JPH0323182B2 - - Google Patents
Info
- Publication number
- JPH0323182B2 JPH0323182B2 JP56110817A JP11081781A JPH0323182B2 JP H0323182 B2 JPH0323182 B2 JP H0323182B2 JP 56110817 A JP56110817 A JP 56110817A JP 11081781 A JP11081781 A JP 11081781A JP H0323182 B2 JPH0323182 B2 JP H0323182B2
- Authority
- JP
- Japan
- Prior art keywords
- carrier
- adsorbent
- gel
- extracorporeal circulation
- hydroxyl group
- 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
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- 238000011038 discontinuous diafiltration by volume reduction Methods 0.000 claims description 4
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- DGVVWUTYPXICAM-UHFFFAOYSA-N β‐Mercaptoethanol Chemical compound OCCS DGVVWUTYPXICAM-UHFFFAOYSA-N 0.000 description 1
Description
本発明は、粒子状担体に被吸着物質と結合可能
なリガンドを保持させてなる体外循環治療用吸着
材に関する。さらに詳しくは、癌、免疫増殖性症
候群、慢性関節リウマチ、全身性エリテマトーデ
ス、アレルギー、臓器移殖時の拒絶反応等の生体
免疫機能に関係した疾患および現象、あるいは腎
炎等の腎臓病、肝炎等の肝臓病などにおいて、血
液、血漿等の体液中に発現し、疾患の原因あるい
は進行と密接な関係をもつていると考えられる悪
性物質を、体液中より吸着、除去する吸着材に関
する。
従来、体外循環治療には、主に肝臓病用に人工
肝臓として活性炭あるいは活性炭を親水性高分子
でコートしたものが用いられてきた。しかし、上
記のように幾多の疾患において、疾患の原因ある
いは進行と密接な関係にある種々の悪性物質が知
られるようになり、さらには該悪性物質を体液中
より選択的に除去する要請が高まつてきたが、活
性炭をベースとする吸着材は、その吸着選択性が
低く、本要請に答えられないのが現状である。
本発明者らは、この悪性物質の選択的吸着、除
去の要請に答えるため鋭意研究の結果、担体に被
吸着物質と生物学的または/および化学的な選択
的相互作用をなす特別な物質を化学結合により保
持させてなる種々の吸着材を見い出し、先に特許
出願した。(特開昭57−122875、特開昭57−
134164、特開昭57−156035)
さらに本発明者らは、該吸着材に用いる粒子状
担体、特に体外循環治療用粒子状担体について詳
細に研究した。
従来、本目的を対象として特別に設計された担
体は知られていない。したがつて、通常アフイニ
テイクロマトグラフイ用として公知の担体を転用
する他はなかつた。
公知の担体としては、アガロース系担体、デキ
ストラン系担体、セルロース系担体等の天然高分
子系担体が知られている(たとえば商品名セフア
ローズ、フアルマシア社、スウエーデン)。しか
し、これらの天然高分子系担体は、以下の欠点を
有する。
(1)機械的強度が不十分なために操作上の制約が
多い。たとえば活性化、固定化等の吸着体の調製
時に破壊されたり、輸送、使用時に担体のカケ、
クダケが生じる。
(2)軟質ゲルであるため、カラムに充填し体外循
環に用いる場合に、除去すべき物質を含む体液を
高流速で流すことができない。体液のような高粘
度、高溶質濃度液を高流速で流すと、軟質ゲルで
あるため、充填体積が減少し、目づまりと流量低
下をおこし、ついには流れなくなる場合もある。
(3)軟質ゲルでありパーマネントポアーではない
ため、体外循環治療用吸着材の必須要件である滅
菌操作も容易に行えない。たとえばエチレンオキ
サイドガス滅菌のよいに薬剤滅菌の場合、凍結乾
燥して滅菌されるが、凍結乾燥によつて細孔が破
壊され、再び水系媒体に分散しても元にもどらな
い。凍結乾燥時その体積は約半量まで減少し、再
び水系媒体に分散しても元の体積のたかだか80%
程度にしかもどらず、吸着能力も減少するのが常
である。凍結乾燥時細孔を保護するため、添加剤
を混入して行う方法もあるが、添加剤が体液に入
るのを防ぐため、使用前に徹底的な洗浄を施さな
ければならない。
また高圧蒸気滅菌のような熱滅菌も、細孔を破
壊するので用いることができない。同様に放射線
滅菌も、その骨格および細孔を破壊するので用い
ることができない。
(4)さらには天然高分子系担体は体外循環治療用
に用いる時、補体系の活性化、凝固系の活性化が
おこり、ロイコペニア、スロンボサイトペニア等
を生来するといわれ、あまり好ましくない。
本発明者らは、従来の担体の欠点を克服した体
外循環治療用担体を鋭意研究した結果、本発明を
完成するに至つた。
すなわち、本発明は、多孔質粒子状担体に被吸
着物質と結合可能なリガンドを共有結合で保持さ
せてなる体外循環治療用吸着材において、該多孔
質粒子状担体が水酸基を有する親水性架橋有機合
成高分子からなり、保水量が0.5〜6g/g、水酸
基密度が5〜17meq/gの範囲にある担体であつ
て、該担体の比表面積が少なくとも5m2/gであ
り、かつ担体を直径10mm、長さ50mmの容器に充填
し通水するとき、容器の入口と出口の圧力差が
200mmHgの状態で、担体の体積減少率が10%以下
である硬質ゲル担体であることを特徴とする体外
循環治療用吸着材に係る。上記吸着剤において、
硬質ゲル担体の平均粒子径が25〜2500μmの範囲
にある場合は、より好ましい体外循環治療用吸着
剤となる。さらには硬質ゲル担体がビニルアルコ
ール単位を主構成成分とする架橋合成高分子であ
り、カルボン酸のビニルエステルとイソシアヌレ
ート環を有するビニル化合物の共重合体を加水分
解して得られる架橋合成高分子である体外循環治
療用吸着材は特に好ましい。
本目的に用いる担体としては、物理的特性とし
て、(1)活性化、固定化等の吸着材の調整、輸送、
使用等に十分に耐える機械的強度、(2)カラムに充
填し、血漿、血液等の高溶質濃度、高粘度な体液
を高流速で流すことができる硬さと平均粒子径、
(3)エチレンオキサイドガス滅菌のような薬剤滅菌
(凍結乾燥滅菌)、高圧蒸気滅菌のような熱滅菌に
耐える細孔の物理的安定性が要求される。本発明
者らは、物理的特性の異なる種々の既存の担体お
よび新たに合成した担体について検討した結果、
実に驚くべきことには、硬質ゲル担体がみごとに
上記要求を満足すること、特に一定の特性値をも
つ担体が好ましい結果を与えることを見い出し
た。
本発明において硬質ゲル担体とは、外力を加え
たときゲルの物性値が一定値以上を保持するもの
をいう。具体的には、ゲルを直径10mm、長さ50mm
の容器に充填し通水するとき、容器の入口と出口
の圧力差が200mmHgの状態で、ゲルの体積減少率
が10%以下であるものをいう。また、このような
ゲルは凍結乾燥したとき、その比表面積は5m2/
g以上の値を保持する。
比表面積とは、乾燥ゲル単位重量当りに吸着し
た窒素ガスが占有する表面でもつて表示したもの
である。つまり比表面積は単位重量のゲルを構成
する物質が乾燥状態でいかに有効に表面を形成し
ているかを表示している。
一般に高分子ゲルは、そのゲルと親和性のある
媒体中で膨潤し、乾燥すると収縮する。膨潤時に
媒体が満たされているポアーが架橋の網目のみで
維持されている軟質ゲルの場合は、乾燥すると網
目がつぶれてしまい、ポアーはほとんど消失す
る。この場合の比表面積は、ほとんど粒子の外側
だけの値になるため、一般に1m2/g以下の低い
値を示す。従来アフイニテイクロマトグラフイ用
