JPH0563214B2 - - Google Patents
Info
- Publication number
- JPH0563214B2 JPH0563214B2 JP6421986A JP6421986A JPH0563214B2 JP H0563214 B2 JPH0563214 B2 JP H0563214B2 JP 6421986 A JP6421986 A JP 6421986A JP 6421986 A JP6421986 A JP 6421986A JP H0563214 B2 JPH0563214 B2 JP H0563214B2
- Authority
- JP
- Japan
- Prior art keywords
- blood
- polysulfone
- separation membrane
- solvent
- weight
- 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
- 239000012528 membrane Substances 0.000 claims description 24
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 15
- 238000000926 separation method Methods 0.000 claims description 13
- 238000009987 spinning Methods 0.000 claims description 13
- 239000004695 Polyether sulfone Substances 0.000 claims description 12
- 229920006393 polyether sulfone Polymers 0.000 claims description 12
- 229920002492 poly(sulfone) Polymers 0.000 claims description 11
- 239000012510 hollow fiber Substances 0.000 claims description 8
- 238000004519 manufacturing process Methods 0.000 claims description 6
- 239000002904 solvent Substances 0.000 claims description 6
- 238000000034 method Methods 0.000 claims description 5
- 239000011347 resin Substances 0.000 claims description 5
- 229920005989 resin Polymers 0.000 claims description 5
- 239000011550 stock solution Substances 0.000 claims description 5
- 230000015271 coagulation Effects 0.000 claims description 4
- 238000005345 coagulation Methods 0.000 claims description 4
- 239000000203 mixture Substances 0.000 claims description 4
- 230000001112 coagulating effect Effects 0.000 claims description 3
- 239000007788 liquid Substances 0.000 claims description 3
- 239000002184 metal Substances 0.000 claims description 3
- 150000003839 salts Chemical class 0.000 claims description 3
- 239000000243 solution Substances 0.000 claims description 2
- 238000002166 wet spinning Methods 0.000 claims description 2
- 229920000642 polymer Polymers 0.000 claims 1
- 239000008280 blood Substances 0.000 description 17
- 210000004369 blood Anatomy 0.000 description 17
- 238000001631 haemodialysis Methods 0.000 description 11
- 230000000322 hemodialysis Effects 0.000 description 11
- ZMXDDKWLCZADIW-UHFFFAOYSA-N N,N-Dimethylformamide Chemical compound CN(C)C=O ZMXDDKWLCZADIW-UHFFFAOYSA-N 0.000 description 9
- 230000036772 blood pressure Effects 0.000 description 8
- JHJLBTNAGRQEKS-UHFFFAOYSA-M sodium bromide Chemical compound [Na+].[Br-] JHJLBTNAGRQEKS-UHFFFAOYSA-M 0.000 description 6
- 241000282472 Canis lupus familiaris Species 0.000 description 5
- 230000017531 blood circulation Effects 0.000 description 4
- 230000007774 longterm Effects 0.000 description 4
- 208000009304 Acute Kidney Injury Diseases 0.000 description 3
- 208000033626 Renal failure acute Diseases 0.000 description 3
- 208000007536 Thrombosis Diseases 0.000 description 3
- 201000011040 acute kidney failure Diseases 0.000 description 3
- 208000012998 acute renal failure Diseases 0.000 description 3
- 238000009534 blood test Methods 0.000 description 3
- 208000020832 chronic kidney disease Diseases 0.000 description 3
- 208000022831 chronic renal failure syndrome Diseases 0.000 description 3
- 230000000052 comparative effect Effects 0.000 description 3
- 238000012360 testing method Methods 0.000 description 3
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 2
- 206010020565 Hyperaemia Diseases 0.000 description 2
