KR20000073589A - Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same - Google Patents

Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same Download PDF

Info

Publication number
KR20000073589A
KR20000073589A KR1019990016988A KR19990016988A KR20000073589A KR 20000073589 A KR20000073589 A KR 20000073589A KR 1019990016988 A KR1019990016988 A KR 1019990016988A KR 19990016988 A KR19990016988 A KR 19990016988A KR 20000073589 A KR20000073589 A KR 20000073589A
Authority
KR
South Korea
Prior art keywords
biodegradable
nonwoven fabric
tissue regeneration
spinning
solution
Prior art date
Application number
KR1019990016988A
Other languages
Korean (ko)
Other versions
KR100336700B1 (en
Inventor
김학용
김선호
김종상
권수한
이덕래
김종관
Original Assignee
오석송
주식회사 메타치재
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by 오석송, 주식회사 메타치재 filed Critical 오석송
Priority to KR1019990016988A priority Critical patent/KR100336700B1/en
Publication of KR20000073589A publication Critical patent/KR20000073589A/en
Application granted granted Critical
Publication of KR100336700B1 publication Critical patent/KR100336700B1/en

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K45/00—Medicinal preparations containing active ingredients not provided for in groups A61K31/00 - A61K41/00
    • A61K45/06—Mixtures of active ingredients without chemical characterisation, e.g. antiphlogistics and cardiaca
    • D—TEXTILES; PAPER
    • D04—BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04H—MAKING TEXTILE FABRICS, e.g. FROM FIBRES OR FILAMENTARY MATERIAL; FABRICS MADE BY SUCH PROCESSES OR APPARATUS, e.g. FELTS, NON-WOVEN FABRICS; COTTON-WOOL; WADDING ; NON-WOVEN FABRICS FROM STAPLE FIBRES, FILAMENTS OR YARNS, BONDED WITH AT LEAST ONE WEB-LIKE MATERIAL DURING THEIR CONSOLIDATION
    • D04H1/00—Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres
    • D04H1/70—Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres
    • D04H1/72—Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres the fibres being randomly arranged
    • D04H1/724—Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres the fibres being randomly arranged forming webs during fibre formation, e.g. flash-spinning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2430/00—Materials or treatment for tissue regeneration
    • A61L2430/12—Materials or treatment for tissue regeneration for dental implants or prostheses
    • D—TEXTILES; PAPER
    • D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2401/00—Physical properties
    • D10B2401/12—Physical properties biodegradable
    • D—TEXTILES; PAPER
    • D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2509/00—Medical; Hygiene

Abstract

PURPOSE: A bio-degradable guided tissue regeneration membrane for treatment of periodontal disease is provided, which is used in tissue defect sites; and shows good productivity, superior function property, and excellent surgery convenience. CONSTITUTION: A process for the preparation of bio-degradable guided tissue regeneration membrane for treatment of periodontal disease comprises of: mixing bio-degradable high-molecular materials and color pigments in a mixer, and spinning the compound in the rate of 1,500m/min using a melting-spinning device to get non-woven fabrics; adding antibiotics-contained microspheres(24)(in the base, the bio-degradable high-molecular materials) to the non-woven fabrics through a feeder to get a non-woven fabric(21); dissolving bio-degradable high-molecular materials in a solvent, and adding color pigment, the violet No.13; pouring the solution in the solution tank of a solution-spinning device, spinning in an adequate speed, adding high-voltage to get the other non-woven fabric(22); piling and pressing the non-woven fabrics(21)(22) with a hot-press roller to get the guided tissue regeneration membrane(23).

Description

치주질환치료용 생체분해성 유도조직재생막 및 그 제조방법{Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same}Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same

본 발명은 뼈 결함부위나 틈새조직, 치아결함부위 등의 조직결함부위에 사용하는 치주질환치료용 생체분해성 유도조직재생막 및 그 제조방법에 관한 것으로서, 특히 치조골성장을 촉진하도록 하며 뼈의 성장을 빠른 시간내에 성장시켜 치유시간을 단축하고, 약물투여에 의한 부작용을 방지하기 위하여 항생제를 부직포에 포함시켜 서서히 약물이 방출되도록 하며 수술시 임의형태로 자유롭게 디자인 할 수 있게하여 시술편의성을 극대화할 수 있도록한 치주질환치료용 생체분해성 유도조직재생막 및 그 제조방법에 관한 것이다.The present invention relates to a biodegradable induced tissue regeneration membrane for the treatment of periodontal disease used for tissue defects such as bone defects, crevices, tooth defects, and the like, and particularly to promote alveolar bone growth and promote bone growth. In order to shorten the healing time by growing in a short time, and to prevent side effects due to drug administration, antibiotics are included in the nonwoven fabric so that the drug is released slowly and freely designed in any form during surgery to maximize the convenience of the procedure. The present invention relates to a biodegradable induced tissue regeneration membrane for treating periodontal disease and a method of manufacturing the same.

일반적으로 유도조직재생막으로 천연 혹은 합성 라텍스(latex)나 폴리테트라플로로에틸렌이 사용되어 왔고 현재도 사용되고 있으나 이것은 비분해성으로 2차 제거 수술이 필요하고 치아 형태에 따라 다양한 형태가 필요하다.In general, natural or synthetic latex (latex) or polytetrafluoroethylene has been used as an induced tissue regeneration membrane, but it is still used. However, it is non-degradable and requires secondary removal surgery and various shapes depending on tooth shape.

또한 종래의 생체분해성 유도조직재생막은 폴리글리콜산을 섬유로 제조하고 이를 편직물로 제조한 후에 여기에 폴리글리콜리드-락티드 공중합체를 용매에 용해하여 제조하는 것도 있으나, 이것은 양쪽면이 모두 기공이 전혀 없어 조직의 성장을 촉진하지 못하여 치유시간이 길어지고 고정이 용이하지 못하여 시술할 때 고도의 기술이 필요하여 시술 성공률이 낮은 문제점이 있다. 또한 치아형태에 따라 다양한 모양으로 판매하고 있으나, 수술할 때 사람마다 모두 치아 형태나 크기가 다르므로 별도의 디자인이 필요하여 불편한 문제점이 있다.In addition, the conventional biodegradable induced tissue regeneration membrane may be prepared by preparing polyglycolic acid as a fiber and then preparing a knitted fabric, and then dissolving the polyglycolide-lactide copolymer in a solvent. There is a problem that the success rate of the procedure is low because a high degree of skill is required when the procedure is not performed because the healing time is long and the fixation is not easy because there is no tissue growth. In addition, it is sold in a variety of shapes depending on the shape of the tooth, but each person has a different problem in the shape or size of the teeth when the operation requires a separate design is inconvenient problem.

