239000004952 Polyamide Substances 0.000 description 1
- 239000004695 Polyether sulfone Substances 0.000 description 1
- 208000001647 Renal Insufficiency Diseases 0.000 description 1
- 239000003513 alkali Substances 0.000 description 1
- 239000007864 aqueous solution Substances 0.000 description 1
- 210000001124 body fluid Anatomy 0.000 description 1
- 239000010839 body fluid Substances 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 230000000052 comparative effect Effects 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 229920001577 copolymer Polymers 0.000 description 1
- 238000002788 crimping Methods 0.000 description 1
- 230000002950 deficient Effects 0.000 description 1
- 229910001873 dinitrogen Inorganic materials 0.000 description 1
- 238000001631 haemodialysis Methods 0.000 description 1
- 230000000322 hemodialysis Effects 0.000 description 1
- 239000011796 hollow space material Substances 0.000 description 1
- 210000003734 kidney Anatomy 0.000 description 1
- 201000006370 kidney failure Diseases 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 210000004185 liver Anatomy 0.000 description 1
- 210000004072 lung Anatomy 0.000 description 1
- 239000000155 melt Substances 0.000 description 1
- 238000012856 packing Methods 0.000 description 1
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 1
- 229920002492 poly(sulfone) Polymers 0.000 description 1
- 229920002239 polyacrylonitrile Polymers 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920006393 polyether sulfone Polymers 0.000 description 1
- 239000004926 polymethyl methacrylate Substances 0.000 description 1
- 229920000098 polyolefin Polymers 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000001223 reverse osmosis Methods 0.000 description 1
- 238000007127 saponification reaction Methods 0.000 description 1
- 230000008961 swelling Effects 0.000 description 1
- 238000000108 ultra-filtration Methods 0.000 description 1
- 229920003169 water-soluble polymer Polymers 0.000 description 1
Landscapes
- Separation Using Semi-Permeable Membranes (AREA)
- Artificial Filaments (AREA)
- Spinning Methods And Devices For Manufacturing Artificial Fibers (AREA)
- External Artificial Organs (AREA)
Description
〔利用分野〕
本発明は、選択透過性のフイン付異形中空糸を
収納した血液透析器を提供するものである。さら
に詳しくはフイン高さ、フイン間の距離が実質上
同一でないことを特徴としたフイン付異形中空糸
を収納した血液透析器に関する。
〔従来技術〕
従来より腎不全患者の血液を浄化し、余剰の水
分を除去するために、血液透析器が使用されてい
る。これは容器の中に透析膜例えば中空糸膜を多
数本収納し、その中空内部に患者の血液を流し、
外部即ち中空糸膜間に透析液を流して、中空糸膜
を介して透析によつて血液中の老廃物を除去し、
電解質濃度を調整すると共に中空糸膜内外に圧力
差を与え、限外過によつて血液中の余剰水分を
除去するものである。また、限外過のみによつ
て多量の水分と共に老廃物などを除去し、抜きす
ぎた水分を電解質などの必要成分と共に補給する
方法(血液過)も実状に応じて適用されてい
る。さらに血液中から血漿を分離し或いはその血
漿の中から特定の有害成分を除去して、自己免疫
疾患などを治療するために中空糸膜を使用するこ