- SECXISVLQFMRJM-UHFFFAOYSA-N N-Methylpyrrolidone Chemical compound CN1CCCC1=O SECXISVLQFMRJM-UHFFFAOYSA-N 0.000 description 2
- 230000001684 chronic effect Effects 0.000 description 2
- 230000003247 decreasing effect Effects 0.000 description 2
- KWGKDLIKAYFUFQ-UHFFFAOYSA-M lithium chloride Chemical compound [Li+].[Cl-] KWGKDLIKAYFUFQ-UHFFFAOYSA-M 0.000 description 2
- 238000000746 purification Methods 0.000 description 2
- 238000004804 winding Methods 0.000 description 2
- HTTJABKRGRZYRN-UHFFFAOYSA-N Heparin Chemical compound OC1C(NC(=O)C)C(O)OC(COS(O)(=O)=O)C1OC1C(OS(O)(=O)=O)C(O)C(OC2C(C(OS(O)(=O)=O)C(OC3C(C(O)C(O)C(O3)C(O)=O)OS(O)(=O)=O)C(CO)O2)NS(O)(=O)=O)C(C(O)=O)O1 HTTJABKRGRZYRN-UHFFFAOYSA-N 0.000 description 1
- 208000001647 Renal Insufficiency Diseases 0.000 description 1
- 210000001367 artery Anatomy 0.000 description 1
- 230000004087 circulation Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000000502 dialysis Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 229960002897 heparin Drugs 0.000 description 1
- 229920000669 heparin Polymers 0.000 description 1
- 238000001802 infusion Methods 0.000 description 1
- 201000006370 kidney failure Diseases 0.000 description 1
- SFMJNHNUOVADRW-UHFFFAOYSA-N n-[5-[9-[4-(methanesulfonamido)phenyl]-2-oxobenzo[h][1,6]naphthyridin-1-yl]-2-methylphenyl]prop-2-enamide Chemical compound C1=C(NC(=O)C=C)C(C)=CC=C1N1C(=O)C=CC2=C1C1=CC(C=3C=CC(NS(C)(=O)=O)=CC=3)=CC=C1N=C2 SFMJNHNUOVADRW-UHFFFAOYSA-N 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 229920002635 polyurethane Polymers 0.000 description 1
- 239000004814 polyurethane Substances 0.000 description 1
- HNJBEVLQSNELDL-UHFFFAOYSA-N pyrrolidin-2-one Chemical compound O=C1CCCN1 HNJBEVLQSNELDL-UHFFFAOYSA-N 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 208000024891 symptom Diseases 0.000 description 1
- 210000003462 vein Anatomy 0.000 description 1
- 238000005303 weighing Methods 0.000 description 1
Description
〔産業上の利用分野〕
本発明は、血液浄化用の中空糸型人工臓器に関
するものである。更に詳しくは、慢性あるいは急
性の腎不全患者の治療を目的とした、すぐれた
過特性と安定性を有する血液透析器、血液過
器、血圧駆動型血液過器等に関するものであ
る。
〔従来技術〕
現在、慢性腎不全患者の治療としては、血液ポ
ンプを使用した間歇的な血液透析や血液過が一
般的に行なわれている。一方、手術後の合併症等
で生じる急性腎不全患者の治療に対しては、迅速
な水分及び溶質の大量の除去が必要となつてくる
ため、従来の間歇的な治療法では対応できないこ
とが多い。
このような場合には連続的血液透析または血液
過が効果的であるが、1日〜2週間程度連続的
に使用するため、これに使用される膜には厳しい
血液適合性が要求され、また従来より用いられて
いる血液透析器や血液過器では、構造あるいは
膜の特性から使用が不可能であつた。すなわち、
従来の透析器や過器においては、その構造のみ
ならず使用される膜そのものについても4〜5時
間という短時間の血液浄化を目的としたものであ
り、従つて過効率を中心に膜の設計がなされて
いるため長時間血液と接触していると膜表面に血
栓が生じ易いという欠点があつた。
更に、長時間の連続使用では患者の心臓に大き
な負担がかかる血液ポンプの使用は好ましくな
く、患者自身の血圧のみによつて体外循環を行う
治療法、すなわち血圧駆動型血液過も検討され
ており、この場合患者の血圧に応じた血流変動、
特に血流低下により膜内に血栓が生じ易いことか
ら、従来の血液浄化器の使用は不可能であつた。
〔発明の目的〕
本発明者らは、以上のような長時間の連続的血
液透析または血液過、更には血液ポンプを使用
しない血圧駆動による血液過を安定して行うこ
とができる中空糸型血液浄化器を得るべく鋭意研
究を進めた結果、特定の樹脂及び樹脂原液組成を
用いることにより、すぐれた性能を有する分離膜
が得られることを見出し、更にこの知見に基づき
種々の検討を行い本発明に至つたものである。
〔発明の構成〕
即ち本発明は、2重管構造の中空繊維製造用ノ
ズルを用い、外側の環状口から紡糸原液を、芯部
から凝固液を凝固浴中へ吐出し凝固せしめる湿式
紡糸法において、紡糸原液がポリエーテルスルホ
ン、ポリスルホン及び溶剤、及び/又は金属塩、
及び/又は非溶剤からなり、ポリエーテルスルホ
ンに対するポリスルホンの重量比が1/9以下で
あることを特徴とする中空繊維状分離膜の製造方
法である。
中空繊維状分離膜の寸法は通常、膜内径が200
〜300μm、膜厚が10〜100μmの範囲で作成が可能
であるが、膜の強度やハウジングに挿入する際の
充填率を向上させるために膜内径は210〜240μm、
膜厚は30〜50μmの範囲が望ましい。
本発明で使用するポリエーテルスルホン及びポ
リスルホンは、それぞれ