として知られているアガロースは軟質ゲルである
ため、乾燥によつてポアーが消失してしまう。し
たがつて、滅菌操作も容易に行えず、さらにはつ
ぶれやすい軟質の網目を持つているため、カラム
に充填し体外循環に用いる場合にも、体液を長時
間、高流速で流すことができない。
一方、ポアーがしつかりした構造をもち、凍結
乾燥や熱滅菌に耐える硬質ゲルの場合には、乾燥
した際にポアーは多少収縮するものの膨潤時の状
態をほとんど維持する。つまりパーマネントポア
ーを有し、比表面積は軟質ゲルより高い値を示
し、少なくとも5m2/g以上の値を示す。
本発明の担体として用いる硬質ゲルの比表面積
は、少なくとも5m2/g以上有するものである
が、この値は一般的に大きいほど好ましい。上限
は1000m2/g位まで使用可能である。
比表面積の測定法はいろいろあるが、本発明で
は、最も一般的な窒素ガスによるBET法で求め
た。また比表面積測定に用いるサンプルは十分乾
燥しておかなければならないが、本発明の担体は
乾燥しにくいこともあり、水にぬれた担体をアセ
トンと平衡にした後、60℃以下で減圧乾燥して測
定用サンプルとした。
本発明に用いる硬質ゲルの保水量(以下WRと
いう)は0.5〜6g/gの範囲にあるのが適当で
あり、好ましくは1.0〜5.0g/gの範囲にあるも
のが最も良好な結果を与える。
WRとは、ゲルを生理食塩水と平衡にした時の
ゲルが粒子内に含みうる生理食塩水の量をゲル乾
燥重量あたりの値として表示したものである。つ
まりWRはゲル内の孔量の目安になる。WRが大き
くなると、水中においてゲル単位体積あたりの骨
格を形成する部分、つまりゲルそのものの重量お
よび生理食塩水中さらには体液中においてゲルの
機械的強度が相対的に低下する。またWRがあま
り小さくなると、吸着に有効な単位重量(または
単位体積)あたりの孔量が少なくなるので吸着能
力が低下する。したがつて、WRが適当な範囲に
あることが本目的の担体にとつて好ましい。
WRは予め十分に乾燥したゲルの重量(W2)を
測定した後に、生理食塩水と十分平衡にしたゲル
を遠心分離器にかけてゲル表面に付着している生
理食塩水を除去した後、その重量(W1)を測定
し、次式によつて求めることができる。
WR=W1−W2/W2(g/g)
以上のように、本発明の吸着材に用いる硬質ゲ
ル担体において、保水量が一定の範囲に入ること
が好ましいが、有効な吸着能力を維持しつつ、し
かも血液、血漿等の体液のような高粘度、高溶質
濃度の液を高流速で長時間安定に流通するには、
さらに硬質ゲル担体の平均粒子径(DW)が一定
の範囲にあることが好ましい。
平均粒子径は小さいほど吸着能力が高くなり好
ましいが、あまり小さ過ぎると体液を高流速で長
時間、安定に流通できなくなる。したがつて、平
均粒子径は25〜2500μmが好ましく、特に全血用
に用いる場合など、より好ましくは150〜1500μm
である。
体外循環治療用吸着材に用いる硬質ゲル担体の
排除限界分子量(Mim)は、硬質ゲル担体に
化学結合により保持させる物質の分子量および目
的吸着物質の分子量を勘案して設定すればよい。
通常タンパク質Mimで103ないし108の範囲にあ
る。タンパク質Mimはゲルのポアー内へ浸透
できない分子の分子量の下限を示す値である。M
imはゲルをカラムに充填して分子量既知の標
準タンパク質を用いて公知の方法で測定すること
ができる。
本発明に用いる硬質ゲル担体の化学的特性とし
ては、(1)被吸着物質に対し、例えば生物学的また
は/および化学的相互作用を示し、これと結合し
うる物質(リガンド)を高密度に化学結合できる
ように官能基の密度が高いこと、(2)目的とする物
質を選択的に吸着するように、担体の血漿タンパ
ク質等に対する非特異吸着が少ないこと、(3)補体
系、凝固系の活性化等の生体成分との反応が少な
いこと、(4)さらに全血用吸着材として用いる場合
には、血球成分との相互作用、すなわち、血栓形
成や血球成分の非特異粘着、残血等が少ないこと
等の特性を備えたものが好ましい。したがつて、
既に述べた物理的特性に加えて、以上の化学的特
性を満たす担体がより好ましく用いられる。
本発明者らは、鋭意研究の結果、水酸基を有す
る架橋合成高分子からなる硬質ゲル担体が、上記
特性を良好に示すことを見い出した。さらには水
酸基密度として5〜17meq/gの範囲にあるもの
が好ましい結果を与え、特に6〜15meq/gの範
囲にあるものがより好ましい結果を与えた。
通常架橋合成高分子は、線状ポリマーと架橋剤
で構成され、水酸基は線状ポリマー中に発現され
る。したがつて、水酸基の密度が高いほど親水性
が増加し、生体成分との相互作用が少なくなり、
リガンドの保持容量も向上して好ましいが、高す
ぎると架橋剤含量が低下して担体の強度が低下す
る。また水酸基の密度が低くすぎると、非特異吸
着が生じて好ましくない。
水酸基の密度は、ゲルをピリジン溶媒中で無水
酢酸と反応させて、水酸基と反応して消費した無
水酢酸の量はまたゲルの重量変化を測定し、これ
から求めることができる。乾燥ゲル1gが1mmo
の無水酢酸と反応したときの水酸基密度が
1meq/gである。
水酸基を有する親水性架橋合成高分子は、水酸
基を有するモノマーの重合またはポリマーの化学
反応による水酸基の導入により合成できる。両者
を併用して合成することもできる。重合方法とし
ては、ラジカル重合法を用いることができる。架
橋剤は重合時共重合により導入するとよい。また
ポリマーの化学反応(ポリマー間、ポリマーと架
橋剤)で導入することを併用してもよい。
一例をあげると、ビニル系モノマーとビニル系
またはアリル系架橋剤との共重合により作ること
ができる。この場合の親水性架橋合成高分子とし
ては、架橋ポリビニルアルコール、架橋ポリ2−
ハイドロオキシエチルアクリレート、架橋ポリ2
−ハイドロオキシエチルメタアクリレート等の架
橋ビニル系ポリマーを例示することができる。特
に架橋ビニルアルコール等のビニルアルコール単
位を主構成成分とする架橋合成高分子が、高い水
酸基密度を与えることができて好ましい結果を与
える。
架橋剤としては、トリアリルイソシアヌレー
ト、トルアリルシアヌレート等のアリル化合物
類、エチレングリコールジメタアクリレート、ジ
エチレングリコールジメタアクリレート等のジ
(メタ)アクリレート類、ブタンジオールジビニ
ルエーテル、ジエチレングリコールジビニルエー
テル、テトラビニルグリオキザール等のポリビニ
ルエーテル類、ジアリリデンペンタエリスリツ
ト、テトラアリロキシエタンのようなポリアリル
エーテル類、グリシジルメタクリレート等のグリ
シジルアクリレート類を用いることができる。特
に機械的強度、硬さ、微細孔構造、化学的特性の
面よりトリアリルイソシアヌレート単位が好まし
い。
また必要に応じてビニルエステル、ビニルエー
テル等のコモノマーを共重合したものも用いるこ
とができる。
ビニル系共重合体の場合には、カルボン酸のビ
ニルエステルとイソシアヌレート環を有するビニ
ル化合物(アリル化合物)を共重合し、共重合体
を加水分解して得られるポリビニルアルコールの
トリアリルイソシアヌレート架橋体が、機械的強
度、硬さ、細孔の安定性、化学的特性の面で特に
良好な担体を与える。
リガンドを硬質ゲル担体に結合する方法は、共
有結合、イオン結合、物理吸着、包理あるいは重
合体表面への沈殿不溶化等あらゆる公知の方法を
用いることができるが、結合物の溶出性よりみ
て、共有結合により固定、不溶化して用いること
が好ましい。そのため通常固定化酵素、アフイニ
テイクロマトグラフイで用いられる公知の担体の
活性化方法およびリガンドの結合方法を用いるこ
とができる。
活性化方法を例示すると、ハロゲン化シアン
法、エピクロルヒドリン法、ビスエポキシド法、
ハロゲン化トリアジン法、ブロモアセチルブロミ
ド法、エチルクロロホルマート法、1,1′−カル
ボニルジイミダゾール法等をあげることができ
る。本発明の活性化方法は、リガンドのアミノ
基、水酸基、カルボキシル基、チオール基等の活
性水素を有する求核反応基と置換および/または
付加反応できればよく、上記の例示に限定される
ものではない。
本発明において、硬質ゲル担体に保持させるリ
ガンドを例示する。
全身性エリテマトーデス治療用としては、抗核
