CN101703794B - Controlled degradable surgical suture thread and fabricating method thereof - Google Patents
Controlled degradable surgical suture thread and fabricating method thereof Download PDFInfo
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- CN101703794B CN101703794B CN200910223340XA CN200910223340A CN101703794B CN 101703794 B CN101703794 B CN 101703794B CN 200910223340X A CN200910223340X A CN 200910223340XA CN 200910223340 A CN200910223340 A CN 200910223340A CN 101703794 B CN101703794 B CN 101703794B
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Abstract
The invention discloses a controlled degradable surgical suture thread and a fabricating method thereof. The innermost part is chitosan fiber core, the middle part is collagen layer, and the outermost part is ethyloic-chitosan layer. From innermost to outermost, the thickness ratio of each layer is 2:X:(3-X), wherein X is larger than 1 and smaller than 3. The value of X is related to degradation velocity of the surgical suture thread: the larger the value, the faster the degradation velocity of the surgical suture thread, and the shorter the healing period of wound suitable to be sutured; and the smaller the value, the slower the degradation velocity of the surgical suture thread, and the longer the healing period of wound suitable to be sutured. The fabricating method of the surgical suture thread comprises: (1) preparing chitosan fiber core and collagen; (2) covering a layer of collagen outside the chitosan fiber; (3) covering a layer of ethyloic-chitosan outside the collagen cover of the chitosan fiber; (4) processing and polishing the suture thread prepared in (3) by an automatic coreless grinder, connecting with suture needles of different models to prepare into a finish product of surgical suture thread. The technical scheme of the invention has plentiful advantages: controllable degradation velocity, high tension strength, improved biocompatibility and anti-infectious property, quick wound healing, no obvious scars, good biocompatibility, etc.
Description
Technical field
The invention belongs to medical instruments field, relate to specifically controlled degradable surgical suture thread and manufacture method thereof that a kind of human body can absorb.
Background technology
Surgical sutures is one of the most basic in surgical operation, most important material, is mainly used in the various sewing hemostasis of organizing, residual cavity locking and organize involutory.Surgical sutures mainly is divided into non-absorbable suture line and the large class of absorbable suture two, and absorbable suture is compared with non-absorbable suture line, and its main advantages is: 1. no antigen (only when absorbing, producing slight tissue reaction); 2. without pyrogenicity; 3. wound healing is complete; 4. without taking out stitches, alleviate patient's misery, reduced the chance of bringing out infection; Thereby absorbable suture is the trend of surgical sutures development.From making raw material, come minute, the absorbable suture of clinical practice mainly contains: 1. natural material; 2. chemical synthetic material; 3. the complex of natural material and chemical synthetic material.Wherein, because the surgical sutures of natural material manufacture meets the social current of consumption concept and the back to nature of environmental protection, be subject to more the support of national policy.
In the natural material surgical sutures, collagen class stitching thread is (as applied for 03102533.1, 89108465.7, 200910013608.7 disclosed), the crust material stitching thread is (as application CN20031029976, 20030603 is disclosed), chitosan class stitching thread (as disclosed in applied for 03129976.8) etc. has market prospect, but large-scale application not yet clinically, its major defect is: collagen stitching thread degradation in vivo is fast, absorb early, be unfavorable for wound healing and alleviate cicatrization (hot Flos Lonicerae. medical stitching thread Biodegradable fiber. textile technology progress, 3:12-13, 2005, Fan Yaoming. the progress of suture. nonwoven techniques and fabrics for industrial use. weaving Leader, 1:58-63,2006), though existing chitin, chitosan stitching thread have certain antibacterial ability, but degraded is fast, especially the chitosan molecule that deacetylation is lower is subject to the more remarkable (Zhang Chunxue of the Degradation of enzyme, Yuan Xiaoyan, Shengjing city. Polymer Fibrous Materials for Biomedical Application. the macromolecule circular, 12:34-38,2006), thereby tensile strength is not high enough, particularly knot strength is poor, cause sutural degradation speed and speed of wound healing be not complementary adaptation (Zhao Jingna. the research application present situation of medical operation suture thread. external silk .2:26-29,2008, Yin Yan, He little Wei, yellow strong, Yu Shujuan. the application of chitosan in medical absorbable suture. Chinese beet sugar industry, 4:28-31,2006).The main cause that produces above defect is, the mechanical strength of these natural materials itself is just not high, after implanting by operation stitching, under the effect of body fluid immersion and enzyme, can degrade, sutural mechanical strength is reduced, miopragia or forfeiture too early.