とも臨床的に試みられている。
透析器の最も重要な性能である透析性能につい
て従来より各種の工夫がなされ改善が行われてき
た。しかしながら透析器内の中空糸間の密着によ
る透析液の偏流の問題が十分に解決されたとは言
えない。これまでの解決策の例としては、透析器
容器中への中空糸の収納量(充填率)をある程度
上げることにより、あるいは中空糸を交差させる
ことにより透析液流動抵抗をもたせ、流れの均一
化をはかることがなされた。更に、中空糸に捲縮
を与えたり、中空糸の周りにカバーヤーンを巻き
つけることにより、中空糸単糸相互の間の密着を
防止すると共に、容器内で均一に分布させ透析液
流動による物質移動の効率化がはかられた。しか
しながら、これらの解決策はまだ十分なものとは
言えず、さらに改善が望まれている。
〔発明の目的〕
本発明は、これらの問題点を解決し、血液処理
等の流体分離において分離効率の優れた中空糸膜
あるいは中空糸束及びそれを充填した流体分離器
を提供することを目的としている。特に流体分離
器内の充填状態が均一になりやすく、充填密度を
高くした場合においても中空糸どうしの密着が非
常に起きにくい中空糸あるいは中空糸束を得るこ
とを目的とするものである。
〔発明の構成〕
本発明者らは、かかる目的を達成するために鋭
意研究を行なつたところ、複数条のフインを有し
た異形中空糸が好ましく、特にフインの高さやフ
イン間の周上距離を不同一にすることが有効であ
ることを見い出し本発明に到達した。
即ち本発明は、選択透過性中空糸を収納した血
液透析器において、外周部に長手方向に延長され
た2〜10条のフインを有し、該フイン各条の平均
高さが実質上不同一でありかつ最も高いフインの
平均高さが最も低いフインの平均高さの1.5〜10
倍であり、さらには隣接2条間距離が実質上不同
一でありかつ該隣接2条間距離の最大値が最小値
の1.5〜10倍である選択透過性中空糸が収納され
ており、尿素ダイアリザンスが170以上であるこ
とを特徴とした血液透析器を提供するものであ
る。
以下本発明についてさらに詳細に説明する。本
発明における異形中空糸は、その外周部において
長手方向に延長された複数条のフインを有したも
のであつて、各フインの平均高さが同一ではな
く、あるいは各フインの隣接2条間距離が同一で
ないこと、又は該高さと隣接2条間距離の両方が
共に不同一であることを特徴とするものである。
即ち複数条のフインのうちの最も高いフインの
平均高さが最も低いフインの平均高さの1.5〜10
倍の異形中空糸が好ましく、特にその倍率が2〜
5である場合には、その充填状態において中空糸
間の密着が生じにくく、またフインどうしあるい
はフインと中空糸壁での密閉空間が発生しにくく
中空糸の外側における流体がより自由に流動しや
すくなる。
また複数条のフインについての隣接2条間距離
の最大値が最小値の1.5〜10倍、更には2〜5倍
であることが好ましい。この範囲に入る場合に
は、該中空糸を充填した流体分離器において、中
空糸間の密着や、フインどうしあるいはフインと
中空糸壁による密閉空間が発生しにくく、中空糸
壁外における流体の流動性が非常に良好となる。
尚この条間周上距離とは、隣接した2条のフイン
の中心部間の中空糸外壁の周に沿つた最短距離を
言う。
本発明の中空糸のフイン数は、2〜10条が好ま
しく、特に3〜8条が好ましい。尚フインが3条
以上の場合には、上記のフイン高さの高いフイン
が1条又は2条の如く比較的少ない方がそのフイ
ンによる密閉空間が出来にくく好ましい。フイン
が11条以上の場合には、フイン根元における膜性
能低下が相対的に大きくなることから実用的でな
い。
また、本発明の中空糸としては、フイン高さの
不同一に加えて隣接2条間距離の不同一を満たし
た場合が最も好ましいが、フイン高さのみを不同
にすることだけでも比較的容易にその効果が得ら
れる。
尚、かかる本発明の異形中空糸における中空糸
の外径、厚み、フインの形状、高さ、厚み、材質
等は特に限定されるものではない。実用的には、
該中空糸の外径として100〜400μ、更には200〜
300μが好ましく、フイン部のない部分の膜厚と
しては5〜50μ、更には5〜30μが好ましい。ま
た該フインの高さとしては5〜200μ、更には10
〜100μの範囲にあることが望ましく、フインの
根元の厚さとしては10〜50μが好ましく、さらに
フインの形状としては、フインの根元の厚さがフ
インの中間部における厚さと同程度かさらにはそ
れより薄いものが有効膜面積の減少が少なく好ま
しい。
本発明の対象となる中空糸膜の素材としては、
選択透過性中空糸膜に成形できるものであれば如
何なるものであつてもよく、その具体例としては
セルロース、セルロースエステル、ポリアミド、
ポリアクリロニトリル、ポリカーボネート、ポリ
メチルメタアクリレート、ポリオレフイン、ポリ
スルホン、ポリエーテルスルホン等及びこれらを
含む共重合体、他の物との混合物などが挙げられ
る。
本発明に係わるフインは異形中空糸を製造する
には、中空糸膜の紡糸原液(溶融物又は溶液)を
常法に従つて紡糸口金の二重円環状スリツトから
気体又は紡糸浴中に押出し、中空部には膜素材と
実質的に反応せず、またこれを溶かさない気体又
は液体をみたして、中空を保持させながら紡糸す
る方法が好ましい。例えばセルロースジアセテー
トにポリエチレングリコールなどの可塑剤を加
え、溶融して紡糸口金の二重円環状スリツトから
空気中に押出し、中心部に窒素ガスを注入してか
ら紡糸して中空糸となす。この中空糸から可塑剤
などを除去し、要すればアルカリで鹸化して血液
処理用の中空糸膜を製造する。その際、膜素材の
溶融物を押出す紡糸口金として本発明に係るフイ
ン付中空糸を得るには二重円環部の外周部に長さ
が異なり及び/又は隣接間距離が異なる複数の切
欠部を有した紡糸口金を用いるのが好ましい。
次に、本発明の血液透析器について説明する。
即ち該血液透析器は、前記した如き異形中空糸を
多数収納したことを特徴とするものである。尚場
合によつては他の中空糸、例えば通常の真円の断
面形状を有した選択透過性中空糸も含んで収納さ