抗体、抗DNA抗体の吸着除去用に、アデニン、
グアニン、シトシン、ウラシル、チミル等のモ
ノ、ジ、トリヌクレオチドのホモポリマー、また
はコポリマー、天然に存在するDNA、RNA等の
核酸を用いることができる。また血中に存在する
DNA、RNA、ENAの吸着除去用に、抗一本鎖
DAN抗体、抗二本鎖のDNA抗体、抗RNA抗体、
抗ENA抗体等の抗核酸抗体、メチル化アルブミ
ンアクチノマイシンD等の塩基性化合物を用いる
ことができる。さらに、血中の免疫複合体の吸着
除去用には、C1q等の補体成分、プロテインA等
の特異タンパク質、抗ヘビーチエイン不変部第2
相抗体等の免疫複合体に対する抗体を用いること
ができる。
慢性関節リウマチ、悪性関節リウマチ治療用と
しては、尿素、塩酸グアニジン、メルカプトエタ
ノール、界面活性剤、有機溶剤等の化学的変性
(凝集)方法、熱、超音波、ガスバブリング等の
物理的変性(凝集)方法により変性された変性γ
−グロブリン、変性イムノグロブリン、凝集γ−
グロブリン、凝集イムノグロブリン、イムノグロ
ブリンのFc部、イムノグロブリンのヘビーチエ
イン不変部第2相およびそれらの前記変性方法に
よる変性体等のリウマチ因子に対する抗原様物
質、および抗リウマチ因子抗体を用いることがで
きる。またリウマチの免疫複合体除去用には、
C1q等の補体成分、プロテインA等の特異タンパ
ク質、抗ヘビーチエイン不変部第2相抗体等の免
疫複合体に対する抗体を用いることができる。
橋本病治療用には、サイグロブリン、甲状線の
ミクロソーム分画成分を用いることができる。
重症筋無力症治療用には、神経筋のアセチルコ
リンレセプター分画成分を用いることができる。
糸球体腎炎治療用には、糸球体基底膜成分、特
発性血小板滅少性紫斑病治療用は、血小板膜成
分、血小板顆粒分画成分、クツシング症候群治療
用にはトランスコーチゾン、抗コーチゾン抗体を
用いることができる。
肝炎の予防、治療用には、A型肝炎ウイルス、
B型肝炎ウイルス等のウイルス表面抗原に対する
抗体を用いることができる。
高血圧治療用には、抗アンジオテンシン抗
体、高脂血症治療用にはヘパリン、抗リポプロテ
イン抗体を用いることができる。
リンパ球異常に基づく免疫疾患治療用には、抗
Bセル抗体、抗サプレツサーT抗体、抗ヘルパー
T抗体等の抗リンパ球抗体を用いることができ
る。
乳ガン等のガン治療用には、プロテインA、抗
イムノグロブリン抗体を用いることができる。
本発明に用いることができるリガンドは、以上
の例示に限定されるものではなく、コングニチニ
ン、コンカナバリンA、フイトヘマアグルチニン
等のレクチン、核酸、アミノ酸、脂質、プロミタ
ン、ヘパリン、抗原、抗体、酵素、基質、補酵素
等の被吸着物質と結合可能な公知の物質を用いる
ことができる。
また硬質ゲル担体に2種以上のリガンドを保持
させて用いることもできる。さらにはリガンドを
保持した担体を2種以上併用して用いることもで
きる。
以上述べてきたように、本発明の体外循環治療
用吸着材は機械的強度が十分であるため、活性
化、固定化等の吸着材の調製や輸送、体外循環使
用特に破壊されたり、カケやクダケを生ずること
が実質的になく、幅広い操作方法、条件を選択す
ることができる。また硬質ゲルであるため、カラ
ムに充填し、体外循環に用いる場合に、吸着、除
去すべき物質を含む体液を高流速で長時間、連続
的に安定に通液することができる。さらに硬質ゲ
ルであり、パーマネントポアーを有するため、体
外循環治療用吸着材の必須条件である滅菌操作も
容易に行えるものである。例えば吸着材を凍結乾
燥してエチレンオキサイドガス滅菌のような薬剤
滅菌も、吸着材の吸着能力を損うことなく実施で
きる。
本発明は、以上の効果を吸着材の基本的特性で
ある吸着能力を犠性にすることなく、高い能力を
維持したまま実施できる長所を併せ持つている。
さらには、水酸基を有する親水性架橋合成高分子
からなる粒子状硬質ゲル担体は、前記物理的特性
に加えて好ましい化学的特性を有し、次の効果を
示した。
高い水酸基密度を有するため、リガンドを高密
度に化学結合でき、目的物質の高い吸着能力を得
られると共に、高親水性であるため血漿タンパク
質等に対する非特異吸着が少ない。また補体系、
凝固形の活性化等の生体成分との反応が少なく、
さらには全血用吸着材として用いる場合にも、血
球成分との相互作用、すなわち、血栓形成や血球
成分の非特異粘着、残血等が少なく、好適に用い
ることができる。
本発明の吸着材は、自己血漿、自己血液等の体
液を浄化、再生する一般的な用法に適用可能であ
り、癌、免疫増殖性症候群、慢性関節リウマチ、
全身性エリテマトーデス等の膠原病、重症筋無力
症等の自己免疫疾患、アレルギー、臓器移植時の
拒絶反応等の生体免疫機能に関係した疾患および
現象、あるいは腎炎等の腎臓病、肝炎等の肝臓病
などの体外循環治療に有効に利用できる。
以下実施例により、本発明の実施の態様をより
詳細に説明する。
実施例 1
酢酸ビニル100g、トリアリルイソシアヌレー
ト24.1g(X=0.20)、酢酸エチル124g、ヘプタ
ン124g、ポリ酢酸ビニル(重合度500)3.1gお
よび2,2′−アゾビスイソブチロニトリル3.1g
よりなる均一混合液と、ポリビニルアルコール1
重量%、リン酸二水素ナトリウム二水和物0.05重
量%およびリン酸水素二ナトリウム十二水和物
1.5重量%を溶解した水400mlとをフラスコに入
れ、十分撹拌したのち、56.5℃で18時間、さらに
75℃で5時間加熱撹拌して懸濁重合をおこない、
粒状共重合体を得た。過水洗、ついでアセトン
抽出後、カセイソーダ46.5gおよびメタノール2
よりなる溶液中で、40℃で18時間、共重合体の
エステル交換反応を行つた。
得られた粒子の平均粒径は150μmであつた。前
記方法で水酸基密度(qOH)を求めたところ
13meq/gであつた。またゲルの保水量は4.4
g/g乾燥ゲルで、比表面積は10m2/gであつ
た。さらに標準球状タンパク質のリン酸緩衝食塩
液を用いてゲルの排除限界分子量を測定したとこ
ろ約180万であつた。
つぎにエステル交換され、水で十分に洗浄され
たゲル50c.c.を200mlの水に懸濁し、3gの臭化シ
アンを加え、プロペラ撹拌羽根を用いて撹拌す
る。2N水酸化ナトリウム溶液を用いてPHを10〜
11に保ち8分間反応させた。反応終了後はすみや
かにガラスフイルターで過し、ついで水2で
洗浄して活性化ゲルを得た。
さらに活性化ゲル5mlを0.1M炭酸水素ナトリ
ウム50mlで洗浄する。リガンドとしてプロテイン
A50mgを0.1M炭酸水素ナトリウムに溶解し、カ
セイソーダ水溶液を用いてPHを9.5に調節し、活
性化ゲルに加える。ついでこれを25℃で16時間振
盪し、ガラスフイルターを用いて過する。得ら
れた吸着材を、0.1M炭酸水素ナトリウム液およ
び酢酸バツフアー(PH4.0)で交互に洗浄した。
該吸着材をもとのゲル粒子と比較して光学顕微
鏡で観察したところ、カケ、クダケ等の破壊はみ
られなかつた。
この吸着材を4mlカラム(L/D=5)に充填
して、ヒト血漿を0.2ml/mm、ヒト全血(ヘパリ
ン添加1200U/100ml血液)を0.5ml/mmでシング
ルパス法にて各1時間通液した。いずれも充填体
積の低下、目づまり、流量低下はみられず、カラ
ム前の圧力計の変化も10〜20mmHgであつた。
通液前後の血漿タンパクおよび血液血球成分の
変動を調べたところ、血漿ではアルブミンの変動
はわずかであり、C3、C4等の補体の減少も少な
かつたが、プロテインAとグロブリンの相互作用
によりグロブリンを約30%吸着した。全血ではカ
ラムはうすい赤色をおびるにととまり、残血は極
めて少なかつた。吸着材の表面の光学顕微鏡観察
を行つたところ、赤色血栓、白色血栓ともに少な
かつた。またカラム通過血の血球数をカウントし
たところ、赤血球、血小板、白血球ともに減少は
比較的少なかつた。
実施例 2
実施例1で示した重合方法、ケン化方法を用い
て下表の物性値のゲルを得た。