In sum, existing collagen or chitosan class can absorb surgical sutures and have following defect: (1) degraded and absorbed speed is asynchronous with wound healing speed, the biggest problem that existing collagen or chitosan class can absorb surgical sutures is that degraded and absorbed speed is difficult to synchronize with wound healing speed, cause sutural effect to be made a discount, if degraded and absorbed speed greatly faster than wound healing speed, can make the stitching thread effect weaken; If degraded and absorbed speed is much slower than wound healing speed, can cause wound healing after stitching thread still remain in human body, can the induce tissue inflammatory reaction and pain; (2) tensile strength and knot strength relative deficiency, reason due to material itself, collagen or the sutural tensile strength of chitosan class and knot strength relatively not high (Zhao Jingna. the research application present situation of medical operation suture thread. external silk .2:26-29,2008; Yin Yan, He little Wei, yellow strong, Yu Shujuan. the application of chitosan in medical absorbable suture. Chinese beet sugar industry, 4:28-31,2006); (3) chitosan class surgical sutures antibacterial ability relatively poor (Yin Yan, He little Wei, yellow strong, Yu Shujuan. the application of chitosan in medical absorbable suture. Chinese beet sugar industry, 4:28-31,2006; Cuero R.G.Antimicrobial action ofexogenous chitosan.EXS.87:315-333,1999).
Summary of the invention
The objective of the invention is in order to solve the existing above-mentioned defect that can absorb surgical sutures, a kind of controlled degradable surgical suture thread by the new material made and manufacture method thereof are proposed, it has better anti-microbial property, greatly reduced the chance of bringing out wound infection, and wound healing is fast, there is no obvious cicatrix, have broad prospects in clinical practice.
Realize that above-mentioned purpose technical scheme of the present invention is, the controlled degradable surgical suture thread outermost is the carboxymethyl chitosan layer, centre is collagen layer, the inside is the chitin fiber core, each layer thickness ratio is, chitin fiber core: collagen layer: carboxymethyl chitosan layer=2: X: (3-X), 1<X<3 wherein.The size of X value is relevant with the stitching thread degradation rate: the X value is larger, and the stitching thread degradation rate is faster, and the wound healing phase that is suitable for stitching is shorter; Otherwise the X value is less, the stitching thread degradation rate is slower, and the wound healing phase that is suitable for stitching is longer.
Technical scheme of the present invention also relates to above-mentioned controlled degradable surgical suture thread manufacture method, and the method comprises the following steps: (1) prepares chitin fiber core and collagen; (2) the outer bread one deck collagen of chitin fiber; (3) bread one deck carboxymethyl chitosan outside the collagen coating of chitin fiber; (4) stitching thread prepared by (3) step carries out being connected and making the surgical sutures finished product with the sewing needle of different model after automatic coreless grinding machine processing polished.
Above-mentioned steps (2) with in step (3), adopted respectively cross-linking agent to be connected chitin fiber core and middle collagen layer, and middle collagen layer and outmost carboxymethyl chitosan layer, the cross-linking agent here can be the glutaraldehyde that concentration is 0.25%.