れていてもよい。
かかる血液透析器では、これらの異形中空糸の
多数が束状に充填されている場合が一般的であ
り、その充填率は30〜80%が好ましい。特に本発
明の如き高さや隣接間隔の異なる複数のフインを
有した異形中空糸を収納した場合には、充填率が
40〜80%、特に50〜80%なる比較的高い充填率に
おいても、中空糸間の密着やフインどうしあるい
はフインと中空糸による密閉空間が生じにくいと
いう非常に優れた利点が得られる。即ち本発明の
血液透析器においては、充填された中空糸のフイ
ンが不均一であるために、局所的な密集が発生し
にくく、中空糸外側での流体の流動状態が均一に
保持されやすい特徴がある。尚、充填率が60〜80
%と高い場合には、中空糸の収納操作がやや難し
いこともあるが、その際には中空糸の収集体を全
体で又は複数のブロツクに分けて他の糸あるいは
テープ状物等をらせん状に巻きつけたり、ネツト
状物によつてくるむなどしてまとめて収納するこ
とが好ましい。そこで用いられる糸、テープ状
物、ネツト等には、水溶性ポリマーからなるもの
や、水中で膨潤するものを用いて水により溶解あ
るいは膨潤させることにより、流体分離時におい
て分離器内全体に該中空糸が均一に分散させるよ
うにすることが望ましい。
また本発明の血液透析器の形式は、特に限定さ
れるものではなく、例えば血液透析器に代表され
る様に、中空糸集束体を収納した円筒状容器、中
空糸両端部を接着開口した管板、血液の分配部と
収集部及び透析液の導入口と導出口からなるもの
が挙げられる。
尚、本発明における尿素ダイアリザンスは、中
空糸の内表面の面積が実質的に1m2である透析器
を使用し、37℃において、中空糸の中空部内に平
均速度1.2cm/secで尿素水溶液を流し、中空糸外
に平均速度1.8cm/secで水を流した場合のものを
いう。
本発明の血液透析器の如き流体分離器は、上記
の如き血液透析や血液過による人工腎臓、人工
肝臓、血漿分離や血漿成分分離、人工肺、腹水処
理等の体液処理器や、その他の限外過器、逆浸
透器さらにはガス分離器等に用いることが可能で
あり、特に透析器などの様に中空糸外の流体の良
好な流動特性が要求される場合に有効である。
以下に実施例をあげてさらに詳述するが、これ
らの実施例により本発明が何ら限定されるもので
はない。
実施例1,2、比較例1,2
セルロースジアセテート100部に対しポリエチ
レングリコール(分子量300)を50部加えたもの
を混合し、その混合物を200℃で溶融し、フイン
付中空糸用の二重円環状スリツトに長さ及び間隔
が表1に示す中空糸が得られる切欠き及び連結部
を有する口金を用いて紡出した。次いで鹸化反応
によりセルロースとなし捲取り后中空糸を中空糸
内表面基準の有効面積が約1m2の血液透析器に組
立てた。第1表には得られた中空糸の形状及び血
液透析器の特性を示す。
但し、尿素ダイアリザンスは37℃で中空糸内の
平均血液側速度が約1.2cm/secの尿素水溶液、透
析液側の平均流速が約1.8cm/secの水を用いて測
定した。又、フイン付糸の場合の有効膜面積はフ
イン部根元部分は透析に無効として算出した。
更に管板リーク率とは、中空糸束の両端部をウ
レタン系接着剤で相互に接着するに際し、中空糸
間の隙間に十分接着剤が浸入せず、透析液側と血
液側との間にできる連通個所の発生による不良品
率のことをいう。
[Field of Application] The present invention provides a hemodialyzer housing a permselective finned irregularly shaped hollow fiber. More specifically, the present invention relates to a hemodialyzer containing irregularly shaped hollow fibers with fins, characterized in that the height of the fins and the distance between the fins are not substantially the same. [Prior Art] Hemodialyzers have conventionally been used to purify the blood of renal failure patients and remove excess water. In this system, a large number of dialysis membranes, such as hollow fiber membranes, are housed in a container, and the patient's blood is poured into the hollow interior of the membrane.
Flowing dialysate externally, that is, between the hollow fiber membranes, and removing waste products from the blood by dialysis through the hollow fiber membranes;
