KR0158669B1 - 투입된 원위치에서 형성되는 생분해성 이식조직 - Google Patents
투입된 원위치에서 형성되는 생분해성 이식조직 Download PDFInfo
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- KR0158669B1 KR0158669B1 KR1019900701183A KR900701183A KR0158669B1 KR 0158669 B1 KR0158669 B1 KR 0158669B1 KR 1019900701183 A KR1019900701183 A KR 1019900701183A KR 900701183 A KR900701183 A KR 900701183A KR 0158669 B1 KR0158669 B1 KR 0158669B1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/0012—Galenical forms characterised by the site of application
- A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
- A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- Health & Medical Sciences (AREA)
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- General Health & Medical Sciences (AREA)
- Epidemiology (AREA)
- Engineering & Computer Science (AREA)
- Medicinal Chemistry (AREA)
- Materials Engineering (AREA)
- Dermatology (AREA)
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- Chemical Kinetics & Catalysis (AREA)
- Surgery (AREA)
- Biomedical Technology (AREA)
- Pharmacology & Pharmacy (AREA)
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- Inorganic Chemistry (AREA)
- Molecular Biology (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Materials For Medical Uses (AREA)
- Medicinal Preparation (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Polysaccharides And Polysaccharide Derivatives (AREA)
- Preparation Of Compounds By Using Micro-Organisms (AREA)
- Polyesters Or Polycarbonates (AREA)
- Prostheses (AREA)
- Medicines That Contain Protein Lipid Enzymes And Other Medicines (AREA)
Abstract
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Description
[발명의 명칭]
투입된 원위치에서 형성되는 생분해성 이식조직
[발명의 상세한 설명]
[기술분야]
본 발명은 생분해성 중합체를 제조하기 위한 방법 및 조성물에 관한 것으로서, 보다 상세하게는 그러한 중합체를 주사될 수 있고 투입된 원위치에서 형성되며 고형인 생분해성 이식조직을 제공하는데 사용되는 방법에 관한 것이다.
[배경기술]
생분해성 중합체는 수년간 봉합재, 외과용 클립, 스태플, 이식조직 및 약물운반시스템 등 의약용도에 이용되어 왔다. 이러한 생분해성 중합체는 대부분 클리콜리드, 락티드, ε-카프로락톤 및 그의 공중합체를 기제로 한 열가소성 물질로, 그 대표적인 예로서는 Schmitt의 미합중국 특허 제3,297,033호에 설명되어 있는 폴리글리콜리드 봉합재와, Schneider의 미합중국 특허 제3,636,956호에 설명되어 있는 폴리(L-락티드-코-글리콜리드) 봉합재, Kaplan등의 미합중국 특허 4,523,591호에 설명되어 있는 폴리(L-락티드-코-글리콜리드) 외과용 클립과 스태플, 및 Boswell등의 미합중국 특허 제3,773,919호와 Yolles의 미합중국 특허 제3,887,699호, Schmitt의 미합중국 특허 제4,155,992호, Pitt등의 미합중국 특허 제4,379,138호, Shalaby등의 미합중국 특허 제4,130,639호 및 제4,186,189호에 설명되어 있는 약물-운반시스템 등이 있다.
상기 특허들에 설명되어 있는 생분해성 중합체는 모두가 열가소성 물질로서, 가열하여 섬유, 클립, 스태플, 핀, 필름 등과 같은 다양한 모양으로 형성될 수 있다. 이들 중합체는 융점이상의 온도로 가열되었을 때만이 액체가 되며, 정상조건에서 이용되는 동안에는 고체로 존재한다.
열경화되는 생분해성 중합체 또한 의약용도에 이용되어 왔다. 이들 중합체는 가교결합반응에 의해 형성되어, 고온에서도 용융되지 않거나 유동될 수 있는 액체를 형성하지 않는 고분자량의 물질이 된다. 이들 물질의 대표적인 예로는, Hostettler의 미합중국 특허 제2,933,477호 및 Hostettler등의 미합중국 특허 제3,186,971호에 설명되어 있는 가교결합된 폴리우레탄이 있으며, ε-카프로락톤과 L-락티드 또는 DL-락티드를 기제로 하고 페록시드 개시제를 통해 가교결합된 공중합체가 Sinclair의 미합중국 특허 제4,045,418호 및 제4,057,537호에 설명되어 있고, Pitt 등의 미합중국 특허 제4,379,138호에는 비스락톤을 단량체 원료로 조합하여 제조되어진 가교결합된 카프로락톤 공중합체가 설명되어 있다. 또한, Pitt 등의 J. Polym. Sci.:Part A:Poly Chem. 25:955-966; 1987에 설명된 바에 따르면, 트리히드록시-관능의 ε-카프로락톤과 ε-발레로락톤의 공중합체를 디이소시아네이트로 가교결합시켜서 생분해성 중합체를 제공하였다. 이들 중합체 역시 가교결합되고 경화되었을 때 교체로 존재한다.
상기 2부류의 생분해성 중합체는 많은 생체의약 용도에 유용하게 사용되어 왔으나, 인간, 포유류, 조류, 어류 및 파충류의 체내로 정의되는 체내에 이용되는 데에는 일부 제한이 따랐다. 즉, 이들 중합체는 고형이기 때문에 이들을 이용할 때에는 항상 먼저 체외에서 중합체 구조물을 형성한 후에 그러한 고형의 구조물을 체내로 삽입해야만 하였다. 예를 들면, 봉합재, 클립 및 스태플은 모두 사용하기 이전에 열가소성의 생분해성 중합체로부터 형성된다. 이들은 체내에 삽입되었을 때 유동되어 그들을 가장 필요로 하는 공극이나 강(腔)을 채우기 보다는 그들의 원래 형태를 유지한다.
이와 마찬가지로, 상기와 같은 생분해성 중합체를 이용하는 약물-운반 시스템도 체외에서 형성되어져야만 한다. 이 경우, 약물을 중합체에 조합하여 그 혼합물을 이식용의 실린더, 디스크 또는 섬유와 같은 임의의 형태로 성형한다.
그러한 고형의 이식조직과 약물-운반 시스템은 절개를 통해서만이 체내로 삽입될 수 있다. 이러한 절개부위는 종종 의료상 요구되는 것보다 넓어질 수 있는데, 이는 환자가 이식조직이나 약물운반시스템을 사용하는 것을 꺼리게 한다.