본 발명은 상기 종래 생체분해성 유도조직재생막의 문제점을 해소하기 위하여 안출된 것으로서, 치조골성장을 촉진하도록 하고 뼈의 성장을 빠른 시간내에 성장시켜 치유시간을 단축하며 약물투여에 의한 부작용을 방지하기 위하여 항생제를 부직포에 포함시켜 약물이 서서히 방출되도록 하고 수술시 임의 형태로 자유롭게 디자인하여 시술편의성을 극대화할 수 있는 치주질환치료용 생체분해성 유도조직재생막을 제공하는데 그 목적이 있다. 상기한 본 발명의 목적을 달성하기 위하여 본 발명의 치주질환치료용 생체분해성 유도조직재생막은 한쪽면은 섬유굵기가 0.1∼0.001μm인 생체분해성 부직포로 이루어진 것으로서 표면이 매우 매끄럽고 부드러워 인체 섬유 조직의 부착이 안되고 또 다른 한쪽면은 섬유굵기가 0.1∼400μm인 생체분해성 부직포로 이루어진 것으로서, 섬유조직이 잘 성장하여 부착이 되도록 하는 것이다. 섬유굵기가 0.1∼0.001μm인 생체분해성 부직포는 용액방사를 통하여 제조하고 이 때 방사구 혹은 컨베어벨트 상에 고전압을 걸어 부직포를 구성하는 섬유의 굵기를 초극세화하고, 또 다른 한쪽면을 구성하는 부직포는 용융방사, 멜트브로운(melt blown), 용액방사를 통하여 섬유굵기가 0.1∼400μm로 되게 제조하며 이를 칼렌더에 의해서 압착하여 생체분해성 유도조직재생막을 제조하는 것이다. 또한 부직포 제조과정중에 정밀한 공급피더로 부직포에 항생제를 균일하게 함유시켜 치주질환 치유시간을 단축시키는 것을 특징으로 하고 있다.The present invention has been made to solve the problems of the conventional biodegradable induced tissue regeneration membrane, to promote alveolar bone growth, to grow bone growth in a short time to shorten the healing time and to prevent side effects by drug administration The purpose of the present invention is to provide a biodegradable induced tissue regeneration membrane for treating periodontal disease that can be included in the nonwoven fabric so that the drug is gradually released and designed freely in any form during surgery to maximize the convenience of the procedure. In order to achieve the above object of the present invention, the biodegradable induced tissue regeneration membrane for treatment of periodontal disease of the present invention is composed of a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm, and the surface is very smooth and soft to attach human fiber tissue. The other side is made of a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 μm, so that the fiber tissue grows well and adheres. A biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm is manufactured through solution spinning, and at this time, a high voltage is applied to a spinneret or a conveyor belt to make the thickness of the fibers constituting the nonwoven fabric extremely small and to form another side of the nonwoven fabric. Is prepared to have a fiber thickness of 0.1 ~ 400μm through melt spinning, melt blown, solution spinning to produce a biodegradable induced tissue regeneration membrane by pressing by calender. In addition, it is characterized in that the periodontal disease healing time is shortened by containing the antibiotic evenly in the nonwoven fabric with a precise feed feeder during the nonwoven fabric manufacturing process.

도1의 (A), (B), (C)는 본 발명의 생체분해성 유도조직재생막을 나타낸 도면으로서,1 (A), (B), (C) is a view showing a biodegradable induced tissue regeneration membrane of the present invention,

(A)는 용액방사에 의해 제조된 부직포의 모형도,(A) is a schematic diagram of a nonwoven fabric produced by solution spinning,

(B)는 용액방사에 의해 제조된 부직포와 항생제 혹은 항생제를 포함하고 있는 마이크로 스페어층의 모형도,(B) is a schematic diagram of a non-woven fabric prepared by solution spinning and a micro spare layer containing antibiotics or antibiotics,

(C)는 유도조직재생막의 개략도,(C) is a schematic of the induced tissue regeneration membrane,

도2는 본 발명의 부직포 제조장치의 개략도이다.2 is a schematic view of a nonwoven fabric manufacturing apparatus of the present invention.

<도면의 주요부분에 대한 부호의 설명><Description of the symbols for the main parts of the drawings>

1 : 호퍼 2 : 압출기1: Hopper 2: Extruder

3 : 계량펌프 4 : 방사구금(spinneret)3: metering pump 4: spinneret

5 : 냉각 및 연신챔버 6 : 냉각공기공급관5: cooling and drawing chamber 6: cooling air supply pipe

7 : 필라멘트 교락장치(entanglement) 8 : 공기흡입장치7 filament entanglement 8 air suction device

9 : 컨베어벨트 10 : 용액탱크9: Conveyor Belt 10: Solution Tank

11 : 용액방사용 계량펌프 12 : 고전압 발생 장치11: solution discharge metering pump 12: high voltage generator

13 : 용액방사용 방사구금 14 : 용매제거장치13 solution spinning spinneret 14 solvent removal device

15 : 가열공기 공급장치 16 : 항생제투입용 피더15: heating air supply device 16: feeder for antibiotic injection

17 : 가이드 벨트 18 : 가열 압착 캘린더17: guide belt 18: heating crimp calendar

19 : 냉각로울러 20 : 권취장치19: cooling roller 20: winding device

이하, 본 발명의 실시예를 첨부도면을 참조하여 상세히 설명하기로 한다.Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

본발명의 치주질환치료용 생체분해성 유도조직재생막은 표면이 매우 매끄럽고 부드러워서 인체 섬유조직에 부착이 안되며, 섬유굵기가 0.1∼0.001μm인 생체분해성 부직포와 인체의 섬유조직이 잘 성장하여 부착이 되도록 한 것으로서 섬유굵기가 0.1∼400μm, 양호하게는 10∼300μm인 생체분해성 부직포를 적층, 압착하여서 구성된다.Biodegradable induced tissue regeneration membrane for treatment of periodontal disease of the present invention is very smooth and soft, so that it does not adhere to human fiber tissues. It is constructed by laminating and compressing a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 µm, preferably 10 to 300 µm.

본 발명의 생체분해성 유도조직재생막의 제조방법을 각 공정별로 상세히 설명하기로 한다.The manufacturing method of the biodegradable induced tissue regeneration membrane of the present invention will be described in detail for each process.

제1공정1st process

생체분해성 고분자물질과 안료를 혼합기에 넣어서 혼합한 후 이 혼합물을 용융방사장치(가)에서 1,500m/min 의 방사속도로 방사하여 부직포를 제조한다.After mixing the biodegradable polymer and pigment into a mixer, the mixture is spun at a spinning speed of 1,500 m / min in a melt spinning apparatus (A) to prepare a nonwoven fabric.

제2공정2nd process

상기 용융방사에 의해 제조된 부직포에 기제인 생체분해성 고분자물질에 항생제를 함유시켜서 제조한 마이크로 스페어를 항생제투입용 피더(6)를 통하여 공급하여 일측의 부직포(21)를 제조한다.A non-woven fabric 21 on one side is prepared by supplying a micro spare prepared by containing an antibiotic in a biodegradable polymer material based on the nonwoven fabric prepared by melt spinning through an antibiotic feeder 6.

제3공정3rd process

생체분해성 고분자물질을 용매에 용해하여 농도 10wt%로 제조한 후 이 용액에 안료로 바이올렛(violet) 13을 투입한다.After dissolving the biodegradable polymer in a solvent to prepare a concentration of 10wt%, violet 13 is added to the solution as a pigment.

제4공정4th process

제3공정에서의 용액을 용액방사장치(나)의 용액탱크(10)에 투입한 후 알맞는 방사속도로 방사하여 부직포를 제조하며 이때 고전압 50kv를 방사구금에 가하여 상기 부직포섬유를 초극세화시킨 타측의 부직포(22)를 제조한다.The solution in the third process is injected into the solution tank 10 of the solution spinning device (b) and then spun at a suitable spinning speed to produce a nonwoven fabric. At this time, the high voltage 50kv is applied to the spinneret to make the nonwoven fabric ultrafine. Nonwoven fabric 22 is manufactured.

제5공정5th process

가열압착로울러(18)에 의해서 상기 2종류의 부직포(21)(22)를 적층, 압착하여 2층으로 적층된 부직포인 유도조직 재생막(23)을 얻는다.The two types of nonwoven fabrics 21 and 22 are laminated and pressed by a heat press roller 18 to obtain an induced tissue regeneration film 23 that is a nonwoven fabric laminated in two layers.

다음에 상기 각 공정들을 더욱 더 구체적으로 설명하기로 한다.Next, the above processes will be described in more detail.