The present invention relates to an adsorbent for extracorporeal circulation therapy, in which a particulate carrier holds a ligand capable of binding to an adsorbed substance. More specifically, diseases and phenomena related to the body's immune system such as cancer, immunoproliferative syndrome, rheumatoid arthritis, systemic lupus erythematosus, allergies, rejection reactions during organ transplants, kidney diseases such as nephritis, hepatitis, etc. The present invention relates to an adsorbent that adsorbs and removes malignant substances from body fluids, such as blood and plasma, which are thought to be closely related to the cause or progression of diseases, such as those associated with liver diseases. Conventionally, activated carbon or activated carbon coated with a hydrophilic polymer has been used as an artificial liver for liver diseases, mainly for extracorporeal circulation therapy. However, as mentioned above, in many diseases, various malignant substances that are closely related to the cause or progression of the disease have become known, and there is a growing need to selectively remove these malignant substances from body fluids. However, adsorbents based on activated carbon have low adsorption selectivity and cannot currently meet this demand. In order to respond to the demand for selective adsorption and removal of malignant substances, the present inventors have conducted extensive research and have developed a special substance that has a biological and/or chemical selective interaction with the adsorbed substance on the carrier. We have discovered various adsorbents that are held together by chemical bonds, and have previously applied for a patent. (JP-A-57-122875, JP-A-57-
134164, JP-A-57-156035) Furthermore, the present inventors conducted detailed research on particulate carriers used in the adsorbent, particularly particulate carriers for extracorporeal circulation treatment. Hitherto, no carrier specifically designed for this purpose is known. Therefore, there was no choice but to repurpose a carrier that is generally known for use in affinity chromatography. As known carriers, natural polymer carriers such as agarose-based carriers, dextran-based carriers, and cellulose-based carriers are known (for example, trade name: Cepharose, Pharmacia, Sweden). However, these natural polymer carriers have the following drawbacks. (1) There are many operational restrictions due to insufficient mechanical strength. For example, the adsorbent may be destroyed during the preparation of the adsorbent during activation or immobilization, or the carrier may break during transportation or use.
Kudake occurs. (2) Since it is a soft gel, when it is packed into a column and used for extracorporeal circulation, it is not possible to flow body fluids containing substances to be removed at a high flow rate. When a high viscosity, high solute concentration liquid such as body fluid is flowed at a high flow rate, since it is a soft gel, the filling volume decreases, causing clogging and a decrease in flow rate, which may eventually stop flowing. (3) Since it is a soft gel and does not have permanent pores, it cannot be easily sterilized, which is an essential requirement for adsorbents for extracorporeal circulation therapy. For example, in the case of ethylene oxide gas sterilization or chemical sterilization, sterilization is performed by freeze-drying, but the pores are destroyed by freeze-drying and do not return to their original state even if they are redispersed in an aqueous medium. During freeze-drying, its volume decreases to about half, and even when redispersed in an aqueous medium, it remains at most 80% of its original volume.