절개를 피하기 위해서는, 이들 중합체를 소립자, 미세구, 스피어, 마이크로캡슐 등으로 만들어 주사하는 방법밖에는 없다. 이들은 체내로 분비될 수 있는 약물을 포함하거나 포함하지 않을 수 있다. 이들 소립자들은 주사기를 통해 체내로 주사할 수는 있지만, 생분해성 이식조직으로서의 요건은 항상 만족시키지 못한다. 즉, 이들은 입자이기 때문에, 연속적인 필름이나 인공조직으로서 요구되는 구조적 통합성을 갖는 고형의 이식조직을 형성할 수 없으며, 이들 소립자나 미세구 또는 마이크로캡슐을 구강, 치은낭, 안구 또는 초막과 같이 유체의 흐름이 있는 임의의 체강에 삽입할 경우에는 그들의 작은 크기와 불연속적인 성질 때문에 거의 유지되지 못한다. 또한, 상기 중합체로부터 제조되며 체내로 분비되어질 약물을 함유하는 미세구 또는 마이크로캡슐은 때때로 대량 생산하기 어렵고, 그들의 저장 및 주사특성에도 문제가 있다. 더우기, 마이크로캡슐 또는 소립자 시스템은 광대한 외과적인 처치를 하기 전에는 그들의 회수가 어렵다는데 가장 큰 단점이 있는 바, 주사 후 부작용이 있을 경우에 이들은 고형의 이식조직에 비해 체내로부터 제거하기가 매우 어렵다.
따라서, 상기 문제점이 극복된 생분해성 중합체 구조를 제공하는 방법 및 조성물이 요구되었다.
또한, 인공기관 및/또는 조절성 운반시스템으로 이용될 수 있는 것으로서 주사가능하며 투입된 위치에서 형성되고 고형인 생분해성 이식조직을 제공하는 방법과 조성물이 요구되었다.
더우기, 연질 및 경질 조직모두에 사용될 수 있도록 부드러운 것으로부터 딱딱한 것에 이르기까지의 넓은 범위의 성질을 갖는 이식조직을 제공할 수 있는 방법 및 조성물이 요구되었다.
[발명의 개시]
본 발명은 액체상태로, 예컨대 주사기 또는 바늘을 통해 투여되며 투여된 후 단시간 내에 응고 및 경화되어 고형이 될 수 있는, 보결(補缺) 이식조직 및 조절성 분비, 약물-운반 시스템에 사용되는 생분해성 중합체의 제조와 그의 사용방법에 관한 것이다. 이식조직은 열경화성 및 열가소성의 2가지 형태의 중합체 시스템으로 이루어진 생분해성 중합체 및 공중합체로 만들어지기 때문에 생분해성이다.
열가소성 시스템은, 고형이며 직쇄인 생분해성 중합체 또는 공중합체를 비독성이며 물과 혼화될 수 있는 용매에 용해시켜서 액상의 용액을 형성함으로써 제공된다. 이 중합체 용액이 수분이 충분히 존재하는 체내에 투입되었을 때, 용매는 중합체로부터 소산 및 확산되고 남아 있는 중합체는 고형의 구조로 응고 및 고화된다. 이들 용액은 근육 또는 지방과 같은 연질의 조직이나, 벼와 같은 경질 조직, 치근막, 구강, 질, 직강, 비강과 같은 강, 혹은 치은낭, 결막과 같은 망상공동 등을 포함한 체내의 어디에나 투입될 수 있다. 약물-운반 시스템의 경우, 생물학적 활성 성분을 그가 용해될 수 있는 중합체 용액에 첨가하여 균질의 용액을 형성하거나 약물을 중합체 용액에 분산시켜 현탁액 또는 분산액을 형성함으로써 제공된다. 이러한 중합체 용액이 체액이나 물에 노출되면, 중합체-약물 혼합물로부터 용매가 소산되고 중합체가 응고되면서 물이 혼합물로 확산되게 되며, 이로써 이식조직이 고화되면서 약물이 중합체 매트릭스에 싸여 포괄되거나 마이크로캡슐화된다. 그후, 약물은 약물이 중합체 매트릭스로부터 확산 및 용해되는 일반적인 과정에 따라 분비된다.
또한, 본 발명의 또 다른 구현에는, 생분해될 수 있으며 투입된 원위치에서 형성 및 경화될 수 있는 가교결합 가능한 중합체를 합성시킴으로써 열경화성 시스템을 제공한다. 그러한 열경화성 시스템은 용매를 포함하지 않으며 반응성이고 액상이며, 올리고머 수준의 중합체로 이루어진 것으로서 투입위치에서 경화되어 고형을 형성하며, 일반적으로는 경화촉매가 첨가된다.
열경화성 시스템에 이용되는 다관능성 중합체는 먼저 DL-락티드 또는 ε-카프로락톤을 다관능성 폴리올을 개시제 및 촉매를 이용하여 공중합 반응시켜서 폴리올-말단 예비중합체를 형성함으로써 합성된다. 그 다음, 폴리올-말단 예비중합체는, 바람직하게는 Schotten-Baumann방법에 의해 알코올 말단을 아크릴로일 클로라이드로 아크릴화시키는 반응, 즉 아크릴 할라이드를 알코올과 반응시키는 것에 의해 아크릴산 에스테르-말단의 예비중합체로 전환된다. 아크릴산 에스테르 예비중합체는 그 밖에 다양한 방법에 의해서도 합성될 수 있는 바, 카복실산(즉, 아크릴 또는 메트아크릴산)과 알코올과의 반응, 카복실산 에스테르(즉, 메틸아크릴레이트 또는 메틸메트아크릴레이트)와 알코올과의 에스테르전이반응, 및 이소시아네이토알킬아크릴레이트(즉, 이소시아네이토에틸 메트아크릴레이트)와 알코올과의 반응에 의해 합성될 수 있다.
액상의 아크릴산-말단 예비중합체는, 바람직하게는 벤조일 페록시드 또는 아조비스이소부티로니트릴을 첨가하여 보다 고화된 구조로 경화시킬 수 있다. 따라서, 이들 가교결합 가능한 중합체를 이용하는 이식조직의 경우, 액상의 아크릴산-종료 예비중합체를 체내로 주사하기 직전에 촉매를 첨가시키게 되면, 충분한 분자량이 얻어질 때까지 가교결합반응이 진행되어 중합체가 고화되게 될 것이다. 주사 후 액상의 예비중합체는 투입하고자 하는 위치의 강 또는 공간으로 유동하며 고화될 때 형태를 갖게될 것이다. 이러한 시스템을 이용하여 약물을 운반하는 경우, 생물학적 활성성분은 액상의 중합체 시스템이 촉매화되지 않은 상태에서 첨가한다.