섬유굵기가 0.1∼0.001μm인 생체분해성 부직포는 용액방사를 통하여 제조하고 이 때 방사구 혹은 컨베어벨트상에 고전압을 걸어 부직포(22)를 구성하는 섬유의 굵기를 초극세화하고 또 다른 한쪽면을 구성하는 부직포(21)는 용융방사, 멜트브로운, 용액방사를 통하여 섬유굵기가 0.1∼400μm으로 제조하며, 이를 칼렌더를 사용하여 압착하여 생체분해성 유도 조직 재생막(guided tissue regeneration)(23)을 제조하는 것이다. 그리고 부직포 제조과정중에 정밀한 공급피더(16)로 부직포에 항생제를 균일하게 함유시켜 치주질환 치유시간을 단축하도록 되어 있다.A biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm is manufactured by solution spinning, and at this time, a high voltage is applied to a spinneret or a conveyor belt to make the thickness of the fibers constituting the nonwoven fabric 22 extremely ultra-thin and constitute another side. The nonwoven fabric 21 is made of a fiber thickness of 0.1 ~ 400μm through melt spinning, melt blown, solution spinning, and pressed using a calender to prepare a biodegradable guided tissue regeneration (23). It is. In the manufacturing process of the nonwoven fabric, the feeder 16 precisely contains antibiotics in the nonwoven fabric to shorten the periodontal disease healing time.

생체분해성 고분자 물질로는 글리콜리드, 락티드, 글리콜산, 젖산, 디옥산원, 트리메틸렌카보네이트, 카프로락톤 등으로 이루어진 합성 분해성 고분자 및 이들로 이루어진 공중합체와 블랜드는 물론 키토산, 셀룰로오스 등으로 이루어진 천연 생체분해성 고분자 물질 및 이들의 공중합체와 블랜드물 등이다. 두께가 0.1∼10mm인 것을 특징으로 하며 양호하게는 0.1∼2mm 범위이다.As biodegradable polymers, synthetic degradable polymers made of glycolide, lactide, glycolic acid, lactic acid, dioxane source, trimethylene carbonate, caprolactone, copolymers and blends thereof, as well as natural products made of chitosan, cellulose, etc. Biodegradable polymeric substances and copolymers and blends thereof. It is characterized by a thickness of 0.1 to 10 mm and preferably in the range of 0.1 to 2 mm.

섬유굵기가 0.1∼0.001μm로 구성된 생체분해성 부직포로 이루어진 표면과 섬유굵기가 0.1∼400μm으로 구성된 생체분해성 부직포로 이루어진 표면의 색상을 서로 다르게 하여 취급 용이성이 우수하게 한다. 섬유굵기가 0.1∼0.001μm로 구성된 부직포나 섬유굵기가 0.1∼400μm로 구성된 생체분해성 부직포를 제조할 때 안료로 칼라 인덱스 솔벤트 바이올렛(Color Index Solvent Violet) 13이나 솔벤트 그린(Solvent Green) 6을 섬유중량에 대하여 0.01∼1wt% 첨가하여 서로 다른 색상을 띄우도록 한다.The surface of the biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm and the surface of the biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 μm are different from each other to facilitate handling. When producing a nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm or a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 μm, color index solvent violet 13 or solvent green 6 is used as a pigment. 0.01 to 1wt% is added to float the different colors.

생체분해성 부직포의 제조방식은 2층 이상으로 적층하는 것을 특징으로 하며 부직포 제조방법은 용액방사, 용융방사, 멜트브로운(melt blown) 등으로 한다. 예를 들면 섬유굵기가 0.1∼400μm인 부직포(21)는 멜트브로운으로 제조하고 섬유굵기가 0.1∼0.001μm인 부직포(22)는 용액방사로 제조하여 적층하거나 혹은 0.1∼400μm인 부직포(21)는 스펀본드(spun bond)로 제조하고 섬유굵기가 0.1∼0.001μm인 부직포(22)는 용액방사로 제조하여 적층할 수도 있다.The method for producing a biodegradable nonwoven fabric is characterized by laminating two or more layers, and the method for producing a nonwoven fabric includes solution spinning, melt spinning, and melt blown. For example, the nonwoven fabric 21 having a fiber thickness of 0.1 to 400 μm is manufactured by melt blown, and the nonwoven fabric 22 having a fiber thickness of 0.1 to 0.001 μm is manufactured by laminating by solution spinning or the nonwoven fabric 21 having 0.1 to 400 μm. May be made of spun bond, and the nonwoven fabric 22 having a fiber thickness of 0.1 to 0.001 µm may be produced by laminating solution spinning.

용액방사시에 방사구 또는 섬유집속위치에 고전압을 가하여 초극세 섬유로 제조된 부직포(22)를 제조하거나 멜트브로운, 스펀본드 등의 용융방사인 경우에도 고전압을 방사구 또는 섬유집속위치에 가하여 0.1∼10μm 정도의 굵기를 갖는 극세섬유의 제조도 가능하다.In the case of solution spinning, high voltage is applied to the spinneret or the fiber focusing position to produce a nonwoven fabric 22 made of ultra-fine fibers, or even in the case of melt spinning such as melt blown or spunbond, It is also possible to produce ultrafine fibers having a thickness of ˜10 μm.

용액방사를 하여 초극세섬유로 이루어진 부직포(22)를 제조할 경우 고분자의 종류에 따라 다르기는 하나 메틸렌클로라이드, 디메틸포름아미드, 에틸아세테이트, 벤젠, 톨루엔, 클로로포름, 아세톤, 디옥산, 테트라하이드로퓨란 등을 이용할 수 있다.When the non-woven fabric 22 made of ultra-fine fibers by solution spinning is produced according to the type of polymer, methylene chloride, dimethylformamide, ethyl acetate, benzene, toluene, chloroform, acetone, dioxane, tetrahydrofuran, etc. It is available.

부직포 제조시 항생제를 첨가하는데 투입방법은 도2에 나타내었듯이 정밀한 공급피더(16)를 이용하여 압착칼렌다(18) 앞의 위치에서 부착시킨다. 항생제는 분말상태 혹은 용매에 분산시켜 용액을 공급하고 별도의 건조기를 이용하여 제거하여도 된다. 분말보다는 용액에 분산시켜 부직포에 균일하게 부착하는 것이 양호하다. 이 때 항생제와 부직포의 결합을 양호하게하기 위해서 바인더(binder)를 사용하여도 된다. 항생제로는 염산미노클린, 염산 테트라사이클린, 메트로니다아졸 (metronidazol) 등이다. 항생제 함량은 부직포 중량에 대하여 0.01∼10wt%이며 양호하게는 0.5∼5wt%범위이다. 또는 기제로 폴리젖산, 소디움알지네이트, 폴리카프로락톤 등을 이용하여 염산미노클린, 염산 테트라사이클린, 메트로니다아졸 (metronidazol) 등이 함유된 마이크로스페어(microsphere)를 제조하고 이를 공급피더(16)로 정량적으로 공급하여 1주 혹은 그 이상을 약물이 서서히 방출됨으로써 항생제의 전신투여에 의한 부작용 발생을 억제할 수 있다. 필요한 부위만 약물을 효과적으로 처리하므로써 치료기간의 단축을 가져올 수 있다. 폴리젖산이나 폴리 글리콜리드-락티드 공중합체, 폴리카프로락톤, 폴리디옥산원 등의 저분자량 고분자와 앞서 언급한 항생제를 메틸렌클로라이드, 톨루엔, 에틸아세테이트 등의 용매에 용해하고 분산매를 첨가하여 교반기로 회전하면 마이크로스페어를 제조할 수 있다.In the nonwoven fabric production, antibiotics are added. The injection method is attached at a position in front of the pressing calendar 18 using a precise feed feeder 16 as shown in FIG. Antibiotics may be dispersed in powder or solvent to provide a solution and removed using a separate dryer. It is better to disperse in solution rather than powder to adhere uniformly to the nonwoven fabric. At this time, a binder may be used in order to improve binding between the antibiotic and the nonwoven fabric. Antibiotics include minoclean hydrochloride, tetracycline hydrochloride, metronidazole, and the like. The antibiotic content is in the range of 0.01 to 10 wt% and preferably in the range of 0.5 to 5 wt% by weight of the nonwoven fabric. Alternatively, using a polylactic acid, sodium alginate, polycaprolactone and the like to prepare microspheres containing minochlorine hydrochloride, tetracycline hydrochloride, metronidazole (metronidazol) and the like quantitatively as a feed feeder (16) The drug may be released slowly for one week or more to suppress side effects caused by systemic administration of antibiotics. Effective treatment of only the necessary area can lead to a shortened treatment period. Low molecular weight polymers such as polylactic acid, polyglycolide-lactide copolymers, polycaprolactones, polydioxane sources and the aforementioned antibiotics are dissolved in a solvent such as methylene chloride, toluene, ethyl acetate, and a dispersion medium is added. Rotating can produce a microspare.