It adjusts the electrolyte concentration and creates a pressure difference between the inside and outside of the hollow fiber membrane, and removes excess water from the blood through ultraviolet filtration. Furthermore, a method (blood filtration) in which a large amount of water and waste products are removed only by ultrafiltration and the excess water removed is replenished together with necessary components such as electrolytes (blood filtration) is also applied depending on the actual situation. Furthermore, clinical trials have also been made to use hollow fiber membranes to separate plasma from blood or remove specific harmful components from the plasma to treat autoimmune diseases and the like. Various efforts have been made to improve the dialysis performance, which is the most important performance of a dialyzer. However, it cannot be said that the problem of uneven flow of dialysate due to close contact between hollow fibers in a dialyzer has been sufficiently solved. Examples of solutions so far include increasing the amount of hollow fibers stored in the dialyzer container (filling rate) to a certain extent, or creating dialysate flow resistance by crossing hollow fibers, making the flow more uniform. It was decided to measure the Furthermore, by crimping the hollow fibers or wrapping a cover yarn around the hollow fibers, it is possible to prevent the hollow fibers from coming into close contact with each other, and to evenly distribute the substances in the container due to the flow of dialysate. Movement efficiency has been improved. However, these solutions are still not sufficient, and further improvements are desired. [Object of the Invention] The purpose of the present invention is to solve these problems and provide a hollow fiber membrane or hollow fiber bundle with excellent separation efficiency in fluid separation such as blood treatment, and a fluid separator filled with the hollow fiber membrane or hollow fiber bundle. It is said that In particular, the object is to obtain a hollow fiber or a hollow fiber bundle in which the filling state in a fluid separator is likely to be uniform, and even when the packing density is increased, it is extremely difficult for the hollow fibers to adhere to each other. [Structure of the Invention] In order to achieve the above object, the present inventors conducted intensive research and found that irregularly shaped hollow fibers having multiple fins are preferable, and in particular, the height of the fins and the circumferential distance between the fins are The present invention has been achieved by discovering that it is effective to make them different. That is, the present invention provides a hemodialyzer containing a permselective hollow fiber, which has 2 to 10 fins extending in the longitudinal direction on the outer periphery, and the average height of each of the fins is substantially different. and the average height of the tallest fin is 1.5 to 10 of the average height of the lowest fin.