열가소성 및 열경화성 시스템 모두 액상으로 이용하는데 있어서의 잇점을 갖는다. 예컨대, 중합체가 액상을 유지하는 동안 주사기 및 바늘을 통해 체내로 주사될 수 있으며, 그 위치에서 잔류되어 고형의 생분해성 이식조직을 형성할 수 있다. 따라서, 절개가 불필요하며 이식조직은 그 강의 형태를 취하게 된다. 더우기, 주사전에 액체에 생물학적 활성성분을 첨가하게 되면 약물-운반 부형제가 제공될 수 있으며, 이렇게 형성된 이식조직은 체내에서 활성성분을 분비하면서 생분해된다. 여기서, 생물학적 활성성분은 체내에 효과를 나타낼 수 있는 약물 또는 기타 다른 물질을 의미한다.
그러므로, 본 발명의 목적은, 생분해성 중합체를 형성하는 방법 및 조성물을 제공하는데 있다.
또한, 본 발명의 목적은 주사될 수 있으며 투입된 원위치에서 형성되고 고형인 생분해성 이식조직을 형성하는데 유용한 중합체를 제공하는데 있다.
또한, 본 발명의 목적은 생물학적 활성 물질의 분비가 조절되는 운반 시스템으로 이용될 수 있는 이식조직을 제공하는데 있다.
그리고, 본 발명의 목적은 연질 및 경질 조직 모두에 사용될 수 있도록 연질이며 탄력성있는 것으로부터 경질이고 딱딱한 것에 이르기까지 광범위한 성질의 이식조직을 제공하는데 있다.
[도면의 간단한 설명]
제1도는 아크릴레이트-말단 예비중합체의 합성과 그에 이은 자유라디칼의 가교결합을 도시한 것이고,
제2도는 디올로 개시된 ε-카프로락톤과 L-락티드와의 공중합 반응과 그로 인한 랜덤 공중합체의 구조를 도시한 것이며,
표 1은 합성된 2관능성의 PLC 예비중합체들을 요약한 것이고,
표 2는 합성된 아크릴산 에스테르 말단의 예비중합체들을 요약한 것이며,
표 3은 경화연구를 요약한 것이다.
[발명의 실시하기 위한 최선의 형태]
본 발명은 투입된 원위치에서 형성되는 생분해성 이식조직과 그를 제조하는 방법에 관한 것이다. 또한, 본 발명은 체내에 주사되어 투입된 원위치에서 고화되며 생물학적 활성성분이 조절된 속도로 분비될 수 있는 액상의 생분해성 중합체로 이루어진 운반시스템에 관한 것이다. 생분해성 중합체 시스템에는, 생적합성 용매에 용해되어 있는 열가소성 중합체와 용매없이 액상으로 존재하는 열경화성 중합체로서 구분되는 2가지 형태가 있다.
A. 열가소성 시스템
열가소성 시스템은 고형이며 직쇄의 생분해성 중합체를 생적합성 용매에 용해시켜 액체를 형성함으로써 제공되며, 이들은 주사기 및 바늘을 통해 투여될 수 있다. 여기에 적용될 수 있는 중합체로는, 예컨대, 폴리락티드, 폴리글리콜리드, 폴리카프로락톤, 폴리디옥사논, 폴리카보네이트, 폴리히드록시부티레이트, 폴리알킬렌록살레이트, 폴리안하이드라이드, 폴리아미드, 폴리에스테르아미드, 폴리우레탄, 폴리아세테이트, 폴리케탈, 폴리오르토카보네이트, 폴리포스파젠, 폴리히드록시발러레이트, 폴리알킬렌석시네이트, 폴리(말산), 폴리(아미노산), 폴리비닐피롤리돈, 폴리에틸렌 글리콜, 폴리히드록시 셀룰로스, 키틴, 키토산 및 폴리오르토 에스테르와, 그의 공중합체, 삼량체, 및 그의 조합물 또는 혼합물 등이 있다. 이들중에서도 결정화도가 보다 낮고 보다 소수성인 중합체가 바람직한데, 이는 이러한 중합체 및 공중합체가 고도의 수소-결합을 갖는 폴리글리콜리드 및 키틴 등의 고결정성 중합체에 비해 생적합성 용매에 보다 잘 용해되기 때문이다. 적절한 용해 변수를 갖는 바람직한 물질로는 보다 무정형이어서 용해성이 우수한 폴리락티드, 폴리카프로락톤 및 이들과 글리콜리드와의 공중합체가 있다.
한편, 생분해성 중합체를 위한 용매는 비독성이며 물과 혼화될 수 있을 뿐만 아니라 생적합성인 것이 바람직하다. 독성을 갖는 용매는 생체내로 어떤 물질을 주사하는데에도 사용해서는 안된다. 또한 용매는 이식부위에서 조직의 자극 또는 괴사가 발생되지 않도록 생적합성을 갖아야만 한다. 그리고, 용매는 체내로 빠르게 분산되고 물이 중합체 용액으로 침투될 수 있어서 응고 및 고화가 일어날 수 있도록 물과 혼화될 수 있어야 한다. 그러한 용매의 예로는 N-메틸-2-피롤리돈, 2-피롤리돈, 에탄올, 프로필렌 글리콜, 아세톤, 에틸아세테이트, 메틸아세테이트, 메틸에틸케톤, 디메틸포름아미드, 디메틸설폭시드, 테트라히드로퓨란, 카프로락탐, 데실메틸설폭시드, 올레인산 및 1-도데실아자사이클로헵탄-2-온등이 있으며, 그들의 용매화 능력과 생적합성을 고려할 때 N-메틸-2-필로리돈, 2-피롤리돈, 디메틸설폭시드 및 아세톤이 바람직하다.
다양한 용매에서 생분해성 중합체의 용해성은 그의 결정성, 친수성, 수소결합 및 분자량에 따라 차이가 있을 것이다. 그러므로, 모든 생분해성 중합체가 동일한 용매에 용해되지는 않을 것인 바, 각 중합체 또는 공중합체에 따라 최적의 용매를 선택하여야 한다. 저분자량의 중합체는 고분자량의 중합체보다 일반적으로 용매에 쉽게 용해될 것이다. 따라서, 다양한 용매에 용해된 중합체의 농도는 중합체의 형태와 그 분자량에 따라 다를 것이다. 반대로, 고분자량의 중합체는 저분자량의 중합체에 비해 일반적으로 빠르게 응고 및 고화될 것이며, 또한 고분자량의 중합체는 저분자량의 중합체보다 높은 용액점도를 나타낼 것이다. 그러므로, 최적의 주사효과를 나타내기 위해서는, 용매중에서의 중합체의 분자량과 농도를 조절하여야 한다.