It usually returns only to a certain extent and the adsorption capacity also decreases. Some methods include adding additives to protect the pores during freeze-drying, but to prevent the additives from entering body fluids, they must be thoroughly washed before use. Furthermore, heat sterilization such as high-pressure steam sterilization cannot be used because it destroys the pores. Similarly, radiation sterilization cannot be used as it destroys the skeleton and pores. (4) Furthermore, when natural polymer carriers are used for extracorporeal circulation therapy, they are said to activate the complement system and coagulation system, resulting in leucopenia, thrombocytopenia, etc., and are therefore not very desirable. The present inventors have completed the present invention as a result of intensive research into a carrier for extracorporeal circulation therapy that overcomes the drawbacks of conventional carriers. That is, the present invention provides an adsorbent for extracorporeal circulation therapy in which a porous particulate carrier holds a ligand capable of binding to an adsorbed substance through a covalent bond, wherein the porous particulate carrier contains a hydrophilic crosslinked organic compound having a hydroxyl group. A carrier made of a synthetic polymer, having a water retention capacity of 0.5 to 6 g/g and a hydroxyl group density of 5 to 17 meq/g, the specific surface area of the carrier being at least 5 m 2 /g, and the diameter of the carrier being When filling a container of 10 mm and length 50 mm and passing water through it, the pressure difference between the inlet and outlet of the container is
The present invention relates to an adsorbent for extracorporeal circulation therapy, which is a hard gel carrier with a volume reduction rate of 10% or less at 200 mmHg. In the above adsorbent,
When the average particle diameter of the hard gel carrier is in the range of 25 to 2500 μm, it becomes a more preferable adsorbent for extracorporeal circulation treatment. Furthermore, the hard gel carrier is a crosslinked synthetic polymer mainly composed of vinyl alcohol units, and is a crosslinked synthetic polymer obtained by hydrolyzing a copolymer of a vinyl compound of carboxylic acid and a vinyl compound having an isocyanurate ring. The adsorbent for extracorporeal circulation therapy is particularly preferred. The carrier used for this purpose has physical properties such as (1) adjustment of adsorbent such as activation and immobilization, transportation,
Mechanical strength sufficient to withstand use, etc.; (2) hardness and average particle size that allow high solute concentration and high viscosity body fluids such as plasma and blood to flow at high flow rates when filled into columns;
(3) Physical stability of the pores is required to withstand chemical sterilization (lyophilization sterilization) such as ethylene oxide gas sterilization and heat sterilization such as high-pressure steam sterilization. As a result of studying various existing carriers and newly synthesized carriers with different physical properties, the present inventors found that
Indeed, it has been surprisingly found that hard gel carriers satisfactorily meet the above requirements, and in particular that carriers with certain characteristic values give favorable results. In the present invention, the term "hard gel carrier" refers to one that maintains gel physical property values above a certain value when external force is applied. Specifically, the gel is 10 mm in diameter and 50 mm in length.
When filling a container and passing water through it, the volume reduction rate of the gel is 10% or less when the pressure difference between the inlet and outlet of the container is 200 mmHg. Furthermore, when such a gel is freeze-dried, its specific surface area is 5 m 2 /
Hold a value greater than or equal to g. The specific surface area is expressed as the surface occupied by nitrogen gas adsorbed per unit weight of dry gel. In other words, the specific surface area indicates how effectively the substance constituting the gel per unit weight forms the surface in a dry state. Generally, polymer gels swell in a medium that has an affinity for the gel and shrink when dried. In the case of a soft gel in which the pores that are filled with the medium during swelling are maintained only by a network of crosslinks, when the gel dries, the network collapses and the pores almost disappear. In this case, the specific surface area is almost limited to the outside of the particle, so it generally shows a low value of 1 m 2 /g or less. Since the agarose conventionally known for use in affixine chromatography is a soft gel, its pores disappear when it dries. Therefore, it is not easy to sterilize, and furthermore, it has a soft mesh that is easily crushed, so even when packed in a column and used for extracorporeal circulation, body fluids cannot be passed through it at a high flow rate for a long period of time. On the other hand, in the case of a hard gel that has a firm pore structure and can withstand freeze-drying and heat sterilization, the pores will shrink somewhat when dried, but will maintain most of their swollen state. In other words, it has permanent pores, and its specific surface area is higher than that of soft gel, and is at least 5 m 2 /g. The hard gel used as the carrier of the present invention has a specific surface area of at least 5 m 2 /g or more, and it is generally preferable that this value is as large as possible. The upper limit can be used up to about 1000m 2 /g. There are various methods for measuring the specific surface area, but in the present invention, it was determined by the most common BET method using nitrogen gas. In addition, the sample used for specific surface area measurement must be sufficiently dry, but since the carrier of the present invention is difficult to dry, the carrier wet with water is equilibrated with acetone and then dried under reduced pressure at 60°C or less. This was used as a sample for measurement. The water retention capacity (hereinafter referred to as W R ) of the hard gel used in the present invention is suitably in the range of 0.5 to 6 g/g, and preferably in the range of 1.0 to 5.0 g/g for best results. give. W R is the amount of saline that the gel can contain within the particles when the gel is equilibrated with saline, expressed as a value per dry weight of gel. In other words, W R is a measure of the amount of pores in the gel. As W R increases, the weight of the part forming the skeleton per unit volume of the gel in water, that is, the weight of the gel itself, and the mechanical strength of the gel in physiological saline and even body fluids decrease relatively. Furthermore, if W R becomes too small, the amount of pores per unit weight (or unit volume) effective for adsorption will decrease, resulting in a decrease in adsorption capacity. Therefore, it is preferable for the carrier for this purpose that W R be within an appropriate range. W R measures the weight (W 2 ) of a sufficiently dried gel in advance, and then centrifuges the gel, which has been sufficiently equilibrated with physiological saline, to remove the physiological saline attached to the gel surface. The weight (W 1 ) can be measured and calculated using the following formula. W R = W 1 - W 2 /W 2 (g/g) As mentioned above, in the hard gel carrier used for the adsorbent of the present invention, it is preferable that the water retention amount falls within a certain range, but the effective adsorption capacity In order to maintain stable flow of fluids with high viscosity and high solute concentration such as blood and plasma for long periods of time at high flow rates,
Furthermore, it is preferable that the average particle diameter (D W ) of the hard gel carrier is within a certain range. The smaller the average particle diameter, the higher the adsorption capacity, which is preferable, but if it is too small, body fluids cannot be stably distributed at a high flow rate for a long time. Therefore, the average particle diameter is preferably 25 to 2500 μm, more preferably 150 to 1500 μm, especially when used for whole blood.
It is. The exclusion limit molecular weight (Mim) of a hard gel carrier used as an adsorbent for extracorporeal circulation therapy may be set by taking into consideration the molecular weight of the substance to be held by the hard gel carrier through chemical bonding and the molecular weight of the target adsorbent.