도1은 본 발명의 유도조직재생막(23)을 보여준 그림이다. 도1에서 (A)는 섬유굵기가 0.1∼400μm인 부직포(21)를 나타내고 있고 (B)는 섬유굵기가 0.1∼0.001μm인 부직포(22)와 항생제를 함유한 마이크로스페어가 있는 층(24)을 나타내고 있다. (C)는 3가지 층을 칼렌더 로울러로 압착하여 형성된 후의 유도재생막(23)을 나타내고 있다.1 is a diagram showing the induced tissue regeneration membrane 23 of the present invention. In Fig. 1, (A) shows a nonwoven fabric 21 having a fiber thickness of 0.1 to 400 µm, and (B) a non-woven fabric 22 having a fiber thickness of 0.1 to 0.001 µm and a layer 24 having a microspare containing antibiotics. Indicates. (C) shows the induction regeneration film 23 after the three layers are formed by pressing with a calendar roller.

용액방사로 제조하여 적층하거나 혹은 0.1∼400μm인 부직포는 스펀본드 (spun bond)로 제조하고 섬유굵기가 0.1∼0.001μm인 부직포는 용액방사로 제조하여 적층할 수도 있다.The nonwoven fabrics prepared by solution spinning or 0.1 to 400 μm may be manufactured by spun bond, and the nonwoven fabrics having a fiber thickness of 0.1 to 0.001 μm may be prepared by solution spinning.

도2는 본 발명의 유도조직재생막을 제조하는 장치의 개략도를 보여준 것으로서 (1)은 원료가 투입되는 호퍼이고 (2)는 생체분해성 고분자 물질을 용융하는 압출기이고 (3)은 일정량씩 공급하는 계량펌프이다. 그리고 (4)는 방사구금이고 (5)는 냉각 및 연신챔버이며 (6)은 블로우를 이용하여 냉각공기를 공급하고 있는 것을 나타낸 것이다. 또한 (7)은 필라멘트 교락장치이며 (8)은공기흡입장치이고 (9)는 방사된 섬유를 집속해주는 컨베어벨트이이다. 이와같은 장치는 일반적으로 부직포 제조시 채용하고 있는 방식이다. 이와같은 부직포 제조장치중에 방사구금(4)에 고전압을 걸어주면 고분자 쇄의 이온화 현상으로 0.1∼1μm 정도의 극세 섬유로 이루어진 부직포의 제조도 가능하다. 도2의 (10)∼(14)까지는 용액방사에 관련된 섬유로 (10)은 용액탱크이고 (11)은 용액방사용 계량펌프이고 (12)는 고전압 발생 장치이다. 고전압의 범위는 10∼200kV정도가 양호하고 고전압의 범위에 따라 섬유의 굵기를 nm수준까지도 제어가 가능하다. 양호한 고전압의 범위는 30∼100kV정도이다. 도2의 (13)은 용액방사용 방사구금이고 (14)는 용매제거장치이며 (15)는 용매제거용 가열공기 공급장치이며 (16)은 항생제 투입용 피더로 분말 혹은 액상으로 된 피더이다. 그리고 (17)은 부직포의 원활한 진행을 위한 가이드 벨트이고 (18)은 2층이상을 적층하기 위한 가열 압착 칼렌더이고 (19)는 냉각로울러이고 (20)은 부직포를 감는 권취장치이다.Figure 2 shows a schematic diagram of a device for producing an induced tissue regeneration membrane of the present invention (1) is a hopper into which the raw material is injected (2) is an extruder for melting a biodegradable polymer material and (3) is a metering to supply a predetermined amount It is a pump. And (4) is spinneret, (5) is cooling and drawing chamber, and (6) is supplying cooling air using blow. In addition, (7) is a filament entanglement device, (8) is an air suction device, and (9) is a conveyor belt which focuses the spun fiber. Such a device is generally employed in the manufacture of nonwoven fabrics. When a high voltage is applied to the spinneret 4 in such a nonwoven fabric manufacturing apparatus, it is also possible to manufacture a nonwoven fabric made of ultrafine fibers of about 0.1 to 1 탆 due to ionization of polymer chains. 2 to 10 are fibers related to solution spinning, 10 is a solution tank, 11 is a solution spinning metering pump, and 12 is a high voltage generator. The range of high voltage is good about 10-200kV and the thickness of the fiber can be controlled to nm level according to the range of high voltage. The preferred high voltage range is about 30 to 100 kV. (13) is a spinneret for solution spinning, (14) is a solvent removing device, (15) is a heating air supply device for removing solvent, and (16) is a feeder for antibiotic injection, which is a powder or liquid feeder. And (17) is a guide belt for smooth running of the nonwoven fabric, (18) is a hot pressing calender for stacking two or more layers, (19) is a cooling roller, and (20) is a winding apparatus for winding the nonwoven fabric.

도2는 본 발명의 한가지 제조장치의 예를 보여준 도면이다. 그러나 부직포의 제조방법을 여러 가지 방법으로 조합하여 제조가 가능하다. 본 발명의 장치에서 특징으로는 섬유굵기가 10μm 이상인 부직포의 제조는 종래의 방법으로 제조할 수 있으나 1μm이하의 초극세섬유로 이루어진 부직포는 종래의 용융방사방법으로는 제조가 어렵다. 따라서 방사구금 부근에 고전압을 걸어 고분자쇄의 이온화 경향성을 이용하여 1μm이하의 초극세섬유로 이루어진 부직포의 제조가 가능하게 된다. 유도조직재생막을 온라인(on-line)상으로 제조가 가능하여 매우 경제적인 시스템이다.2 shows an example of one manufacturing apparatus of the present invention. However, it is possible to combine the manufacturing method of the nonwoven fabric in various ways. In the device of the present invention, the nonwoven fabric having a fiber thickness of 10 μm or more can be prepared by a conventional method, but a nonwoven fabric made of ultrafine fibers of 1 μm or less is difficult to manufacture by a conventional melt spinning method. Therefore, by applying a high voltage near the spinneret, it is possible to manufacture a nonwoven fabric made of ultra-fine fibers of 1 μm or less by using the ionization tendency of the polymer chain. Induction tissue regeneration membrane can be produced on-line (on-line) is a very economical system.

이하 본 발명을 실시예를 통하여 구체적으로 설명하고자 한다.Hereinafter, the present invention will be described in detail through examples.

본 발명은 아래 실시예에만 국한 된것은 아니다.The invention is not limited to the following examples.