예컨대, 락트산을 축합시켜서 형성된 저분자량의 폴리락트산은 N-메틸-2-피롤리돈(NMP)에 용해시켜서 73중량%의 용액으로 만들어야, 23-게이지의 주사바늘을 통해 쉽게 유입시킬 수 있을 것이다. 반면, DL-락티드를 부가 중합반응시켜서 형성된 고분자량의 폴리(DL-락티드)(DL-PLA)는 NMP에 50중량%만 용해시켰을 때 상기와 동일한 점도를 얻을 수 있다. 이러한 고분자량의 중합체 용액은 물에 투입했을 때 즉시 응고되는 반면, 저분자량의 중합체 용액은 보다 농축되었다 할지라도 물에 투입되었을 때 매우 느린 속도로 응고된다.
느리게 응고되는 경향의 중합체는, 혼합용매를 사용함으로써 응고속도를 향상시킬 수 있다. 즉, 혼합용매중 하나의 액상성분은 중합체를 잘 용해시키는 것으로 하고 나머지 하나는 난용해성 또는 불용해성의 것으로 하며, 두 액상성분의 비율을 중합체를 용해시키되 생리환경에서 물과 같은 불용해성 용매가 극소량 증가하여도 중합체를 침전시키는 정도가 되게 한다. 그리고, 필수적으로 용매시스템은 물과 중합체 모두와 혼화될 수 있어야 한다. 그러한 2성분의 용매 시스템으로는 저분자량의 DL-PLA를 위한 것으로서 NMP와 에탄올을 이용한 것을 예로 들 수 있다. 이처럼, NMP/중합체 용액에 에탄올을 첨가하게 되면 응고속도가 매우 향상된다.
본 발명자들은, 때때로 고분자량 중합체가 매우 높은 농도로 함유된 용액의 경우 보다 희석된 용액에서 보다 느리게 응고 및 고화된다는 것을 발견하였다. 이는, 고농도의 중합체가 중합체 매트릭스내로부터 용매가 확산되는 것을 방지하여 결과적으로 중합체를 침전시킬 수 있도록 매트릭스 내로 물이 침투하는 것을 막게 되기 때문인 것으로 추측되는 바, 용매가 중합체 용액으로부터 확산되고 중합체내로 물이 침투되어 응고될 수 있는 적정농도로 하여야 한다.
열가소성 시스템의 기대되는 용도의 하나는, 중합체 용액을 주사기에 채워 바늘을 통해 체내로 주입하는 것이다. 중합체 용액이 투입된 후에 용매는 소산되고 잔류된 중합체는 고화되어 고형구조를 형성한다. 이때, 이식조직은 기계적인 힘에 의해 그 주위의 조직 또는 뼈에 부착될 것이며, 그 주위를 둘러싸고 있는 강(腔)형태를 취할 수 있다. 따라서, 생분해성 중합체 용액은 콜라겐 같이 피부하로 주사되어 조직을 형성하고 손상부위를 채울 수 있으며, 또한 화상과 같은 상처에 주사되어 반흔이 깊어지는 것을 막을 수 있다. 이러한 이식조직은, 콜라겐과는 달리, 선택된 중합체의 종류와 그 분자량에 따라 분해시간을 몇주로부터 몇 년에 이르기까지 다양하게 할 수 있다. 또한 주사될 수 있는 중합체 용액은, 히드록시아파타이트 플러그와 같은 다른 고형의 생분해성 이식조직을 뼈의 틈을 사이에 주입했을 경우에는, 뼈의 손상부위를 보완해 주거나 혹은 연속적인 매트릭스를 제공하는데 사용될 수 있다. 이들 주사될 수 있는 시스템은 그의 기계적 결합특성으로 인해 조직과 조직 또는 다른 이식조직을 접착시키거나 조직 및 인공기관을 캡슐로 싸는데 사용할 수 있다.
열가소성 시스템의 기대되는 또 다른 용도는 약물-운반 시스템을 제공하는 것이다. 이 경우, 주사전에 중합체 용액에 생체활성물질을 첨가한 후에 중합체/용매/활성물질의 혼합물을 체내로 주사한다. 이때 약물이 용매에 가용성이면 약물과 중합체와의 균질한 용액을 형성하여 이를 주사용할 수 있을 것이며, 약물이 용매에 잘 용해되지 않으면 약물이 중합체 용액중에 분산 또는 현탁된 현탁액 및 분산액을 체내로 주사할 수도 있다. 이러한 양자 모두에서, 용매는 소산되고 중합체는 고화되어 고형의 매트릭스내의 약물을 포괄하게 될 것이다. 약물은 이러한 고형의 이식조직으로부터 분비될 때 단일성 중합체 부품으로부터 약물을 분비하는데 있어서의 일반적인 과정에 따른다. 약물의 분비는 이식조직의 크기 및 형태와, 이식조직에 약물을 충전하는 방법, 약물 및 특정 중합체를 포함한 침투요인, 중합체의 분해 등에 영향을 받는다. 이 분야에 숙련된 자들은 운반시키고자 하는 생체활성물질에 따라 목적하는 분비속도 및 기간을 갖도록 상기 변수를 조정할 수 있을 것이다.
여기서 사용된 약물 또는 생체활성물질(생물학적 활성물질)이라는 용어는, 체내에서 국부적 또는 전신에 작용하는 생리학적 또는 약제학적으로 활성을 갖는 물질이면 모두가 포함된다. 주사될 수 있고 투입된 원위치에서 형성되는 고형의 이식조직 시스템에 사용되는 약물 및 생물학적 활성물질의 대표적인 예로는, 펩타이드제, 단백질제, 제감작제, 항원, 왁찐, 항감염제, 항생제, 살균제, 항알레르기제, 스테로이드성 소염제, 충혈제거제, 축동제, 항콜린제, 교감신경흥분제, 진정제, 혈압저하제, 향신경제, 배란제, 체액성제, 프로스타글란딘, 진통제, 진경제, 항말라리아제, 항히스타민제, 강심제, 비스테로이드성 소염제, 항파킨슨제, 혈압강하제, β-아드레날린 차단제, 영양제 및 벤조페난트리딘 알카로이드 등이 있다. 이 분야에 숙련된 자들에게는, 수용성 환경에서 분비될 수 있는 상기 이외의 약물 및 생물학적 활성물질도 목적하는 주사가능한 운반시스템에 이용될 수 있다. 또한, 다양한 형태의 약물 또는 생물학적 활성물질이 이용될 수 있는 바, 체내에 주사되었을 때 생물학적으로 활성화되는 비하전성 분자, 분자복합체, 염, 에스테르 등과 같은 형태도 포함된다. 주사가능하고 투입된 위치에서 고형이 되는 이식조직에 조합되는 약물 또는 생물학적 유효성분의 양은 목적하는 분비형태와 생물학적인 효과를 나타내는데 요구되는 약물의 농도 및 약물을 방출하여야 할 치료기간에 따라 결정된다. 중합체 용액에 조합되는 약물의 양의 상한선은 수용체 용액 또는 분산액의 점도가 주사바늘을 통해 주사될 수 있는 정도이면 제한이 없으며, 또한 운반 시스템에 조합되는 약물의 양의 하한선은 단순히 약물의 활성과 치료기간에 따른다.