permselective hollow fibers are housed in which the distance between two adjacent fibers is substantially different and the maximum value of the distance between the two adjacent fibers is 1.5 to 10 times the minimum value. The present invention provides a hemodialyzer characterized by a dialysance of 170 or more. The present invention will be explained in more detail below. The irregularly shaped hollow fiber in the present invention has a plurality of fins extending in the longitudinal direction on its outer periphery, and the average height of each fin is not the same, or the distance between two adjacent fins is not the same. are not the same, or both the height and the distance between two adjacent strips are not the same. In other words, the average height of the highest fin among the multiple fins is 1.5 to 10 times the average height of the lowest fin.
It is preferable to use irregularly shaped hollow fibers with a magnification of 2 to 2 times.
5, it is difficult for the hollow fibers to come into close contact with each other in the filled state, and it is also difficult to form a sealed space between the fins or between the fins and the hollow fiber wall, making it easier for the fluid outside the hollow fibers to flow more freely. Become. Further, it is preferable that the maximum value of the distance between two adjacent fins of a plurality of fins is 1.5 to 10 times, more preferably 2 to 5 times, the minimum value. If it falls within this range, in a fluid separator filled with the hollow fibers, it is difficult for the hollow fibers to come into close contact with each other, or to create a sealed space between the fins or between the fins and the hollow fiber wall, and the fluid flow outside the hollow fiber wall. The properties are very good.
Incidentally, the term "inter-strip circumferential distance" refers to the shortest distance along the circumference of the hollow fiber outer wall between the centers of two adjacent fins. The number of fins in the hollow fiber of the present invention is preferably 2 to 10, particularly preferably 3 to 8. In the case where there are three or more fins, it is preferable that the number of high fins is relatively small, such as one or two fins, because the fins are less likely to create a closed space. If the number of fins is 11 or more, it is not practical because the membrane performance deteriorates relatively at the base of the fins. Furthermore, it is most preferable that the hollow fibers of the present invention satisfy not only the unevenness of the fin heights but also the unevenness of the distance between two adjacent fibers, but it is relatively easy to make only the fin heights different. The effect can be obtained. Note that the outer diameter, thickness, shape, height, thickness, material, etc. of the hollow fibers of the irregularly shaped hollow fibers of the present invention are not particularly limited. Practically,
The outer diameter of the hollow fiber is 100 to 400μ, more preferably 200 to 400μ.
It is preferably 300μ, and the thickness of the portion without fins is preferably 5 to 50μ, more preferably 5 to 30μ. In addition, the height of the fins is 5 to 200 μm, and even 10 μm.
It is desirable that the thickness is in the range of ~100μ, the thickness of the base of the fin is preferably 10~50μ, and the shape of the fin is such that the thickness of the base of the fin is about the same as the thickness of the middle part of the fin, or even better. Thinner layers are preferable because the effective membrane area is less reduced. Materials for hollow fiber membranes that are the subject of the present invention include:
Any material may be used as long as it can be formed into a permselective hollow fiber membrane, and specific examples thereof include cellulose, cellulose ester, polyamide,
Examples include polyacrylonitrile, polycarbonate, polymethyl methacrylate, polyolefin, polysulfone, polyethersulfone, copolymers containing these, and mixtures with other substances. In order to produce the irregularly shaped hollow fibers of the fins according to the present invention, the spinning dope (melt or solution) of the hollow fiber membrane is extruded through the double annular slit of the spinneret into a gas or a spinning bath according to a conventional method. A preferred method is to fill the hollow part with a gas or liquid that does not substantially react with or dissolve the membrane material, thereby maintaining the hollow part while spinning. For example, a plasticizer such as polyethylene glycol is added to cellulose diacetate, it is melted and extruded into the air through a double annular slit in a spinneret, nitrogen gas is injected into the center, and the material is spun into hollow fibers. Plasticizers and the like are removed from the hollow fibers, and if necessary, they are saponified with alkali to produce hollow fiber membranes for blood treatment. At that time, in order to obtain the finned hollow fiber according to the present invention as a spinneret for extruding the melt of the membrane material, a plurality of notches with different lengths and/or with different distances between adjacent ones are formed on the outer periphery of the double ring part. It is preferred to use a spinneret with a Next, the hemodialyzer of the present invention will be explained.