[Industrial Application Field] The present invention relates to a hollow fiber type artificial organ for blood purification. More specifically, the present invention relates to a hemodialyzer, a hemodialysis device, a blood pressure-driven hemodialysis device, etc., which have excellent performance characteristics and stability, and are intended for the treatment of patients with chronic or acute renal failure. [Prior Art] Currently, intermittent hemodialysis or hemodialysis using a blood pump is generally performed as a treatment for patients with chronic renal failure. On the other hand, for the treatment of patients with acute renal failure caused by complications after surgery, etc., it is necessary to rapidly remove large amounts of water and solutes, which may not be possible with conventional intermittent treatment methods. many. Continuous hemodialysis or hemodialysis is effective in such cases, but since it is used continuously for about one day to two weeks, the membrane used for this requires strict blood compatibility, and It has been impossible to use conventional hemodialyzers and blood filters due to their structure or membrane characteristics. That is,
In conventional dialyzers and dialysis machines, not only their structure but also the membranes used are intended for blood purification in a short time of 4 to 5 hours, and therefore the membrane design focuses on overefficiency. Because of this, there was a drawback that blood clots were likely to form on the membrane surface if it was in contact with blood for a long time. Furthermore, it is not desirable to use a blood pump, which puts a heavy burden on the patient's heart when used continuously for a long period of time, and a treatment method that performs extracorporeal circulation using only the patient's own blood pressure, that is, a blood pressure-driven blood pump, is also being considered. , in this case blood flow fluctuations depending on the patient's blood pressure,
In particular, it has been impossible to use conventional blood purifiers because blood clots are likely to form within the membrane due to decreased blood flow. [Object of the Invention] The present inventors have developed a hollow fiber type blood system that can stably perform long-term continuous hemodialysis or hemodialysis as described above, as well as blood pressure-driven hemodialysis without using a blood pump. As a result of intensive research to obtain a purifier, it was discovered that a separation membrane with excellent performance could be obtained by using a specific resin and resin stock solution composition.Based on this knowledge, various studies were conducted and the present invention was developed. This is what led to this. [Structure of the Invention] That is, the present invention relates to a wet spinning method in which a hollow fiber manufacturing nozzle with a double tube structure is used, and a spinning dope is discharged from an outer annular opening and a coagulating liquid is discharged from a core into a coagulating bath and coagulated. , the spinning stock solution is polyether sulfone, polysulfone and solvent, and/or metal salt,
and/or a non-solvent, and the weight ratio of polysulfone to polyethersulfone is 1/9 or less. Hollow fibrous separation membranes typically have an inner diameter of 200 mm.
~300μm, and the film thickness can be made in the range of 10 to 100μm, but in order to improve the strength of the membrane and the filling rate when inserting it into the housing, the inner diameter of the membrane is 210 to 240μm.