It is usually in the range of 10 3 to 10 8 for the protein Mim. Protein Mim is a value indicating the lower limit of the molecular weight of molecules that cannot penetrate into the pores of the gel. M
im can be measured by a known method by filling a gel into a column and using a standard protein of known molecular weight. The chemical properties of the hard gel carrier used in the present invention include (1) a high density of substances (ligands) that exhibit, for example, biological and/or chemical interactions with the adsorbed substance and can bind to it; (2) The carrier has low nonspecific adsorption to plasma proteins, etc. so that it selectively adsorbs the target substance, (3) Complement system, coagulation system (4) Furthermore, when used as an adsorbent for whole blood, there is no interaction with blood cell components, such as thrombus formation, non-specific adhesion of blood cell components, and residual blood. It is preferable that the material has characteristics such as having a small number of problems. Therefore,
In addition to the physical properties already mentioned, a carrier that satisfies the above chemical properties is more preferably used. As a result of extensive research, the present inventors have discovered that a hard gel carrier made of a crosslinked synthetic polymer having hydroxyl groups exhibits the above characteristics well. Furthermore, those with a hydroxyl group density in the range of 5 to 17 meq/g gave preferable results, and particularly those with a hydroxyl group density in the range of 6 to 15 meq/g gave more preferable results. Generally, crosslinked synthetic polymers are composed of a linear polymer and a crosslinking agent, and hydroxyl groups are expressed in the linear polymer. Therefore, the higher the density of hydroxyl groups, the more hydrophilic it becomes and the less interaction with biological components.
It is preferable because it also improves the retention capacity of the ligand, but if it is too high, the content of the crosslinking agent decreases and the strength of the carrier decreases. Furthermore, if the density of hydroxyl groups is too low, non-specific adsorption will occur, which is not preferable. The density of hydroxyl groups can be determined by reacting the gel with acetic anhydride in a pyridine solvent, and measuring the amount of acetic anhydride consumed by reacting with the hydroxyl groups by measuring the change in weight of the gel. 1g of dry gel is 1mmo
The hydroxyl group density when reacting with acetic anhydride is
It is 1meq/g. A hydrophilic crosslinked synthetic polymer having a hydroxyl group can be synthesized by polymerizing a monomer having a hydroxyl group or introducing a hydroxyl group through a chemical reaction of a polymer. It is also possible to synthesize both in combination. As the polymerization method, a radical polymerization method can be used. The crosslinking agent is preferably introduced by copolymerization during polymerization. In addition, introduction through a chemical reaction of polymers (between polymers, between polymers and a crosslinking agent) may be used in combination. For example, it can be made by copolymerizing a vinyl monomer and a vinyl or allyl crosslinking agent. In this case, the hydrophilic crosslinked synthetic polymers include crosslinked polyvinyl alcohol, crosslinked poly(2-
Hydroxyethyl acrylate, crosslinked poly2
- Crosslinked vinyl polymers such as hydroxyethyl methacrylate can be exemplified. In particular, crosslinked synthetic polymers containing vinyl alcohol units as a main component, such as crosslinked vinyl alcohol, can provide a high hydroxyl group density and give favorable results. Examples of crosslinking agents include allyl compounds such as triallyl isocyanurate and tolylyl cyanurate, di(meth)acrylates such as ethylene glycol dimethacrylate and diethylene glycol dimethacrylate, butanediol divinyl ether, diethylene glycol divinyl ether, and tetravinyl. Polyvinyl ethers such as glyoxal, polyallyl ethers such as diarylidene pentaerythrite and tetraallyloxyethane, and glycidyl acrylates such as glycidyl methacrylate can be used. In particular, triallylisocyanurate units are preferred from the viewpoints of mechanical strength, hardness, micropore structure, and chemical properties. If necessary, copolymerized comonomers such as vinyl esters and vinyl ethers may also be used. In the case of vinyl copolymers, triallylisocyanurate crosslinking of polyvinyl alcohol obtained by copolymerizing a vinyl ester of carboxylic acid and a vinyl compound (allyl compound) having an isocyanurate ring and hydrolyzing the copolymer. The body provides a particularly good support in terms of mechanical strength, hardness, pore stability and chemical properties. Any known method such as covalent bonding, ionic bonding, physical adsorption, embedding, or precipitation insolubilization on the polymer surface can be used to bond the ligand to the hard gel carrier. It is preferable to use it after being fixed and insolubilized by covalent bonding. Therefore, it is possible to use commonly known methods for activating immobilized enzymes, carriers used in affinity chromatography, and binding methods for ligands. Examples of activation methods include cyanogen halide method, epichlorohydrin method, bisepoxide method,
Examples include the halogenated triazine method, the bromoacetyl bromide method, the ethyl chloroformate method, and the 1,1'-carbonyldiimidazole method. The activation method of the present invention is not limited to the above examples as long as it can perform a substitution and/or addition reaction with a nucleophilic reactive group having active hydrogen such as an amino group, a hydroxyl group, a carboxyl group, or a thiol group of the ligand. . In the present invention, the ligands to be retained on the hard gel carrier will be exemplified. For the treatment of systemic lupus erythematosus, adenine,
Homopolymers or copolymers of mono-, di-, and trinucleotides such as guanine, cytosine, uracil, and thymil, and naturally occurring nucleic acids such as DNA and RNA can be used. also present in the blood
Anti-single-stranded for adsorption removal of DNA, RNA, and ENA.
DAN antibody, anti-double-stranded DNA antibody, anti-RNA antibody,
Anti-nucleic acid antibodies such as anti-ENA antibodies and basic compounds such as methylated albumin actinomycin D can be used. Furthermore, for the adsorption and removal of immune complexes in the blood, complement components such as C1q, specific proteins such as protein A, anti-heavichain constant region 2
Antibodies to the immune complex, such as complementary antibodies, can be used. For the treatment of rheumatoid arthritis and malignant rheumatoid arthritis, chemical denaturation (coagulation) methods such as urea, guanidine hydrochloride, mercaptoethanol, surfactants, and organic solvents, physical denaturation (coagulation) methods such as heat, ultrasound, and gas bubbling are used. ) Modified γ modified by method
-Globulin, modified immunoglobulin, aggregated γ-
Antigen-like substances against rheumatoid factors such as globulin, aggregated immunoglobulin, Fc region of immunoglobulin, heavy chain constant region 2 of immunoglobulin, and modified products thereof by the above-mentioned modification method, and anti-rheumatoid factor antibodies can be used. . In addition, for the removal of rheumatoid immune complexes,
Antibodies against immune complexes such as complement components such as C1q, specific proteins such as protein A, and anti-heavichein constant region 2 phase antibodies can be used. For the treatment of Hashimoto's disease, thyglobulin, a microsomal fraction of thyroid gland, can be used. For the treatment of myasthenia gravis, neuromuscular acetylcholine receptor fraction components can be used. Glomerular basement membrane components are used to treat glomerulonephritis, platelet membrane components and platelet granule fraction components are used to treat idiopathic thrombocytopenic purpura, and transcortisone and anticortisone antibodies are used to treat Cushing syndrome. be able to. For the prevention and treatment of hepatitis, hepatitis A virus,
Antibodies against viral surface antigens such as hepatitis B virus can be used. Anti-angiotensin antibodies can be used to treat hypertension, and heparin and anti-lipoprotein antibodies can be used to treat hyperlipidemia. For the treatment of immune diseases based on lymphocyte abnormalities, anti-lymphocyte antibodies such as anti-B cell antibodies, anti-suppressor T antibodies, and anti-helper T antibodies can be used. Protein A and anti-immunoglobulin antibodies can be used to treat cancer such as breast cancer. Ligands that can be used in the present invention are not limited to the above examples, but include lectins such as congnitinin, concanavalin A, and phytohemaagglutinin, nucleic acids, amino acids, lipids, promitan, heparin, antigens, antibodies, enzymes, Known substances that can bind to adsorbed substances such as substrates and coenzymes can be used. It is also possible to use a hard gel carrier holding two or more types of ligands. Furthermore, two or more types of carriers holding ligands can be used in combination. As described above, the adsorbent for extracorporeal circulation treatment of the present invention has sufficient mechanical strength, so it does not cause destruction, chipping, etc. during the preparation and transportation of the adsorbent such as activation and immobilization, especially when used in extracorporeal circulation. There is virtually no formation of mold, and a wide range of operating methods and conditions can be selected. In addition, since it is a hard gel, when it is packed into a column and used for extracorporeal circulation, body fluids containing substances to be adsorbed and removed can be stably passed continuously at a high flow rate for a long period of time. Furthermore, since it is a hard gel and has permanent pores, it can be easily sterilized, which is an essential condition for an adsorbent for extracorporeal circulation therapy. For example, lyophilization of the adsorbent and chemical sterilization such as ethylene oxide gas sterilization can also be carried out without impairing the adsorption capacity of the adsorbent. The present invention has the advantage that the above-mentioned effects can be achieved without sacrificing the adsorption ability, which is a basic characteristic of the adsorbent, while maintaining high ability.