실시예1Example 1

10rad/sec, 240℃에서 8,000poise인 폴리글리콜산 생체분해성 펠릿과 솔벤트그린(solvent green) 6를 폴리글리콜산에 대하여 0.04wt%를 넣어 혼합기를 사용하여 혼합하였다. 도2의 용융방사장치(가)를 이용하여 방사속도를 1,500m/min으로 방사하였고, 이 때 사용한 방사구금(나)은 방사공이 96공이고 방사공의 직경이 0.3mm인 것을 사용하였다. 이 부직포를 이루는 섬유의 굵기는 평균 15μm이었고, 용융방사에 의해 제조된 부직포를 도2의 항생제투입용 피더(16)에서 중량평균 분자량이 2,000인 폴리젖산을 기제로 하여 염산미노클린 항생제가 함유된 마이크로스페어를 전체 부직포 중량에 대하여 1wt% 함유하도록 정량 공급피더(16)를 이용하여 공급하였다. 또한 중량평균분자량이 280,000인 글리콜리드-락티드(90/10 몰비)공중합체를 메틸렌클로라이드 용매에 용해하여 농도가 10wt%를 제조하였고, 이 용액에 바이올렛 13을 0.03wt%를 투입하였다. 도2의 용액방사장치(나)의 용액탱크(10)에 투입하고 부직포를 제조하였으며 고전압 50kV를 방사구금(13)에 걸어서 섬유를 초극세화하였다. 제조된 부직포를 이루는 섬유의 굵기는 0.08μm으로 표면이 매우 매끄럽고 부드러운 부직포를 제조하였고, 가열 압착로울러(18)를 사용하여 2종류의 부직포를 적층하였다. 적층된 부직포의 두께는 500μm 이었고 섬유의 굵기가 15μm인 부직포의 두께는 350μm이었고 섬유 굵기가 0.08μm인 부직포의 두께는 150μm이었다.Polyglycolic acid biodegradable pellets of 8,000 poise and solvent green 6 at 10 rad / sec and 240 ° C. were mixed in an amount of 0.04 wt% based on polyglycolic acid. The spinning speed was spun at 1,500 m / min using the melt spinning apparatus (a) of FIG. 2, and the spinnerets (b) used were 96 spinners and 0.3 mm spinners. The thickness of the fibers constituting the nonwoven fabric was 15 μm on average, and the nonwoven fabric prepared by melt spinning was made based on polylactic acid having a weight average molecular weight of 2,000 in the antibiotic feeder 16 of FIG. Micro spares were supplied using a fixed feeder 16 to contain 1 wt% of the total nonwoven weight. In addition, a glycolide-lactide (90/10 molar ratio) copolymer having a weight average molecular weight of 280,000 was dissolved in a methylene chloride solvent to prepare a concentration of 10 wt%, and violet solution (0.03 wt%) was added to the solution. 2 was added to the solution tank 10 of the solution spinning apparatus (b) of FIG. 2 to prepare a nonwoven fabric, and the fiber was ultrafine by applying a high voltage of 50 kV to the spinneret 13. The thickness of the fibers constituting the prepared nonwoven fabric was 0.08 μm to prepare a non-woven fabric having a very smooth and soft surface, and two kinds of nonwoven fabrics were laminated using a heat compression roller 18. The thickness of the laminated nonwoven fabric was 500 μm, the thickness of the nonwoven fabric having a fiber thickness of 15 μm was 350 μm, and the thickness of the nonwoven fabric having a fiber thickness of 0.08 μm was 150 μm.

실시예2Example 2

도2의 용융방사장치(가)를 이용하여 융점이 60℃이고 용융지수(melt flow rate, MFR)가 30g/10min인 폴리카프로락톤을 사용하였다. 방사온도는 235℃로 하고 96개의 방사공이 있고 방사공의 직경이 0.12mm인 것을 사용하였다. 이 때 방사구금에 고전압장치를 50kV를 설치하여 극세화 하였고, 방사속도는 3500m/min으로 하여 섬유직경이 3μm인 것을 제조하였다. 용융방사에 의해 제조된 부직포를 도2의 항생제투입용 피더(16)에서 중량평균 분자량이 2,000인 폴리젖산을 기제로 하여 염산테트라사이클린 항생제가 함유된 마이크로스페어를 전체 부직포 중량에 대하여 1.5wt% 함유하도록 정량 공급피더(16)를 이용하여 공급하였다. 또한 중량평균분자량이 180,000인 글리콜리드-락티드(90/10 몰비)공중합체를 메틸렌클로라이드 용매에 용해하여 농도가 12wt%를 제조하였으며 도2의 용액방사장치(나)의 용액탱크(10)에 투입하고 부직포를 제조하였다. 고전압 80kV를 방사구금(13)에 걸어서 섬유를 초극세화하였고, 제조된 부직포를 이루는 섬유의 굵기는 0.03μm으로 표면이 매우 매끄럽고 부드러운 부직포를 제조하였으며 가열 압착로울러(18)를 사용하여 2종류의 부직포를 적층하였다. 적층된 부직포의 두께는 350μm 이었고 섬유의 굵기가 3μm인 부직포의 두께는 180μm이었고 섬유 굵기가 0.03μm인 부직포의 두께는 120μm이었다.Polycaprolactone having a melting point of 60 ° C. and a melt flow rate (MFR) of 30 g / 10 min was used in the melt spinning apparatus (a) of FIG. 2. The spinning temperature was set at 235 ° C., and there were 96 spin holes and 0.12 mm in diameter. At this time, the high voltage device was installed in the spinneret, and 50kV was micronized. The spinning speed was 3500m / min, and the fiber diameter was 3μm. The nonwoven fabric prepared by melt spinning was contained in the antibiotic feeder 16 of FIG. 2, based on polylactic acid having a weight average molecular weight of 2,000, and containing 1.5 wt% of microspares containing tetracycline hydrochloride with respect to the total weight of the nonwoven fabric. It was supplied using a fixed feeder 16 so as to. In addition, 12 wt% of a glycolide-lactide (90/10 molar ratio) copolymer having a weight average molecular weight was dissolved in a methylene chloride solvent to prepare a 12 wt% concentration in the solution tank 10 of the solution spinning device (B) of FIG. Was added and a nonwoven fabric was prepared. The superfine fiber was made by applying high voltage 80kV to the spinneret 13, and the thickness of the fabric constituting the manufactured nonwoven fabric was 0.03μm, which produced a very smooth and soft nonwoven fabric, and used two kinds of nonwoven fabrics by using a heat compression roller (18). Was laminated. The thickness of the laminated nonwoven fabric was 350 μm, the thickness of the nonwoven fabric having a thickness of 3 μm was 180 μm, and the thickness of the nonwoven fabric having a fiber thickness of 0.03 μm was 120 μm.