The film thickness is preferably in the range of 30 to 50 μm. The polyether sulfone and polysulfone used in the present invention are each
以上のように、ポリエーテルスルホン及びポリ
スルホンを含む特定な樹脂原液組成より得られた
中空繊維状分離膜は、血液と接触する膜の表面状
態と血液過速度、すなわち除水能とのバランス
が良好に保たれ、この結果血液透析または血液
過を極めて効率よくかつ安定に行い得るものであ
る。従つて、慢性あるいは急性腎不全患者の治療
において、従来困難とされていた長時間の連続的
血液透析または血液過、更には血液ポンプを使
用しない血圧駆動による血液過に対しても効果
的である。
実施例 1
ポリエーテルスルホン14重量%、ポリスルホン
1重量%、NaBr5重量%及びジメチルホルムア
ミド80重量%を溶解混合した。この溶液を紡糸原
液として、中空繊維製造用ノズルの外側の環状口
から紡糸原液を、また芯部からは水を吐出し、水
からなる凝固浴中へ導いて凝固せしめ、40m/分
の速度で巻取りを行つた。ここで紡糸温度、すな
わち紡糸原液及び内部凝固液の温度は40℃であつ
た。巻取つた中空繊維状分離膜は60℃の温水中に
7時間、更に流水中に10時間の浸漬を行つた。得
られた中空繊維状分離膜は内径220μm、膜厚
30μmであつた。
この中空繊維状分離膜3000本をポリカーボネー
ト製の円筒カラムに挿入し、両端をポリウレタン
により接着固定した後、両端部を切断し中空繊維
状分離膜の開口部を得た。中空繊維状分離膜の有
効長は10cmであつた。
次いで、体重約16Kgの尿管結紮した雑種犬の頸
部動、静脈に外シヤントを設置し、血圧駆動によ
る血液過を行つた。その際ヘパリンを400IU/
時間を持続注入を行つた。その結果、700〜1500
ml/時間の除水が安定して得られ、100時間以上
の連続過が可能であり、この間犬の状態も良好
であつた。
以下の実施例及び比較例においては、特に断ら
ない限り本実施例と同様にして紡糸、評価試験等
を行うものとする。
実施例 2
ポリエーテルスルホン15重量%、ポリスルホン
1.5重量%、LiCl4重量%及びN−メチル−2−ピ
ロリドン79.5重量%よりなる紡糸原液を用いた。
巻取り速度は50m/分であつた。得られた膜は内
径230μm、膜厚35μmであつた。犬による血液
過試験では、900〜1400ml/時間の除水で、100時
間以上の安定な連続過が可能であつた。
実施例 3
ポリエーテルスルホン15重量%、ポリスルホン
1重量%、エタノール3重量%及びN−メチル−
2−ピロリドン81重量%の組成よりなる紡糸原液
を用いた。犬による血液過試験では除水能、長
時間安定性ともに良好であつた。
比較例 1
ポリエーテルスルホン15重量%、NaBr5重量
%及びジメチルホルムアミド80重量%よりなる紡
糸原液を用いた。犬による血液過試験では、長
時間の安定性では良好であつたが、除水能が600
ml/分以下と低い値であつた。この値は、腎不全
患者の症状に対しては除水能が不十分である。
比較例 2
ポリエーテルスルホン13重量%、ポリスルホン
2重量%、NaBr5重量%及びジメチルホルムア
ミド80重量%よりなる紡糸原液を用いた。血液
過試験においては、試験開始後約5時間は1000〜
1300ml/時間の高い除水能を示したが、その後急
激に低下し、50時間後100ml/時以下になつたた
め実験を中止した。使用した中空繊維状分離膜の
内部に血栓が認められ、これが除水量低下の原因
であつた。
As described above, the hollow fibrous separation membrane obtained from a specific resin stock solution composition containing polyethersulfone and polysulfone has a good balance between the surface condition of the membrane in contact with blood and blood overvelocity, that is, water removal ability. As a result, hemodialysis or blood filtration can be performed extremely efficiently and stably. Therefore, in the treatment of patients with chronic or acute renal failure, it is effective against long-term continuous hemodialysis or blood hyperemia, which was previously considered difficult, as well as blood hyperemia caused by blood pressure drive without the use of a blood pump. . Example 1 14% by weight of polyethersulfone, 1% by weight of polysulfone, 5% by weight of NaBr and 80% by weight of dimethylformamide were dissolved and mixed. Using this solution as a spinning dope, the spinning dope is discharged from the outer annular opening of the hollow fiber manufacturing nozzle, and water is discharged from the core, which is introduced into a coagulation bath consisting of water and coagulated at a speed of 40 m/min. I did the winding. Here, the spinning temperature, that is, the temperature of the spinning dope and the internal coagulation liquid, was 40°C. The rolled hollow fiber separation membrane was immersed in warm water at 60°C for 7 hours and then in running water for 10 hours. The obtained hollow fibrous separation membrane has an inner diameter of 220 μm and a membrane thickness.
It was 30μm. 3,000 of these hollow fibrous separation membranes were inserted into a cylindrical column made of polycarbonate, both ends of which were adhesively fixed with polyurethane, and then both ends were cut to obtain openings in the hollow fibrous separation membranes. The effective length of the hollow fibrous separation membrane was 10 cm. Next, an external shunt was placed in the cervical artery and vein of a mongrel dog weighing approximately 16 kg with ureteral ligation, and blood pressure-driven blood flow was performed. At that time, administer heparin at 400IU/
Continuous infusion was performed for several hours. As a result, 700-1500
A stable water removal rate of ml/hour was obtained, and continuous treatment for over 100 hours was possible, and the dog remained in good condition during this period. In the following Examples and Comparative Examples, unless otherwise specified, spinning, evaluation tests, etc. will be conducted in the same manner as in this Example. Example 2 Polyethersulfone 15% by weight, polysulfone
A spinning dope consisting of 1.5% by weight, 4% by weight of LiCl and 79.5% by weight of N-methyl-2-pyrrolidone was used.