Furthermore, the particulate hard gel carrier made of a hydrophilic crosslinked synthetic polymer having hydroxyl groups had favorable chemical properties in addition to the above-mentioned physical properties, and exhibited the following effects. Since it has a high hydroxyl group density, it can chemically bond ligands at a high density and obtain a high adsorption capacity for target substances, and because it is highly hydrophilic, there is little nonspecific adsorption to plasma proteins and the like. Also, the complement system,
There is little reaction with biological components such as activation of coagulated forms,
Furthermore, when used as an adsorbent for whole blood, there is little interaction with blood cell components, ie, thrombus formation, non-specific adhesion of blood cell components, residual blood, etc., and it can be suitably used. The adsorbent of the present invention can be applied to general uses for purifying and regenerating body fluids such as autologous plasma and autologous blood, and is applicable to cancer, immunoproliferative syndrome, rheumatoid arthritis,
Collagen diseases such as systemic lupus erythematosus, autoimmune diseases such as myasthenia gravis, allergies, diseases and phenomena related to the body's immune function such as rejection during organ transplants, kidney diseases such as nephritis, and liver diseases such as hepatitis. It can be effectively used for extracorporeal circulation treatment such as. Embodiments of the present invention will be explained in more detail with reference to Examples below. Example 1 100 g of vinyl acetate, 24.1 g of triallylisocyanurate (X = 0.20), 124 g of ethyl acetate, 124 g of heptane, 3.1 g of polyvinyl acetate (degree of polymerization 500) and 3.1 g of 2,2'-azobisisobutyronitrile
A homogeneous mixed liquid consisting of polyvinyl alcohol 1
wt%, sodium dihydrogen phosphate dihydrate 0.05 wt% and disodium hydrogen phosphate dodecahydrate
Add 400ml of water in which 1.5% by weight was dissolved into a flask, stir thoroughly, and then heat at 56.5℃ for 18 hours.
Suspension polymerization was carried out by heating and stirring at 75°C for 5 hours.
A granular copolymer was obtained. After washing with water and then extracting with acetone, add 46.5 g of caustic soda and 2 methanol.
The transesterification reaction of the copolymer was carried out at 40°C for 18 hours in a solution consisting of: The average particle size of the obtained particles was 150 μm. When the hydroxyl group density (qOH) was determined using the above method
It was 13meq/g. Also, the water retention capacity of the gel is 4.4
g/g dry gel, and the specific surface area was 10 m 2 /g. Furthermore, the exclusion limit molecular weight of the gel was measured using a phosphate buffered saline solution of a standard globular protein, and was found to be approximately 1.8 million. Next, 50 c.c. of the gel that has been transesterified and thoroughly washed with water is suspended in 200 ml of water, 3 g of cyanogen bromide is added, and the suspension is stirred using a propeller stirring blade. Adjust the pH to 10 using 2N sodium hydroxide solution
11 and allowed to react for 8 minutes. After the reaction was completed, it was immediately filtered through a glass filter and then washed with 2 portions of water to obtain an activated gel. Further, 5 ml of activated gel is washed with 50 ml of 0.1M sodium bicarbonate. Protein as a ligand
Dissolve 50 mg of A in 0.1 M sodium bicarbonate, adjust the pH to 9.5 using aqueous caustic soda solution, and add to the activated gel. This is then shaken for 16 hours at 25°C and filtered through a glass filter. The obtained adsorbent was washed alternately with 0.1M sodium hydrogen carbonate solution and acetic acid buffer (PH4.0). When the adsorbent was compared with the original gel particles and observed under an optical microscope, no breakage such as chipping or flaking was observed. This adsorbent was packed into a 4 ml column (L/D = 5), and human plasma was added at 0.2 ml/mm and human whole blood (heparin added 1200 U/100 ml blood) was added at 0.5 ml/mm using a single pass method. The solution was passed for an hour. In all cases, no decrease in packing volume, clogging, or decrease in flow rate was observed, and the change in the pressure gauge in front of the column was 10 to 20 mmHg. When we examined changes in plasma proteins and blood cell components before and after fluid passage, we found that albumin in plasma showed only slight changes, and complements such as C 3 and C 4 decreased little; however, the interaction between protein A and globulin Approximately 30% of globulin was absorbed by the action. With whole blood, the column was only pale red in color, and there was very little residual blood. When the surface of the adsorbent was observed under an optical microscope, there were few red thrombi and white thrombi. Furthermore, when the number of blood cells in the blood passing through the column was counted, there was a relatively small decrease in red blood cells, platelets, and white blood cells. Example 2 Using the polymerization method and saponification method shown in Example 1, a gel having the physical properties shown in the table below was obtained.