실시예3Example 3

융점이 103℃이고 용융지수(MFR)가 32g/10min인 폴리프로피오락톤 (polypropiolactone)칩과 솔벤트그린 6를 폴리프로피오락톤에 대하여 0.28wt%를 넣어 혼합기를 사용하여 혼합하였다. 방사온도는 247℃로, 방사속도는 3500m/min으로 하여 부직포를 제조하였고, 방사구금은 실시예2와 동일한 것을 사용하였다. 제조된 부직포의 섬유굵기는 12μm이었고, 용융방사에 의해 제조된 부직포를 도2의 항생제투입용 피더(16)에서 염산미노클린 항생제(평균 직경 8μm)를 전체 부직포 중량에 대하여 0.5wt% 함유하도록 정량 공급피더(16)를 이용하여 공급하였다. 또한 중량평균분자량이 150,000인 글리콜리드-락티드(90/10 몰비)공중합체를 메틸렌클로라이드 용매에 용해하여 농도가 15wt%를 제조하였고, 이 용액에 바이올렛 13을 0.03wt%를 투입하였다. 도2의 용액방사장치(나)의 용액탱크(10)에 투입하고 부직포를 제조하였고, 고전압 80kV를 방사구금(13)에 걸어서 섬유를 초극세화하였다. 제조된 부직포를 이루는 섬유의 굵기는 0.008μm으로 표면이 매우 매끄럽고 부드러운 부직포를 제조하였으며, 가열 압착로울러(18)를 사용하여 2종류의 부직포를 적층하였다. 적층된 부직포의 두께는 280μm 이었고 섬유의 굵기가 12μm인 부직포의 두께는 200μm이었고 섬유 굵기가 0.008μm인 부직포의 두께는 80μm이었다.A polypropiolactone chip and a solvent green 6 having a melting point of 103 ° C. and a melt index (MFR) of 32 g / 10 min were added at 0.28 wt% based on the polypropiolactone, and mixed using a mixer. The spinning temperature was 247 ° C., the spinning speed was 3500 m / min to produce a nonwoven fabric, and the spinneret was the same as in Example 2. The fiber thickness of the prepared nonwoven fabric was 12 μm, and the nonwoven fabric prepared by melt spinning was quantitated to contain 0.5 wt% of minochlorine hydrochloride (average diameter 8 μm) in the antibiotic feeder 16 of FIG. 2 with respect to the total nonwoven weight. The feed was supplied using a feeder 16. Also, a glycolide-lactide (90/10 molar ratio) copolymer having a weight average molecular weight of 150,000 was dissolved in a methylene chloride solvent to prepare a concentration of 15 wt%, and 0.03 wt% of violet 13 was added to the solution. In the solution tank 10 of the solution spinning device (b) of FIG. 2, a nonwoven fabric was produced, and the fiber was ultrafine by applying high voltage 80 kV to the spinneret 13. The thickness of the fibers forming the nonwoven fabric was 0.008 μm to prepare a very smooth and smooth nonwoven fabric, and two kinds of nonwoven fabrics were laminated using a heat compression roller 18. The thickness of the laminated nonwoven fabric was 280 μm, the thickness of the nonwoven fabric having a thickness of 12 μm was 200 μm, and the thickness of the nonwoven fabric having a fiber thickness of 0.008 μm was 80 μm.

실시예4Example 4

융점이 175℃이고 중량평균분자량이 150,000인 젖산으로부터 제조된 폴리젖산을 이용하여 방사온도 230℃로, 방사속도는 1500m/min으로 하여 부직포를 제조하였다. 방사구금은 실시예2와 동일한 것을 사용하였고, 제조된 부직포의 섬유굵기는 17μm이었다. 용융방사에 의해 제조된 부직포를 도2의 항생제투입용 피더(16)에서 염산테트라사이클린 항생제(평균 직경 11μm)를 전체 부직포 중량에 대하여 0.6wt% 함유하도록 정량 공급피더(16)를 이용하여 공급하였다. 또한 중량평균분자량이 150,000인 글리콜리드-락티드(90/10 몰비)공중합체를 메틸렌클로라이드 용매에 용해하여 농도가 15wt%를 제조하였고, 도2의 용액방사장치(나)의 용액탱크(10)에 투입하고 부직포를 제조하였다. 고전압 80kV를 방사구금(13)에 걸어서 섬유를 초극세화하였으며, 제조된 부직포를 이루는 섬유의 굵기는 0.008μm으로 표면이 매우 매끄럽고 부드러운 부직포를 제조하였다. 가열 압착로울러(18)를 사용하여 2종류의 부직포를 적층하였다. 적층된 부직포의 두께는 450μm이었고 섬유의 굵기가 17μm인 부직포의 두께는 330μm이었고 섬유 굵기가 0.008μm인 부직포의 두께는 80μm이었다.A nonwoven fabric was prepared using a polylactic acid prepared from lactic acid having a melting point of 175 ° C. and a weight average molecular weight of 150,000 at a spinning temperature of 230 ° C. and a spinning speed of 1500 m / min. The spinneret was the same as in Example 2, and the fiber thickness of the prepared nonwoven fabric was 17 μm. The nonwoven fabric produced by melt spinning was supplied using a fixed feeder 16 so that tetracycline hydrochloride (average diameter of 11 μm) of tetracycline hydrochloride (average diameter of 11 μm) was contained in the antibiotic feeder 16 of FIG. 2. . In addition, a glycolide-lactide (90/10 molar ratio) copolymer having a weight average molecular weight of 150,000 was dissolved in a methylene chloride solvent to prepare a concentration of 15 wt%, and the solution tank 10 of the solution spinning device (B) of FIG. 2 was used. Into a nonwoven fabric. The fiber was ultrafine by applying high voltage 80 kV to the spinneret 13, and the nonwoven fabric made of nonwoven fabric had a thickness of 0.008 μm to produce a very smooth and soft nonwoven fabric. Two types of nonwoven fabrics were laminated using the heat press roller 18. The thickness of the laminated nonwoven fabric was 450 μm, the thickness of the nonwoven fabric having a thickness of 17 μm was 330 μm, and the thickness of the nonwoven fabric having a fiber thickness of 0.008 μm was 80 μm.

실시예5Example 5

융점이 105℃이고 1,1,2,2, 테트라클로로에탄(tetrachloroethane)용매로 측정한 고유점도가 1.2dl/g폴리디옥산원을 이용하여 방사온도 200℃로, 방사속도는 1500m/min으로 하여 부직포를 제조하였다. 방사구금은 실시예2와 동일한 것을 사용하였고, 제조된 부직포의 섬유굵기는 15μm이었다. 용융방사에 의해 제조된 부직포를 도2의 정량공급피더인 (16)으로 글리콜리드-락티드 공중합체를 기제로 사용하여 제조한 염산미노클린이 함유된 마이크로스페어를 전체부직포 중량에 대하여 1.5wt% 함유하도록 공급하였다. 또한 중량평균분자량이 150,000인 글리콜리드-락티드 (90/10 몰비)공중합체를 메틸렌클로라이드 용매에 용해하여 농도가 15wt%인 것을 제조하였고, 도2의 용액방사장치(B)의 용액탱크(10)에 투입하고 부직포를 제조하였으며, 고전압 80kV를 방사구금에 걸어서 방사속도 120m/min으로 방사하여 초극세 섬유를 제조하였다. 제조된 부직포를 이루는 섬유의 굵기는 0.01μm으로 표면이 매우 매끄럽고 부드러운 부직포를 제조하였으며, 가열 압착로울러(18)를 사용하여 2종류의 부직포를 적층하였다. 적층된 부직포의 두께는 420μm이었고 섬유의 굵기가 15μm인 부직포의 두께는 310μm이었고 섬유 굵기가 0.01μm인 부직포의 두께는 110μm이었다.Melting point is 105 ℃, and the intrinsic viscosity measured by 1,1,2,2, tetrachloroethane solvent is 1.2 ℃ / g using polydioxane source and spinning temperature is 200 ℃ and spinning speed is 1500m / min. To prepare a nonwoven fabric. The spinneret was the same as in Example 2, and the fiber thickness of the prepared nonwoven fabric was 15 μm. 1.5 wt% of the non-woven fabric prepared by melt spinning was prepared using the glycolide-lactide copolymer as a quantitative feeder of FIG. It was fed to contain. In addition, a glycolide-lactide (90/10 molar ratio) copolymer having a weight average molecular weight of 150,000 was dissolved in a methylene chloride solvent to prepare a concentration of 15 wt%. The solution tank (10) of the solution spinning device (B) of FIG. ) And a non-woven fabric was prepared, and a super-fine fiber was manufactured by spinning a high voltage 80 kV at a spinneret at a spinning speed of 120 m / min. The thickness of the fibers constituting the prepared nonwoven fabric was 0.01 μm to prepare a very smooth and soft nonwoven fabric, and two kinds of nonwoven fabrics were laminated using a heat compression roller 18. The thickness of the laminated nonwoven fabric was 420 μm, the thickness of the nonwoven fabric having a fiber thickness of 15 μm was 310 μm, and the thickness of the nonwoven fabric having a fiber thickness of 0.01 μm was 110 μm.