상기 모든 경우에서, 주사될 수 있는 중합체 용액으로부터 형성된 고형의 이식조직은 체내에서 느리게 생분해되어 이들이 소멸되면서 천연조직이 성장 및 대체되도록 할 것이다. 그러므로, 연질 조직의 손상부위에 주사할 경우, 손상부를 채우고 골격을 제공하여 천연 콜라겐 조직이 성장되도록 할 것이며, 이러한 콜라겐 조직은 점차 생분해성 중합체를 대체하게 될 것이다. 뼈와 같은 경질의 조직에 사용될 경우, 생분해성 중합체는 새로운 골세포의 성장을 지지할 것이며, 이들 새로운 골세포는 점차 분해된 중합체를 대체하게 될 것이다. 약물-운반 시스템의 경우, 주사될 수 있는 시스템으로부터 형성된 고형의 이식조직은 그 매트릭스에 포함된 약물을 그 약물이 고갈될 때까지 조절된 속도로 분비할 것이다.
이때, 일부 약물의 경우 중합체를 약물이 완전히 분비된 후에 분해되도록 할 수 있으며, 펩티드나 단백질 등의 또 다른 약물의 경우에는 중합체에 비-확산약물이 체액에 노출될 때까지 분해된 후에 완전히 분비되도록 할 수 있다.
B. 열경화성 시스템
주사가능하며, 투입된 위치에서 형성되고 생분해성인 이식조직은 적당히 관능화된 생분해성 중합체를 가교결합시킴으로써 제조될 수도 있다. 열경화성 시스템은 반응성이고 액상이며, 올리고머 수준의 중합체로 이루어진 것으로, 경화되어 고체가 되며, 일반적으로 경화촉매가 첨가된다. 중합체로는 앞서 열가소성 시스템에서 설명한 생분해성 중합체중 어느 것이나 사용될 수 있으나, 이들 중합체 또는 공중합체중에서 저분자량의 올리고머는 액상이어야 하며 예비중합체의 말단에 관능기를 갖고 있어서 아크릴로일 클로라이드와 반응하여 아크릴산 에스테르 말단의 예비중합체를 형성할 수 있어야 하는 제한이 있다.
바람직한 생분해성 시스템은, 폴리(DL-락티드-코-카프로락톤) 또는 DL-PLC로부터 제조된 것이다. 이러한 물질로부터 제조된 저분자량의 중합체 또는 올리고머는 실온에서 유동될 수 있는 액상이다. 히드록시-말단의 PLC 예비중합체는 DL-락티드 또는 L-락티드와 ε-카프로락톤을 다관능성 폴리올 개시제 및 촉매로 공중합 반응시켜서 합성될 수 있다. 이러한 예비중합체를 제조하는데 유용한 촉매는 염기성 또는 중성 에스테르 호환(에스테르 전이반응)촉매가 바람직하며, 그러한 촉매로는 포름산, 아세트산, 라우르산, 스테아르산 및 벤조산과 같은 탄소원자수 18이상을 포함하는 카복실산의 금속에스테르가 일반적으로 사용되며, FDA 승인 및 효과를 고려할 때 옥토산주석(stannous octoate)과 염화제일주석이 특히 바람직하다.
2관능성 폴리에스테르가 요구되는 경우 에틸렌 글리콜과 같은 2관능성 쇄-개시제가 사용되며, 트리메틸올프로판과 같은 3관능성 개시제는 3관능성 중합체를 제조하는데 사용된다. 이들 쇄-개시제의 사용량은 그 결과로 얻고자 하는 중합체 또는 공중합체의 분자량에 따라 결정된다. 쇄-개시제가 고농도로 존재할 때 하나의 2관능성 개시제는 단지 하나의 중합체 쇄만을 개시하는 한편, 2관능성 개시제의 농도가 매우 낮을 경우에는 각 개시제는 2개의 중합체쇄를 개시시킬 수 있다. 어느 경우에나, 제1도에 나타낸 바와 같이 중합체는 히드록시기 말단을 갖는다. 이러한 예에서, 2관능성 개시제 분자당 단지 하나의 중합체 쇄만이 개시되는 것으로 추측되는데, 이러한 추측은 예비중합체에 대한 분자량의 이론 값을 산출할 수 있도록 한다.
합성된 2관능성 PLC 예비중합체의 목록을 다음의 표 1에 나타내었다. 이때 그 관능성 PLC 예비중합체의 합성을 다음과 같이 수행하였다. 적당량의 DL-락티드, ε-카프로락톤 및 에틸렌 글리콜을 질소하의 플라스크중에서 조합하고 유조에서 155℃로 가열하여 단량체를 용융 훈련한 다음, 0.03 내지 0.05중량%의 SnCl2를 첨가하여 촉매시켜서 공중합반응을 밤새도록 수행하였다. 예비중합체의 히드록실 수는 표준 적정법에 의해 결정하였으며, 액상 예비중합체의 가드너-홀트 점도는 ASTM D 1545 방법에 따라 측정하였다. 최고 분자량의 예비중합체(MW=5000)는 실온에서도 고형이었으므로 그의 가드너 홀트 점도를 측정할 수 없었다.
디올 예비중합체는, 제2도에 나타낸 바와 같이 Schotten-Baumann 조건하에서 아크릴로일 클로라이드와 반응시켜서 아크릴산 에스테르-말단 예비중합체로 전환시키며, 이를 다음의 표 2에 요약하였다. 디올 예비중합체를 아크릴산 에스테르-말단의 예비중합체로 전환시키기 위하여 그 밖의 다른 방법도 사용될 수 있다.