That is, the hemodialyzer is characterized by housing a large number of irregularly shaped hollow fibers as described above. In some cases, other hollow fibers, such as permselective hollow fibers having a normal perfect circular cross-sectional shape, may also be housed. In such a hemodialyzer, a large number of these irregularly shaped hollow fibers are generally packed in a bundle, and the filling rate is preferably 30 to 80%. In particular, when housing irregularly shaped hollow fibers having a plurality of fins with different heights and adjacent spacings as in the present invention, the filling rate is low.
Even at a relatively high filling rate of 40 to 80%, especially 50 to 80%, a very excellent advantage can be obtained in that close contact between hollow fibers and closed spaces between fins or between fins and hollow fibers are unlikely to occur. That is, in the hemodialyzer of the present invention, since the fins of the filled hollow fibers are nonuniform, local crowding is less likely to occur, and the fluid flow state on the outside of the hollow fibers is likely to be maintained uniformly. There is. In addition, the filling rate is 60 to 80
%, it may be a little difficult to store the hollow fibers, but in that case, you can collect the hollow fibers as a whole or divide them into multiple blocks and add other threads or tape-like materials in a spiral shape. It is preferable to store them all together by wrapping them in a net or wrapping them in a net-like material. Threads, tape-like materials, nets, etc. used in this process are made of water-soluble polymers or materials that swell in water, and by dissolving or swelling them in water, the entire interior of the separator is filled with hollow material during fluid separation. It is desirable to ensure that the threads are evenly distributed. Further, the type of the hemodialyzer of the present invention is not particularly limited; for example, as typified by a hemodialyzer, a cylindrical container housing a hollow fiber bundle, a tube with both ends of the hollow fibers adhesively opened, These include plates, blood distribution and collection sections, and dialysate inlets and outlets. In addition, the urea dialysance in the present invention uses a dialyzer in which the inner surface area of the hollow fiber is substantially 1 m2 , and a urea aqueous solution is poured into the hollow part of the hollow fiber at an average speed of 1.2 cm/sec at 37°C. This refers to the situation when water is flowed outside the hollow fiber at an average speed of 1.8 cm/sec. The fluid separator such as the hemodialyzer of the present invention is applicable to the above-mentioned hemodialysis, artificial kidney, artificial liver, plasma separation, plasma component separation, artificial lung, ascites treatment, etc., and other body fluid treatment devices. It can be used in filters, reverse osmosis devices, gas separators, etc., and is particularly effective in cases where good flow characteristics of the fluid outside the hollow fibers are required, such as in dialyzers. The present invention will be described in more detail below with reference to Examples, but the present invention is not limited to these Examples in any way. Examples 1 and 2, Comparative Examples 1 and 2 100 parts of cellulose diacetate and 50 parts of polyethylene glycol (molecular weight 300) were mixed together, the mixture was melted at 200°C, and a double layer for finned hollow fibers was prepared. Spinning was carried out using a spinneret having a heavy annular slit, a notch and a connecting portion to obtain hollow fibers having the lengths and intervals shown in Table 1. Next, cellulose was formed by a saponification reaction, and the hollow fiber was assembled into a hemodialyzer having an effective area of about 1 m 2 based on the inner surface of the hollow fiber. Table 1 shows the shape of the hollow fibers obtained and the characteristics of the hemodialyzer. However, the urea dialysance was measured at 37° C. using an aqueous urea solution with an average flow rate of about 1.2 cm/sec on the blood side in the hollow fiber and water with an average flow rate of about 1.8 cm/sec on the dialysate side. In addition, the effective membrane area in the case of a thread with fins was calculated assuming that the root portion of the fins is ineffective for dialysis. Furthermore, the tube sheet leakage rate refers to the fact that when the ends of a hollow fiber bundle are bonded together with a urethane adhesive, the adhesive does not sufficiently penetrate into the gaps between the hollow fibers, causing leakage between the dialysate side and the blood side. This refers to the rate of defective products due to the occurrence of communication points.