전술한 바와 같이, 본 발명은 유도조직재생막을 섬유굵기가 전혀 다른 2가지 형태의 부직포를 온라인으로 제조하여 한쪽은 섬유조직의 성장을 억제하고 또다른 한쪽면은 섬유굵기가 커서 기공도가 크므로 섬유조직성장을 촉진하여 치조골성장을 촉진하도록하며 뼈의 성장을 빠른 시간내에 성장시켜 치유시간을 단축하며 약물투여에 의한 부작용을 방지할 수 있게 되고, 수술시 원하는 만큼 손쉽게 디자인하여 수술편의성이 매우 우수하며 제품생산성이 우수하고 기능성이 매우 양호한 효과가 있다.As described above, in the present invention, two types of nonwoven fabrics having different fiber thicknesses are produced online with induced tissue regeneration membranes, so that one side suppresses the growth of the fibrous tissue and the other side has large pore size. It promotes fibrous tissue growth to promote alveolar bone growth, grows bone growth in a short time, shortens healing time, and prevents side effects due to drug administration. It has excellent product productivity and very good functionality.

Claims (11)

치추질환 치료용 유도조직재생막에 있어서, 섬유굵기가 0.1∼0.001μm이며 용융방사에 의해 제조된 일측의 생체분해성 부직포와 섬유굵기가 0.1∼400μm이며 용액방사에 의해 제조된 타측의 생체분해성 부직포가 적층, 압착되어서 이루어진 것을 특징으로 한 치주질환치료용 생체분해성 유도조직재생막(guided tissue regeneration)In the induced tissue regeneration membrane for the treatment of intervertebral diseases, the biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 μm, the one side produced by melt spinning, and the fiber thickness of 0.1 to 400 μm, and the other biodegradable nonwoven fabric prepared by solution spinning Biodegradable guided tissue regeneration for periodontal disease treatment, characterized in that it is laminated and compressed 생체분해성 유도조직재생막의 제조방법에 있어서, 생체분해성 고분자물질과 안료를 혼합기에 넣어서 혼합한 후 이 혼합물을 용융방사장치에서 방사하여 부직포를 제조하는 제1공정과;A method for producing a biodegradable induced tissue regeneration membrane, comprising: a first step of preparing a nonwoven fabric by mixing a biodegradable polymer material and a pigment in a mixer and then spinning the mixture in a melt spinning apparatus; 용융방사에 의해 제조된 부직포에 기제인 생체분해성 고분자물질에 항생제를 함유시켜서 제조한 마이크로 스페어를 항생제투입용 피더를 통해서 공급하여 일측 부직포를 제조하는 제2공정과 ;A second step of producing a nonwoven fabric by supplying a micro spare prepared by containing an antibiotic in a biodegradable polymer material based on a nonwoven fabric produced by melt spinning through an antibiotic feeder; 생체분해성 고분자물질을 용매에 용해하여서 이 용액에 안료를 투입하는 제3공정과 ;A third step of dissolving the biodegradable polymer in a solvent and injecting a pigment into the solution; 제3공정에서의 용액을 용액장사장치의 용액탱크에 투입한 후 방사하여 부직포를 제조하며, 이때 고전압을 방사구금에 가하여 부직포섬유를 초극세화시킨 타측 부직포를 제조하는 제4공정과;A fourth step of manufacturing the nonwoven fabric by adding the solution in the third step into a solution tank of the solution releasing device and spinning the same, wherein a high voltage is applied to the spinneret to produce the other side of the nonwoven fabric which is extremely fine; 가열압착로울러에 의해서 일측과 타측의 부직포를 적층, 압착하여 2층으로 적층된 부직포를 제조하는 제5공정에 의해서 이루어진 것을 특징으로하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법Method of manufacturing a biodegradable inducible tissue regeneration membrane for treatment of periodontal disease, characterized in that by the fifth step of manufacturing a non-woven fabric laminated in two layers by laminating, compressing the nonwoven fabric of one side and the other side by a heat compression roller. 제2항에 있어서, 생체분해성 고분자물질은 글리콜리드, 락티드, 글리콜산, 젖산, 디옥산원, 트리메틸렌카보네이트, 카프로락톤으로 이루어진 합성 분해성 고분자 및 이들로 이루어진 공중합체와 블랜드는 물론 키토산, 셀룰로오스로 이루어진 천연 생체분해성 고분자 및 이들의 공중합체와 블랜드물인 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The biodegradable polymer according to claim 2, wherein the biodegradable polymer is a synthetic degradable polymer composed of glycolide, lactide, glycolic acid, lactic acid, dioxane source, trimethylene carbonate, caprolactone, copolymers and blends thereof, as well as chitosan and cellulose. Natural biodegradable polymer and copolymers and blends thereof made of a biodegradable induced tissue regeneration membrane for the treatment of periodontal disease, characterized in that 제2항에 있어서, 생체분해성 고분자물질의 두께가 0.1∼10mm인 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The method of claim 2, wherein the biodegradable polymer material has a thickness of 0.1 to 10 mm. 제2항에 있어서, 일측의 섬유굵기가 0.1∼0.001μm로 구성된 생체분해성 부직포로 이루어진 표면과 타측의 섬유굵기가 0.1∼400μm으로 구성된 생체분해성 부직포로 이루어진 표면의 색상을 서로 다르게 하는 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The surface of the biodegradable nonwoven fabric having a fiber thickness of one side of 0.1 to 0.001 μm and the surface of the biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 μm of the other side are different from each other. Method for preparing biodegradable induced tissue regeneration membrane for treatment of periodontal disease 제5항에 있어서, 섬유굵기가 0.1∼0.001μm로 구성된 생체분해성부직포나 섬유굵기가 0.1∼400μm로 구성된 생체분해성 부직포로 제조할 때 안료로 칼러 인덱스 솔벤트 바이올렛 13이나 솔벤트 그린 6을 부직포섬유중량에 대하여 0.01∼1wt% 첨가하여 서로 다른 색상을 띄우도록 하는 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법6. A color index solvent violet 13 or solvent green 6 as a pigment when prepared from a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 0.001 µm or a biodegradable nonwoven fabric having a fiber thickness of 0.1 to 400 µm. Method for producing a biodegradable inducible tissue regeneration membrane for treatment of periodontal disease, characterized in that to add a different color by adding 0.01 ~ 1wt% with respect to 제2항에 있어서, 부직포 제조방법은 용액방사, 용융방사, 멜트브로운으로 제조하는 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The method of claim 2, wherein the nonwoven fabric is manufactured by solution spinning, melt spinning, or melt blown. 제2항에 있어서, 방사구 또는 섬유집속위치에 고전압을 가하여 초극세 섬유로 제조된 부직포인 것을 특징으로 하는 생체분해성 유도조직재생막The biodegradable induced tissue regeneration membrane according to claim 2, wherein the non-woven fabric is made of ultra-fine fibers by applying a high voltage to a spinneret or a fiber focusing position. 제6항에 있어서, 0.1∼0.001μm의 섬유로 구성된 부직포 제조시 용액방사를 하고 0.1∼400μm인 부직포의 제조는 용융 혹은 용액방사를 하는 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The method of claim 6, wherein the production of a non-woven fabric consisting of 0.1 to 0.001μm fibers and spinning the solution and the production of 0.1 to 400μm non-woven fabric is a biodegradable induced tissue regeneration membrane for treating periodontal disease, characterized in that the melting or solution spinning Way 제9항에 있어서 용액방사시 용매는 메틸렌클로라이드, 디메틸포름아미드, 에틸아세테이트, 벤젠, 톨루엔, 메틸알코올, 에틸알코올 등인 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The method of claim 9, wherein the solvent during solution spinning is methylene chloride, dimethylformamide, ethyl acetate, benzene, toluene, methyl alcohol, ethyl alcohol, and the like. 제2항에 있어서 항생제로는 염산미노클린, 연산 테트라사이클린, 메트로니다아졸(metronidazol) 인 것을 특징으로 하는 치주질환치료용 생체분해성 유도조직재생막의 제조방법The method of claim 2, wherein the antibiotic is minochlorine hydrochloride, ophthalmic tetracycline, metronidazole (metronidazol) method of producing a biodegradable induced tissue regeneration membrane for treating periodontal disease, characterized in that
KR1019990016988A 1999-05-12 1999-05-12 Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same KR100336700B1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
KR1019990016988A KR100336700B1 (en) 1999-05-12 1999-05-12 Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
KR1019990016988A KR100336700B1 (en) 1999-05-12 1999-05-12 Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same