TMF 및 디클로로메탄 모두가 아크릴화 반응의 용매로서 유용하다. TMF를 용매로 사용하였을 때 몇몇 문제가 있는 바, 반응의 부생성물로서 형성된 트리에틸아민 히드로클로라이드는 미세하게 분배되어 반응혼합물을 여과시키는 것에 의해서는 효과적으로 제거시킬 수 없다. 트리에틸아민 히드로클로라이드(Et3N·HCl)는 아크릴류의 중합반응을 유발한다고 보고된 바 있다(미합중국 특허 제4,405,798). 몇몇의 경우, Et3N·HCl을 전부 제거하는데 실패하였을 때 아크릴산 에스테르-말단의 예비중합체는 보다 일찍 겔화되었다. 따라서 Et3N·HCl 전부를 효과적으로 제거하기 위해서는, 예비중합체를 물로 추출하는 것이 필요하다. 반응을 THF에서 수행하는 경우에는, 먼저 THF를 진공에서 증발시키고 CH2Cl2층을 물로 추출하는데, 때때로 이렇게 추출하는 동안 안정한 유화액이 되었다. 아크릴화 반응은 이후에 THF 대신 CH2Cl2에서 수행하였다. 본 발명자들은 이러한 용매를 사용하면 반응혼합물로부터 Et3N·HCl을 여과해 내기가 보다 용이함을 발견하였으며, 여과 후 유기 분획을 물로 직접 추출할 수 있었다.
디올 및 아크릴산 예비중합체 모두를 IR 및1H NMR 스펙트로스코피하여 시험하였다. 디올 예비중합체에 대한 IR 스펙트럼의 특징은 약 3510cm-1에서 돌출된 O-H 스트레치를 갖는데 있다. 아크릴화 반응에서, O-H 스트레치의 정도는 현저히 감소되며, 약 1640cm-1에서 새로운 흡수가 나타났는데, 이 새로운 흡수는 아크릴기와 관련된 C-C 스트레치로 인한 것이다. 마찬가지로, 아크릴 에스테르기의 존재는1H NMR 스펙트라에, 5.9 내지 6.9ppm의 범위에서 비닐 프로톤에 대한 특징적인 공명을 나타내었다.
그런 다음, 아크릴 예비중합체와 다음 예비중합체를 표 3에 요약한 바와 같이 경화시켰다. 예비중합체를 경화시키는 일반적인 방법은 다음과 같은 바, 작은 비이커에 담겨 있는 5.0g의 아크릴산 예비중합체에 약 1㎖의 CH2Cl2에 벤조일페록시드(BP)를 용해시켜서 된 용액을 첨가시켰다. 일부의 경우, 예비중합체를 BP용액에 투입하기 전에 부형제 또는 부가적인 아크릴 단량체를 첨가시켰다. 이 혼합물을 교반시킨 후 페리접시에 붇고, 이 접시를 예열된 진공오븐에서 경화시켰다. 샘플의 일부는 진공이 아닌 공기중에서 경화시켰다. 이들 샘플을 다음의 표 3에 나타내었다.
이러한 열경화성 시스템은 생분해성 이식조직이 요구되는 어느 곳에나 이용될 수 있다. 예컨대, 예비중합체는 경화제를 첨가한 후 짧은 시간동안 액상으로 존재하기 때문에, 액상 예비중합체/경화제 혼합물은 주사기를 통해 체내에 주사될 수 있다. 그런 다음, 혼합물은 투입된 원위치에서 교화되므로 이식조직을 제공하기 위해 절개할 필요가 없다. 또한, 약물-운반 시스템은 예비중합체를 주사하기 전에 생물학적 활성성분을 첨가함으로써 제공될 수 있다. 이때, 시스템은 투입된 원위치에서 경화되어 고형이 될 것이며, 결국 생분해되어 약물을 점차 분비하게 될 것이다.
[실시예에 대한 상세한 설명]
본 발명을 다음의 실시예를 통해 예시하였다. 다음의 실시예는 본 발명의 범위를 한정하는 것이 아닌 바 이들 이외의 다른 동등한 구현예가 존재할 수 있음이 본 명세서와 도면 및 첨부된 청구범위에 의해 명백해질 것이다.
[실시예 1]
폴리(DL-락트산)은 락트산을 간단히 다중축합반응시켜 제조하였다. 촉매는 사용하지 않았으며 반응시간을 다양하게 하여 이론상 서로 다른 분자량을 갖는 중합체들을 합성하였다. 이러한 고분자들을 DL-PLA 올리고머로 표시하였다. 다량의 고형 올리고머를 NMP에 용해시 중합체와 용매의 비가 68:32가 되게 하였다. 살균물 활성, 특히 충치균에 대해 활성을 갖는 벤조페난트리딘 알카로이드, SaCl(생귀나린 클로라이드)을 중합체 용액에 첨가하여 총혼합액중에 약물이 2중량% 함유된 분산액이 되게 하였다. 분산액과 중합체 용액을 바늘이 없는 살균처리한 주사기로 투석튜브(직경 11.5mm)에 주사한 후, 약물과 중합체의 혼합 용액의 손실을 막기 위해 6인치 길이의 투석튜브 끝을 묶고 주사된 물질이 담겨진 튜브를 37℃를 유지하면서 pH 7의 소렌슨 완충액에서 방치하였다. 수용체 용액에 액침하였을 때, 약물/중합체 덩어리는 단단하게 응고되었으나 약물은 수용체 용액에서 주황색을 나타내면서 중합체로부터 분리되었다. 투석튜브에 주사된 용액의 양은 약 250㎖ 또는 고체로 100㎎정도로 하였다. 투석튜브로는 분자차단 계수가 3,500인 것을 선택하였다. 이러한 분자차단계수의 것을 사용하게 되면 중합체에서 분비된 SaCl은 튜브의 벽을 통해서 쉽게 확산되는 반면, 고체성 중합체는 잔류되었다. 약물/중합체 매트릭스를 포함하고 있는 투석튜브를 자주 옮겨서 새로운 수용체 용액에 담아 두었다. 그런 다음, 분비된 약물을 포함하는 사용되었던 수용체 용액을 pH 2.76으로 산성화시켜서, 모든 분비된 약물이 약물의 이미늄 이온형태로 전환시키고, 약물의 농도를 237㎚ 파장에서의 UV 흡광도로 결정하였다. 분비된 약물의 누적질량과 누적분율을 계산하여 시간에 대한 함수로 표시하였다. 첫날내에는 약 60%의 약물이 분비되었으며 2일 후에는 72%, 5일 후에는 85%, 9일 후에는 90%, 14일 후에는 97%가 분비되었다.
[실시예 2]
생귀나린의 에탄올 에스더인 SaEt(에톡시디히드로생귀나린)를 상기 실시예 1에서와 같은 DL-PLA 올리고머/NMP 용액에 첨가하였다. SaEt는 중합체 용액에 용해되어 약물과 중합체의 균질용액이 되었다. 수용체 용액에 약 250㎕의 용액을 첨가하고 상기 실시예 1에서와 같은 방법으로 분비된 약물을 정량하였다. SaEt이 물에 대한 용해도가 낮다는 점에서 예측될 수 있는 바와 같이 SaEt의 분비는 SaCl에서 보다 낮았다. 첫날에는 거의 45%가 분비되었고, 2일 후에는 52%, 5일 후에는 60%, 9일 후에는 70%, 14일 후에는 80%가 유지되었다.