The above-mentioned method for preparing the chitin fiber core is: by chitosan, (molecular weight is for being greater than 1.0 * 10
6deacetylation is more than 90%) be dissolved in 5～6% acetic acid,diluted solution, add 2～3% carbamide, 0.3% zinc acetate as auxiliary agent, be prepared into the spinning solution containing 2～6% chitosans, spinning solution by filtering, after vacuum outgas, be that 0.2～3mm spinning head sprays in 3～8%NaOH solution it is solidified through diameter, then through 2～5 times of stretching, wash, under tension state, in 70 ℃ of dry 1h, final acquisition has the chitin fiber of sufficient mechanical strength.
Method prepared by above-mentioned collagen is: get fresh mammiferous tendon, remove fascia, fat, frozen section, with 37 ℃ of digestion 36h of 0.5% pancreatin, by 0.5mol/L acetic acid swelling for the tendon sheet of digestion, mix, add saturated NaCl precipitating collagen, dialysis precipitating liquid, purification collagen.
Method prepared by above-mentioned collagen can be also: get fresh mammiferous skin, washing, unhairing, defat, be cut into the fritter of 1～3cm, adds appropriate pepsin and acetum, place 3～5 days for 4 ℃, intermittent stirring, after extracting liquid filtering, add NaCl to ultimate density be 10%, the 1500rpm centrifugalize obtains the collagen precipitation, it is used to the 0.5mol/L acetate dissolution, and the TrisHCl buffer of pH7.5 and distilled water be dialysis alternately, until inspection does not measure Cl
-till, obtain collagen purification solution.
Above-mentioned outside chitin fiber the method for bread one deck collagen be: at ambient temperature, prepare saturated collagen solution, after putting into chitin fiber immersion 3min, dry, with the glutaraldehyde cross-linking of concentration 0.25%, distilled water wash, gradient ethanol, acetone dehydration, after drying, can dry step increase collagen layer thickness by repeating immersion.
The method of the above-mentioned carboxymethyl chitosan of coated outside one deck at chitin fiber collagen coating is: under heating condition, prepare saturated carboxymethyl chitosan sugar juice, after being cooled to room temperature, after putting into the chitin fiber immersion 3min of collagen coating, dry the glutaraldehyde cross-linking that is 0.25% by concentration, distilled water wash, gradient ethanol, acetone dehydration, after drying, can increase carboxymethyl chitosan thickness by repeatedly soaking to dry.
The advantage that technical scheme of the present invention has comprises: 1. degradation speed is controlled, surgical sutures of the present invention be take chitin fiber as core, by special chemical reaction at the surface-crosslinked last layer collagen layer of chitin fiber, again at the crosslinked last layer carboxymethyl chitosan layer in collagen layer outside, the carboxymethyl chitosan layer, collagen layer and chitosan core are degraded under different enzyme effects in human body, due to these three kinds of composition locus differences, the priority sequence of operation of enzyme is also different, carboxymethyl chitosan and degradation of chitosan are slow, collagen degradation is fast, reach the purpose of control degradation speed by the mass ratio of controlling the three, make sutural degradation rate consistent with wound healing speed, 2. tensile strength is high, pliability good, knotting is convenient, existing chitin, the sutural tensile strength relative deficiency of chitosan, chemical crosslinking effect meeting by packaging technique improves sutural tensile strength greatly, stitching thread is more easily operated, overcome the shortcoming that pure collagen stitching thread absorption phase is short and wet knot strength is low simultaneously.Surgical sutures ultimate strength>500N of the present invention, tie greatly ultimate strength>300N, meets the relevant regulations of 109 pages of 90 editions two appendix of Chinese Pharmacopoeia; 3. biocompatibility and anti-infection property have been improved, the present invention has improved the biocompatibility of chitin fiber by increasing collagen layer, be positioned at the outermost carboxymethyl chitosan of stitching thread and have better anti-inflammation effect than chitosan, wound that can should secondary suture to some carries out primary suture; 4. wound healing fast, without obvious cicatrix, chitosan and collagen have the effect that promotes wound healing, reduces cicatrix, after healing, wound surface is similar to normal structure, without obvious cicatrix; 5. good biocompatibility, zoopery of the present invention shows, stitching thread of the present invention has good biocompatibility (comprising histocompatibility, blood compatibility and immunity), without allergy, stimulation, haemolysis and inflammatory reaction, without other untoward reaction.