Publications (2)

Publication Number Publication Date
KR20000073589A true KR20000073589A (en) 2000-12-05
KR100336700B1 KR100336700B1 (en) 2002-05-13

Family

ID=19585039

Family Applications (1)

Application Number Title Priority Date Filing Date
KR1019990016988A KR100336700B1 (en) 1999-05-12 1999-05-12 Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same

Country Status (1)

Country Link
KR (1) KR100336700B1 (en)

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR100336701B1 (en) * 1999-07-26 2002-05-13 오석송 A teethridege tissue recovery membrane, and a process of preparing the same
KR100464930B1 (en) * 2001-06-30 2005-01-05 이승진 Barrier membrance for guided tissue regeneration and the preparation thereof
KR100571478B1 (en) * 2003-10-28 2006-04-17 이승진 Fibrous porous support made of biodegradable polymer and method for preparing same
KR100875189B1 (en) * 2005-08-26 2008-12-19 이화여자대학교 산학협력단 Fibrous three-dimensional porous support for tissue regeneration using electrospinning and its preparation method
KR100968231B1 (en) * 2007-12-28 2010-07-06 한양대학교 산학협력단 Nonwoven Nanofibrous Membranes for Guiding Bone Tissue Regeneration and Their Preparation Method
KR100970717B1 (en) * 2007-03-26 2010-07-16 주식회사 예스바이오 Barrier membranes for guided bone regeneration
WO2013078201A1 (en) * 2011-11-21 2013-05-30 Agratech International, Inc. Chitosan dental surgical membrane and method of making
WO2017115906A1 (en) * 2015-12-31 2017-07-06 주식회사 웰나노스 Drug releasing dental biodegradable fiber chip, and manufacturing method therefor

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR100336701B1 (en) * 1999-07-26 2002-05-13 오석송 A teethridege tissue recovery membrane, and a process of preparing the same
KR100464930B1 (en) * 2001-06-30 2005-01-05 이승진 Barrier membrance for guided tissue regeneration and the preparation thereof
KR100571478B1 (en) * 2003-10-28 2006-04-17 이승진 Fibrous porous support made of biodegradable polymer and method for preparing same
KR100875189B1 (en) * 2005-08-26 2008-12-19 이화여자대학교 산학협력단 Fibrous three-dimensional porous support for tissue regeneration using electrospinning and its preparation method
KR100970717B1 (en) * 2007-03-26 2010-07-16 주식회사 예스바이오 Barrier membranes for guided bone regeneration
KR100968231B1 (en) * 2007-12-28 2010-07-06 한양대학교 산학협력단 Nonwoven Nanofibrous Membranes for Guiding Bone Tissue Regeneration and Their Preparation Method
WO2013078201A1 (en) * 2011-11-21 2013-05-30 Agratech International, Inc. Chitosan dental surgical membrane and method of making
CN104039365A (en) * 2011-11-21 2014-09-10 农业技术国际有限公司 Chitosan dental surgical membrane and method of making
WO2017115906A1 (en) * 2015-12-31 2017-07-06 주식회사 웰나노스 Drug releasing dental biodegradable fiber chip, and manufacturing method therefor

Also Published As

Publication number Publication date
KR100336700B1 (en) 2002-05-13

Similar Documents

Publication Publication Date Title
US11828006B2 (en) Methods of orienting multifilament yarn and monofilaments of poly-4-hydroxybutyrate and copolymers thereof
Williamson et al. Gravity spinning of polycaprolactone fibres for applications in tissue engineering
Nair et al. Development of novel tissue engineering scaffolds via electrospinning
EP0668083B2 (en) Composite bioabsorbable materials and surgical articles made therefrom
KR100751733B1 (en) Method of preparing porous polymer scaffold for tissue engineering using gel spinning technique
AU2007219355A1 (en) Regenerative medicine devices and melt-blown methods of manufacture
US6031069A (en) Triblock terpolymer, its use in medical products and process for its production
KR100336700B1 (en) Biodegradable guided tissue regeneration in teriodontal dental therapy and methods of producing the same
CA2937954A1 (en) Time-dependent synthetic biological barrier material
KR101035870B1 (en) Absorbable bulky multi-filament draw textured yarn, manufacturing method thereof and medical use using them
KR20050048360A (en) Nonwoven nanofibrous membranes for guided tissue regeneration and their fabrication method
CN105970315A (en) Preparation method of medical PLLA (poly-l-lactic acid) melt-spun fibers
CN108721680A (en) A kind of polylactic acid/Lappaconitine composite fibre and its preparation and application
JPH1150369A (en) Non-woven fabric of biodegradable, conjugate, continuous fiber
CN114129778B (en) Method for preparing guided tissue regeneration membrane by combining electrostatic spinning and electrostatic spraying
WO2016095824A1 (en) Anti-infective dressing bag and fabricating method therefor
RU2500693C1 (en) Single-step method of producing polylactide-based nonwoven material and nonwoven material
JPH11286864A (en) Biodegradable non-woven fabric
CN108939168A (en) Melatonin nerve conduit composition, nerve conduit, preparation method and application thereof
CN105709280B (en) Anti-infective cladding bag of one kind and preparation method thereof
Korkjas et al. An ultrasound-enhanced electrospinning for generating multilayered nanofibrous structures
KR101643814B1 (en) Preparation method of dry-type skin care pack composed of nano fiber web and non-woven fabric, dry-type skin care pack prepared by the same, and skin care method using the dry-type skin care pack
JP2000096416A (en) Biodegradable nonwoven fabric
CN117626527A (en) Micro-nano fiber composite biological film based on electrostatic spinning technology and preparation method and application thereof
Singhi Wet spinning of poly (4-hydroxybutyrate) to produce drug-loaded fibers for controlled drug delivery applications

Legal Events

Date Code Title Description
A201 Request for examination
N231 Notification of change of applicant
E902 Notification of reason for refusal
E902 Notification of reason for refusal
E701 Decision to grant or registration of patent right
GRNT Written decision to grant
FPAY Annual fee payment

Payment date: 20130503

Year of fee payment: 12

FPAY Annual fee payment

Payment date: 20140507

Year of fee payment: 13

LAPS Lapse due to unpaid annual fee