[실시예 3]
라우릴 알코올을 개시제로 하고 SnCl을 촉매로 하여 DL-락티드를 개환 중합반응시켜서 0.08dL/g의 고유점도와 2,000의 이론 분자량을 갖는 폴리(DL-락티드)를 제조하였다. 그런 다음, 이 중합체를 NMP에 40중량%의 중합체 용액이 되게 하고, SaCl을 NMP에 상기 중합체가 용해되어 있는 용액에 1.5%가 되게 분산시키고 분비속도를 상기 실시예 1의 방법으로 정량하였다. 이러한 분자량이 보다 큰 중합체로 부터의 약물의 분비속도는 DL-PLA 올리고머에서 보다 늦는 바, 첫날에는 약 32%가 분비되었고, 2일 후에는 40%, 5일 후에는 45%, 15일 후에는 50%가 분비되었다.
[실시예 4]
상기 실시예 3에서와 동일한 NMP에 DL-PLA 용해시켜서 된 동일 중합체 용액에 SaEt를 첨가하여 약물이 1.5중량%로 함유된 균일한 약물 용액을 얻었다. 약물의 분비속도를 상기 실시예 1에서와 동일한 방법으로 측정한 결과, DL-PLA 올리고머에서 보다 SaEt의 분비가 훨씬 늦었는 바, 첫날에는 약 8%, 2일 후에는 14%, 5일 후에는 20%, 9일 후에는 23%, 14일 후에는 28%가 분비되었다.
[실시예 5]
충전된 약물이 중합체 용액으로부터 약물을 분비하는데 미치는 효과를 40중량% DL-PLA 올리고머를 함유하는 NMP에 SaCl를 첨가함으로써 입증하였다. 약물을 중합체 용액에 2,7,14중량%로 분산시켰다. 상기 실시예 1과 같은 방법을 사용하여 이들 제형으로 부터의 약물의 분비를 측정한 결과 확산분비하는 매트릭스 운반시스템에 충전된 약물 양이 클수록 분비의 분율속도가 낮은 것으로 나타났다. 2%가 충전된 제형에서는 1일 후에는 65%, 2일 후에는 75%, 5일 후에는 88%가 분비되었고, 7%가 충전된 제형에서는 1일 후에는 48% 2일 후에 52%, 5일 후에는 58%가 분비되었으며, 14%가 충전된 제형에서는 1일 후에 38%, 2일 후에는 43%, 5일 후에는 49%가 분비되었다.
[실시예 6]
개시제로서 라우릴 알코올을 사용하고 SaCl를 촉매로서 사용하여 글리코리드와 DL-락티드 혼합액을 개환중합반응시켜서 폴리(DL-락트디-코-글리코리드)를 제조하였다. 이때, 두 단량체의 비율은 최종공중합체(DL-PLG)에서 핵자기 공명분광계로 정량하였을 때 두 단중합체의 비가 50:50이 되도록 조정하였고, 또한 개시제로는 1500달톤의 이론 분자량을 갖는 중합체가 되도록 조정되었다. 그런 다음, 얻어진 공중합체를 NMP에 용해하여 70중량%의 중합체 용액을 얻었다. SaCl을 상기 용액에 첨가하여 약물이 중합체용액에, 2중량%가 함유되도록 하였다.
이 제형으로 부터의 약물의 분비속도를 상기 실시예 1에서와 동일한 방법으로 정량한 결과, 이 공중합체는 DL-PLA 올리고머나 분자량 2000의 DL-PLA에서 보다 분비속도가 낮았는 바, 2일 후에는 약 7%, 5일 후에는 10%, 7일 후에는 12%, 14일 후에는 16%의 약물이 분비되었다.
[실시예 7]
상기 실시예 6에서와 동일한 NMP에 DL-PLG를 용해시켜서 된 중합체 용액에 SaEt를 첨가하여 2중량%의 약물 용액을 얻었다. 이 제형으로 부터의 약물의 분리비속도를 앞에서 언급한 방법으로 정량한 결과, 이 제형으로 부터의 SaEt의 분비속도는 상기 실시예 6에서 설명한 SaCl 분비속도와 동일하였다.
[실시예 8]
상기 실시예 6에서와 동일한 NMP에는 DL-PLG를 용해시켜서 된 용액에 유리염기형의 테트라사이클린(TCB)을 첨가하였다. 약물을 중합체 용액에 완전히 용해하여 2.4중량%의 약물 용액이 되게 하였다. 이 제형으로 부터의 약물의 분비속도를 수용체 용액을 pH 2.76으로 산성화하시키는 것을 제외하고 상기 실시예 1에서와 유사한 방법으로 정량하고, TCB의 농도를 약물에 대한 적절한 파장에서 UV 흡수로 정량하였다. 이 제형에서 TCB의 분비는 매우 선형적이며 동일한 공중합체에서의 SaEt나 SaCl의 분비 보다 더 높은 속도를 내었는 바, 1일 후에는 약 44%의 약물이 분비되었고, 2일 후에는 54%, 5일 후에는 68%, 6일 후에는 78%, 7일 후에는 80%, 9일 후에는 87%, 12일 후에는 96%, 14일 후에는 거의 100%가 분비되었다.
[실시예 9]
상기 실시예 6에서와 동일한 NMP에 DL-PLG를 용해시켜서 된 용액에 테트라사이클린 염산염(TCH)을 첨가하였으며, 이 염형태의 약물을 중합체 용액에 완전히 용해시켰다. 이 제형으로 부터의 약물의 분비속도를 상기 실시예 8에서와 동일하게 측정한 결과, 분비속도가 다소 낮은 것을 제외하고는 유리염기형태와 유사하였는 바, 1일이 지난 후에는 약물이 약 32%가 분비되었고 2일 후에는 40%, 5일 후에는 57%, 6일 후에는 64%, 7일 후에는 75%, 9일 후에는 82%, 12일 후에는 92%, 14일 후에는 약 100%가 분비되었다.