The accompanying drawing explanation
Fig. 1 is the sectional structure chart of controlled degradable surgical suture thread of the present invention;
1-1, carboxymethyl chitosan layer in figure; 1-2, collagen layer; 1-3, chitin fiber core;
Fig. 2 is each layer thickness definition of controlled degradable surgical suture thread of the present invention figure; 1-1L in figure is carboxymethyl chitosan layer thickness (3-X), and 1-2L is collagen layer thickness (X), and 1-3L is chitin fiber core thickness (2), is also the radius of 1-3.
Fig. 3 is the manufacturing flow chart of operation suture thread of the present invention.
The specific embodiment
Below technical scheme of the present invention is specifically described, as shown in the figure, Fig. 1 is the sectional structure chart of controlled degradable surgical suture thread of the present invention, and in figure, the structure of controlled degradable surgical suture thread from the inside to the outside, be followed successively by, chitin fiber core 1-3, collagen layer 1-2 and carboxymethyl chitosan layer 1-1, each layer thickness ratio is, chitin fiber core: collagen layer: carboxymethyl chitosan layer=2: X: (3-X), 1<X<3 wherein.The size of X value is relevant with the stitching thread degradation rate: the X value is larger, and the stitching thread degradation rate is faster, and the wound healing phase that is suitable for stitching is shorter; Otherwise the X value is less, the stitching thread degradation rate is slower, and the wound healing phase that is suitable for stitching is longer.For example, for soft tissue laceration or operative incision, usually to carry out 4 layered sutures and close, that is: Musclar layer (stitching thread of the present invention that the model that can use X=1 is 3#, healing stage is 12-15 days); Fascia layer (stitching thread of the present invention that the model that can use X=0.5 is 3#, healing stage is 14-17 days); Hypodermis layer (stitching thread of the present invention that the model that can use X=1.5 is 1#, healing stage is 10-13 days); Skin layer (stitching thread of the present invention that the model that can use X=2 is 1#, healing stage is 8-11 days).
Fig. 2 is each layer thickness definition of controlled degradable surgical suture thread of the present invention figure, 1-1L in figure is carboxymethyl chitosan layer thickness (3-X), 1-2L is collagen layer thickness (X), and 1-3L is chitin fiber core thickness (2), is also the radius of 1-3.
Fig. 3 is the manufacturing flow chart of controlled degradable surgical suture thread of the present invention, and when manufacturing controlled degradable surgical suture thread of the present invention, at first with highly purified chitosan, (relative molecular mass is for being greater than 1.0 * 10 as shown in the figure
6, deacetylation is more than 90%) be raw material, adopt wet spinning process to prepare chitin fiber, the spinning head of the different pore size of use customization prepares the chitin fiber of different pore size, stitching thread as different model is made raw material, concrete grammar is, chitosan is dissolved in 5～6% acetic acid,diluted solution, add 2～3% carbamide, 0.3% zinc acetate is as auxiliary agent, be prepared into the spinning solution containing 2～6% chitosans, to filter, spinning solution after vacuum outgas, through diameter, be that 0.2～3mm spinning head sprays in 3～8%NaOH solution it is solidified, again through 2～5 times of stretchings, washing, under tension state in 70 ℃ of dry 1h, the final chitin fiber with sufficient mechanical strength that obtains, carry out the collagen preparation after completing the chitin fiber preparation, concrete preparation method is: get fresh mammiferous tendon, remove fascia, fat, frozen section, with 37 ℃ of digestion 36h of 0.5% pancreatin, by 0.5mol/L acetic acid swelling for the tendon sheet of digestion, mix, add saturated NaCl precipitating collagen, dialysis precipitating liquid, purification collagen, method prepared by collagen can be also: get fresh mammiferous skin, washing, unhairing, defat, be cut into the fritter of 1～3cm, adds appropriate pepsin and acetum, place 3～5 days for 4 ℃, intermittent stirring, after extracting liquid filtering, add NaCl to ultimate density be 10%, the 1500rpm centrifugalize obtains the collagen precipitation, it is used to the 0.5mol/L acetate dissolution, and the TrisHCI buffer of pH 7.5 and distilled water be dialysis alternately, until inspection does not measure Cl
-till, obtain collagen purification solution.