【表】
該ゲルを実施例1と同様にして、活性化および
固定反応を行つた後に、該吸着材をもとの各ゲル
粒子と比較して光学顕微鏡で観察したところ、カ
ケ、クダケ等の破壊はみられなかつた。
また実施例1と同様にして、ヒト血漿、ヒト全
血(ヘパリン添加1200U/100ml血液)を通液し
たところ、いずれの吸着材も充填体積の低下、目
づまり、流量低下はほとんどみられなかつた。血
漿タンパク質の変動を調べたところ、アルブミ
ン、C3、C4等の補体の減少はいずれもごくわず
かであつた。固定したプロテインAによるグロブ
リンの吸着は、いずれも顕著にみられ、約15〜50
%減少した。
全血を用いた実験でも、残血、血栓形成、血球
数変化等は比較的少なかつた。
実施例 3
酢酸ビニル100g、トリアリルイソシアヌレー
ト32.2g(X=0.25)、酢酸エチル100g、n−ヘ
プタノール100g、ポリ酢酸ビニル6.6gおよび
2,2′−アゾビスイソブチロニトリル3.3gより
なる均一混合液を実施例1と同様に懸濁重合し、
得られた粒子のエステル交換反応をおこなつた。
得られたゲルの物性は平均粒径100μm、qOH=
12meq/g、WR=3.4g/gおよび比表面積は20
m2/gであつた。
実施例1と同様に排除限界分子量を測定したと
ころ約200万であつた。活性化は実施例1と同様
に行い、固定化プロテインAに代つてプロタミン
を用いた。他は実施例1と同様である。湿潤状態
の吸着材を121℃、20分間オートクレーブ滅菌し
たところ、吸着材の体積減少はほとんど認められ
なかつた。滅菌有無の2種類の吸着材について、
実施例1と同様にヒト血漿を通液したところ、ア
ルブミン、C3、C4等の補体の減少はいずれもご
くわずかであり、固定したプロタミンによるイム
ノグロブリンMの吸着は、単純免疫拡散法にて測
定したところ、いずれも顕著にみられ、約35%減
少した。[Table] After activating and fixing the gel in the same manner as in Example 1, the adsorbent was compared with the original gel particles and observed under an optical microscope. No destruction was seen. In addition, when human plasma and human whole blood (heparin-added 1200 U/100 ml blood) were passed through in the same manner as in Example 1, there was almost no decrease in filling volume, clogging, or decrease in flow rate for any of the adsorbents. . When changes in plasma proteins were examined, decreases in complements such as albumin, C 3 and C 4 were all minimal. The adsorption of globulin by immobilized protein A is remarkable in all cases, with approximately 15 to 50
%Diminished. Even in experiments using whole blood, there were relatively few residual blood, thrombus formation, changes in blood cell counts, etc. Example 3 A homogeneous solution consisting of 100 g of vinyl acetate, 32.2 g of triallylisocyanurate (X = 0.25), 100 g of ethyl acetate, 100 g of n-heptanol, 6.6 g of polyvinyl acetate and 3.3 g of 2,2'-azobisisobutyronitrile The mixed solution was subjected to suspension polymerization in the same manner as in Example 1,
The obtained particles were subjected to a transesterification reaction.
The physical properties of the obtained gel are: average particle size 100μm, qOH=
12meq/g, W R = 3.4g/g and specific surface area is 20
m 2 /g. The exclusion limit molecular weight was measured in the same manner as in Example 1 and was found to be approximately 2 million. Activation was performed in the same manner as in Example 1, using protamine instead of immobilized protein A. The rest is the same as in Example 1. When the wet adsorbent was sterilized in an autoclave at 121°C for 20 minutes, almost no volume reduction was observed. Regarding the two types of adsorbents: sterile and non-sterile,
When human plasma was passed in the same manner as in Example 1, there was only a slight decrease in complements such as albumin, C 3 and C 4 , and the adsorption of immunoglobulin M by fixed protamine was confirmed by simple immunodiffusion When measured at
Claims (1)
リガンドを共有結合で保持させてなる体外循環治
療用吸着材において、該多孔質粒子状担体が水酸
基を有する親水性架橋有機合成高分子からなり、
保水量が0.5〜6g/g、水酸基密度が5〜
17meq/gの範囲にある担体であつて、該担体の
比表面積が少なくとも5m2/gであり、かつ担体
を直径10mm、長さ50mmの容器に充填し通水すると
き、容器の入口と出口の圧力差が200mmHgの状態
で、担体の体積減少率が10%以下である硬質ゲル
担体であることを特徴とする体外循環治療用吸着
材。 2 硬質ゲル担体がビニルアルコール単位を主構
成成分とする架橋合成高分子である特許請求の範
囲第1項記載の体外循環治療用吸着材。[Scope of Claims] 1. An adsorbent for extracorporeal circulation therapy in which a porous particulate carrier covalently holds a ligand capable of binding to an adsorbed substance, wherein the porous particulate carrier has a hydrophilic cross-linking having a hydroxyl group. Made of organic synthetic polymer,
Water retention capacity is 0.5~6g/g, hydroxyl group density is 5~
When the carrier is in the range of 17 meq/g, the specific surface area of the carrier is at least 5 m 2 /g, and the carrier is filled in a container with a diameter of 10 mm and a length of 50 mm and water is passed through the container, the inlet and outlet of the container are An adsorbent for extracorporeal circulation therapy, characterized in that it is a hard gel carrier with a volume reduction rate of 10% or less under a pressure difference of 200 mmHg. 2. The adsorbent for extracorporeal circulation treatment according to claim 1, wherein the hard gel carrier is a crosslinked synthetic polymer whose main constituent is vinyl alcohol units.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP56110817A JPS5812656A (en) | 1981-07-17 | 1981-07-17 | Adsorbing material for treating recirculation |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP56110817A JPS5812656A (en) | 1981-07-17 | 1981-07-17 | Adsorbing material for treating recirculation |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS5812656A JPS5812656A (en) | 1983-01-24 |
JPH0323182B2 true JPH0323182B2 (en) | 1991-03-28 |
Family
ID=14545406
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP56110817A Granted JPS5812656A (en) | 1981-07-17 | 1981-07-17 | Adsorbing material for treating recirculation |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPS5812656A (en) |
Families Citing this family (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS6077769A (en) * | 1983-10-05 | 1985-05-02 | 鐘淵化学工業株式会社 | Production of adsorbing body |
JPS59102436A (en) * | 1982-12-02 | 1984-06-13 | Kanegafuchi Chem Ind Co Ltd | Adsorbent body |
JPS59196738A (en) * | 1983-04-21 | 1984-11-08 | Kanegafuchi Chem Ind Co Ltd | Adsorbent and preparation thereof |
JPS59139937A (en) * | 1983-01-28 | 1984-08-11 | Asahi Chem Ind Co Ltd | Adsorbent for lipoprotein with low specific gravity |
JPS63115572A (en) * | 1986-10-31 | 1988-05-20 | 鐘淵化学工業株式会社 | Globular particle for direct blood infusion |
JPH01280469A (en) * | 1989-03-10 | 1989-11-10 | Kanegafuchi Chem Ind Co Ltd | Absorbent |
US20080154007A1 (en) * | 2004-12-28 | 2008-06-26 | Kaneka Corporation | Cross-Linked Polymer Particle and Manufacturing Method Thereof |
JP5386770B2 (en) * | 2005-11-08 | 2014-01-15 | 株式会社カネカ | Crosslinked polymer particles and method for producing the same |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS534788A (en) * | 1976-07-02 | 1978-01-17 | Tomita Pharma | Improved adsorbents |
JPS54131586A (en) * | 1978-04-05 | 1979-10-12 | Asahi Chem Ind Co Ltd | Adsorbent |
-
1981
- 1981-07-17 JP JP56110817A patent/JPS5812656A/en active Granted
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS534788A (en) * | 1976-07-02 | 1978-01-17 | Tomita Pharma | Improved adsorbents |
JPS54131586A (en) * | 1978-04-05 | 1979-10-12 | Asahi Chem Ind Co Ltd | Adsorbent |
Also Published As
Publication number | Publication date |
---|---|
JPS5812656A (en) | 1983-01-24 |
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