[실시예 10]
0.26DL/g의 고유점도와 약 10,000달톤의 이론 분자량을 가진 DL-PLA는 라우릴 알코올을 개시제로 하고 SnCl을 촉매로 하여 DL-락티드의 재환 중합반응에 의해 제조되었다. NMP에 중합체를 녹여 중량비로 50% 중합체 용액이 되게 하였다. 다량 (100㎕)의 중합체 용액을 토끼의 피부하에 주사하고 USP 음성 소성제의 조직반응과 비교하였다. 드레이즈 법에 따라 주사 후 즉히, 주사 후 1시간과 6시간, 7일, 14일, 21일에 희생되어질 때까지 매일 한 번씩 국소자극에 대한 시험부위의 징후를 측정하였다. 시험부위에서 1반응은 USP 음성 소성체 대조율과 동등하게 나타났다. 또한 중합체 용액(100㎕)을 비이글 개의 치분비물로 생성된 부위 차육하로 투여하였고 대조 부위는 염류 용액으로 씻어내었다. 상기 개는 매일 사망률, 약물독성 효과, 체중, 부분적 치은 자극을 시험하였다. 상기 동물들은 15일과 21일에 희생되었으며 대조부위와 시험부위간에 뚜렷한 차이는 없었다.
[실시예 11]
0.126DL/g 고유점도와 약 10,000정도의 분자량을 가진 DL-PLA를 NMP에 용해하여 중량비로 50% 중합체 용액이 되게 하였다. 중합체 용액에 SaCl를 가하여 중량비로 2.4% 분산이 되게 하여 게이지 23의 무딘 주사바늘이 장착된 1cc용약 주사기로 이물질을 그레이하운드 개의 치은낭에 주사하였다. 상기 물질은 주사의 좁은 팁에서 쉽게 흘러나왔고, 상기 중합체는 낭내에 타액과 유동체에 접촉될 때 필름이나 고체로 응집되거나 침전되었다. 상기 개는 낭주변 조직에 붙어 있는 낭내에 상기 물질의 덩어리가 남아 있는 약 2주 관찰되었는데 밝은 오렌지에서 엷은 흰색으로 천천히 변해갔다. 낭내에서 구액의 작은 양을 뽑기 위해 치은낭 입구에 작은 종이 조각으로 페리오스트립(Periostrip)을 써서 이식체를 포함하는 낭에서 구액을 2주 동안 채집하였다.
수집된 유동체의 부피는 종이조각의 저항역수로 변화를 측정하는 페리오트론을 써서 정량한다. 페리오트론을 사용하기 전에 기지부피의 세럼으로 표준화한다. 수집된 유동액을 포함하는 종이조각은 0.5% 부피비의 메탄올-염산 용액으로 추출하고 기지농도의 동일한 화합물을 기준으로 하여 약물의 양을 정량하는 액체 크로마토그래피에 주사한다. 종이조각에서 추출된 SaCl의 양은 약물 농도를 계산하기 위해 수집된 구액량으로 나눈다. 이러한 기술로, 중합체의 전달계를 가진 치은낭에서 구액내에 SaCl의 농도는 2주 동안의 관찰에서 거의 상수로 나타났다. 구액내에 SaCl 농도는 3일 후에 63.2㎍/㎖, 7일 후에 80.2㎍/㎖ 10일 후에 67.8㎍/㎖, 14일 후에 70.5㎍/㎖였다.
[실시예 12]
아크릴레이트 말단 예비중합체의 합성에 대한 예증의 제시되었다. 두 개의 말단 수산화기를 갖는 예비중합체 100g과 재증류된 THF 200㎖를 질소 기류하에서 첨가용 깔대기 기체 주입구 교반기, 고무관이 설치된 세 개의 목이 있는 500㎖ 둥근 바닥 플라스크에 넣는다. 플라스크를 냉수용상에 넣어 냉각하고 건조한 트리에틸아민(0.95당량/당량 OH)을 주사기로 넣었다. 첨가 깔대기에는 15㎖ THF에 녹은 15.4g 아크릴로일 클로라이드(0.95당량/당량 OH)를 충진하고 반응 혼합물을 교반하면서 1시간 동안 천천히 가한다. 혼합용액을 하룻동안 교반하고 실온이 되도록 방치하였다. 침전된 트리에틸아민 염산염을 여과에 의해 제거하고 여과액은 진공하에 증발시키면 엷은 노란색의 기름이 뜨는데 이것이 아크릴레이트-말단-예비중합체이다. 용매로서 CH2Cl2를 적용한 아실화도 같은 방법으로 진행하였다. 그러나 0℃에서 반응시간은 1시간 감소하여 반응혼합물은 실온에 도달하기 위해 1시간 동안 방치되었다. 2t3NHCl을 여과하고 여과액에 CH2Cl2(약 800㎖) 추가분을 가하여 여과액을 250㎖물로 여러차례 추출해냈다. 유기층은 NgSO4/Na2SO4로 건조시켜 여과하고 진공하에서 유상이 될 때까지 농축한다. 아크릴릭 예비중합체의 병을 호일로 싸서 미리 반응되는 것을 막기 위해 냉장고에 보관하였다.
측정하지 못함.
TMPTETA=트리메틸올프로판 트리에톡시트리아크릴레이트
AIBN=아조비스이소부티로니트릴
대기압하에서 공기중에서 경화됨.
디올 예비중합체를 이용함.
Claims (7)
- 물에 섞이는 생적합성 유기 용매 내에 용해된 생분해성 열가소성 중합체를 사용하여 고형의 이식조직을 원위치에서 형성시키기 위한 액체 조성물을 제조하는 방법.
- 제1항에 있어서, 상기 용매는 상기 중합체를 용해시킬 수 있는 제1용매와 상기 중합체를 용해시킬 수 없는 제2용매를 함유하는 이성분의 혼합용매로 이루어진 것으로서, 이 혼합용매에 존재하는 제1용매 및 제2용매는 상기 중합체가 용해되어질 수 있는 비율로 혼합되어 있으며, 상기 중합체는 원위치에서 액체 조성물로부터 침전되며, 그 결과 제1용매에 대한 제2용매의 비율이 높아지게 되는 방법.
- 제1항에 있어서, 추가로 생물학적 활성 성분을 사용하는 것인 방법.
- 제1항에 따른 방법으로 형성된 생분해성 이식조직.
- 제3항에 따른 방법으로 형성된 생분해성 이식조직.
- 체내에 투입되었을 때 소산되어 이식조직을 형성할 수 있는 생적합성 용매에 용해시킨 유효량이 비반응성 생적합성 중합체로 이루어진 것인 생분해성 이식조직을 원위치에서 형성시키기 위한 조성물.
- 제6항에 있어서, 유효량의 생물학적 활성 성분을 추가로 포함하는 조성물.
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US07252645 US4938763B1 (en) | 1988-10-03 | 1988-10-03 | Biodegradable in-situ forming implants and method of producing the same |
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PCT/US1989/004239 WO1990003768A1 (en) | 1988-10-03 | 1989-09-27 | Biodegradable in-situ forming implants |
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1990
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1991
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1993
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1994
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1995
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1997
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1998
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2005
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- 2005-09-14 NO NO2005021C patent/NO2005021I1/no unknown
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