本発明の異形中空糸充填した血液透析器は、充
填状態が全体的に均一となりやすい利点がある。
即ち、充填状態において中空糸どうしの密着が非
常に少ないばかりでなく、フインどうしあるいは
フインと中空糸による密閉空間が形成されにくい
ために中空糸外側での流体の流動状態が極めて均
一になりやすい特徴がある。それ故、中空糸外側
での流体の流速及び濃度が局部的に不均一になる
ことが極めて少なく、流体の分離効率に優れた効
果が得られる。
The hemodialyzer filled with irregularly shaped hollow fibers of the present invention has the advantage that the filling state tends to be uniform throughout.
In other words, not only is there very little close contact between the hollow fibers in the packed state, but also it is difficult to form a sealed space between the fins or between the fins and the hollow fibers, so the fluid flow state outside the hollow fibers tends to be extremely uniform. There is. Therefore, the flow rate and concentration of the fluid outside the hollow fibers are extremely unlikely to become locally non-uniform, and excellent fluid separation efficiency can be obtained.
Claims (1)
いて、外周部に長手方向に延長された2〜10条の
フインを有し、該フイン各条の平均高さが実質上
不同一でありかつ最も高いフインの平均高さが最
も低いフインの平均高さの1.5〜10倍であり、さ
らには隣接2条間距離が実質上不同一でありかつ
該隣接2条間距離の最大値が最小値の1.5〜10倍
である選択透過性中空糸が収納されており、中空
糸の内表面積1m2換算の尿素ダイアリザンスが
170以上であることを特徴とする血液透析器。1. A hemodialyzer containing permselective hollow fibers, which has 2 to 10 fins extending in the longitudinal direction on the outer periphery, and the average height of each fin is substantially the same and the most The average height of the tallest fins is 1.5 to 10 times the average height of the lowest fin, and furthermore, the distances between two adjacent fins are substantially different, and the maximum value of the distance between the two adjacent fins is greater than the minimum value. Contains hollow fibers with selective permselectivity that is 1.5 to 10 times larger, and the urea dialysance of 1 m2 of the inner surface area of the hollow fibers is
170 or more.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP10277385A JPS61266609A (en) | 1985-05-16 | 1985-05-16 | Modified cross-section hollow fiber, modified cross-section hollow fiber bundle and fluid separator |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP10277385A JPS61266609A (en) | 1985-05-16 | 1985-05-16 | Modified cross-section hollow fiber, modified cross-section hollow fiber bundle and fluid separator |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS61266609A JPS61266609A (en) | 1986-11-26 |
JPH0244226B2 true JPH0244226B2 (en) | 1990-10-03 |
Family
ID=14336474
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP10277385A Granted JPS61266609A (en) | 1985-05-16 | 1985-05-16 | Modified cross-section hollow fiber, modified cross-section hollow fiber bundle and fluid separator |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS61266609A (en) |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS56308A (en) * | 1979-03-17 | 1981-01-06 | Akzo Nv | Hollow fiber made of synthetic polymer and heat transfer device using same |
JPS56148908A (en) * | 1980-08-25 | 1981-11-18 | Nippon Zeon Co Ltd | Hollow fiber |
JPS5850761A (en) * | 1981-09-21 | 1983-03-25 | Fujitsu Ltd | Semiconductor device |
-
1985
- 1985-05-16 JP JP10277385A patent/JPS61266609A/en active Granted
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS56308A (en) * | 1979-03-17 | 1981-01-06 | Akzo Nv | Hollow fiber made of synthetic polymer and heat transfer device using same |
JPS56148908A (en) * | 1980-08-25 | 1981-11-18 | Nippon Zeon Co Ltd | Hollow fiber |
JPS5850761A (en) * | 1981-09-21 | 1983-03-25 | Fujitsu Ltd | Semiconductor device |
Also Published As
Publication number | Publication date |
---|---|
JPS61266609A (en) | 1986-11-26 |
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