The winding speed was 50 m/min. The obtained membrane had an inner diameter of 230 μm and a thickness of 35 μm. In a blood flow test using dogs, stable continuous flow for over 100 hours was possible with water removal of 900 to 1400 ml/hour. Example 3 15% by weight polyethersulfone, 1% by weight polysulfone, 3% by weight ethanol and N-methyl-
A spinning dope having a composition of 81% by weight of 2-pyrrolidone was used. In blood tests using dogs, both water removal ability and long-term stability were good. Comparative Example 1 A spinning dope consisting of 15% by weight of polyether sulfone, 5% by weight of NaBr and 80% by weight of dimethylformamide was used. In a blood test using dogs, the long-term stability was good, but the water removal ability was 600%.
The value was low, less than ml/min. This value indicates insufficient water removal ability for the symptoms of patients with renal failure. Comparative Example 2 A spinning dope consisting of 13% by weight of polyethersulfone, 2% by weight of polysulfone, 5% by weight of NaBr and 80% by weight of dimethylformamide was used. In the blood test, the blood pressure is 1000~5 hours after the start of the test.
Although it showed a high water removal capacity of 1,300 ml/hour, it rapidly decreased after 50 hours and became less than 100 ml/hour, so the experiment was discontinued. Thrombus was observed inside the hollow fibrous separation membrane used, and this was the cause of the decrease in water removal.
Claims (1)
外側の環状口から紡糸原液を、芯部から凝固液を
凝固浴中へ吐出し凝固せしめる湿式紡糸法におい
て、紡糸原液がポリエーテルスルホン、ポリスル
ホン及び溶剤、及び/又は金属塩、及び/又は非
溶剤からなり、ポリエーテルスルホンに対するポ
リスルホンの重量比が1/9以下であることを特
徴とする中空繊維状分離膜の製造方法。 2 凝固液の組成が水、または水、金属塩及び/
又は該樹脂の溶剤、及び/又は該樹脂の非溶剤か
らなることを特徴とする、特許請求の範囲第1項
記載の中空繊維状分離膜の製造方法。 3 ポリエーテルスルホン及びポリスルホンが、
それぞれ 【式】及び のくり返し単位を有する重合体よりなることを特
徴とする、特許請求の範囲第1項記載の中空繊維
状分離膜の製造方法。[Claims] 1. Using a hollow fiber manufacturing nozzle with a double tube structure,
In the wet spinning method in which the spinning stock solution is discharged from the outer annular port and the coagulation solution is discharged from the core into a coagulation bath and coagulated, the spinning stock solution contains polyethersulfone, polysulfone, a solvent, and/or a metal salt, and/or a non-solvent. A method for producing a hollow fiber separation membrane, characterized in that the weight ratio of polysulfone to polyethersulfone is 1/9 or less. 2 The composition of the coagulating liquid is water, or water, metal salt and/or
The method for producing a hollow fibrous separation membrane according to claim 1, characterized in that the method comprises a solvent for the resin and/or a non-solvent for the resin. 3 Polyether sulfone and polysulfone are
[formula] and The method for producing a hollow fibrous separation membrane according to claim 1, characterized in that the hollow fiber separation membrane is made of a polymer having repeating units.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP6421986A JPS62221402A (en) | 1986-03-24 | 1986-03-24 | Production of hollow fibrous separation membrane |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP6421986A JPS62221402A (en) | 1986-03-24 | 1986-03-24 | Production of hollow fibrous separation membrane |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS62221402A JPS62221402A (en) | 1987-09-29 |
JPH0563214B2 true JPH0563214B2 (en) | 1993-09-10 |
Family
ID=13251767
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP6421986A Granted JPS62221402A (en) | 1986-03-24 | 1986-03-24 | Production of hollow fibrous separation membrane |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS62221402A (en) |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CA2192351A1 (en) | 1994-06-07 | 1995-12-14 | Akira Hajikano | Porous polysulfone membrane and process for producing the same |
CN1076630C (en) * | 1997-12-17 | 2001-12-26 | 四川联合大学 | Polyether sulphone hollow fibre film and its manufacturing method and use |
-
1986
- 1986-03-24 JP JP6421986A patent/JPS62221402A/en active Granted
Also Published As
Publication number | Publication date |
---|---|
JPS62221402A (en) | 1987-09-29 |
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