Carry out bread one deck collagen outside chitin fiber after completing chitin fiber core and collagen preparation, concrete grammar is: at ambient temperature, prepare saturated collagen solution, after putting into chitin fiber immersion 3min, dry, with the glutaraldehyde cross-linking of concentration 0.25%, distilled water wash, gradient ethanol, acetone dehydration, after drying, can dry step increase collagen layer thickness by repeating immersion.
The 3rd step is carried out the coated outside one deck carboxymethyl chitosan at chitin fiber collagen coating, concrete grammar is: under heating condition, prepare saturated carboxymethyl chitosan sugar juice, after being cooled to room temperature, after putting into the chitin fiber immersion 3min of collagen coating, dry, the glutaraldehyde cross-linking that is 0.25% by concentration, distilled water wash, gradient ethanol, acetone dehydration, after drying, can increase carboxymethyl chitosan thickness by repeatedly soaking to dry.
Finally, the controlled degradable surgical suture thread of above-mentioned manufacture is carried out after automatic coreless grinding machine processing polished, with the sewing needle of different model, be connected and make the controlled degradable surgical suture thread finished product.
Technique scheme has only embodied the optimal technical scheme of technical solution of the present invention, and those skilled in the art have all embodied principle of the present invention to some changes that wherein some part may be made, within belonging to protection scope of the present invention.
Claims (7)
1. controlled degradable surgical suture thread, it is characterized in that this stitching thread forms by three layers, outermost is carboxymethyl chitosan layer (1-1), and centre is collagen layer (1-2), and the inside is chitin fiber core (1-3), described chitin fiber core, the thickness proportion of collagen layer and carboxymethyl chitosan layer is 2:X:(3-X), 1<X<3 wherein, the size of X value is relevant with the stitching thread degradation rate: the X value is larger, the stitching thread degradation rate is faster, and the wound healing phase that is suitable for stitching is shorter; Otherwise the X value is less, the stitching thread degradation rate is slower, and the wound healing phase that is suitable for stitching is longer.
2. controlled degradable surgical suture thread manufacture method according to claim 1, is characterized in that, the method comprises the following steps:
(1) prepare chitin fiber core and collagen;
(2) the outer bread one deck collagen of chitin fiber;
(3) wrap again one deck carboxymethyl chitosan in the collagen coating outside of chitin fiber;
(4) stitching thread prepared by (3) step carries out being connected and making the surgical sutures finished product with the sewing needle of different model after automatic coreless grinding machine processing polished;
Above-mentioned steps (2) has adopted respectively cross-linking agent to be connected chitin fiber core and collagen layer with in step (3), and collagen layer and carboxymethyl chitosan layer;
In above-mentioned steps (1), the preparation method of chitin fiber core is: chitosan is dissolved in 5～6% acetic acid,diluted solution, add 2～3% carbamide, 0.3% zinc acetate as auxiliary agent, be prepared into the spinning solution containing 2～6% chitosans, by the spinning solution after filtration, vacuum outgas, through diameter, be that 0.2～3mm spinning head sprays in 3～8% NaOH solution it is solidified, again through 2～5 times of stretchings, washing, under tension state, in 70 ℃ of dry 1h, final acquisition has the chitin fiber of sufficient mechanical strength.
3. according to the controlled degradable surgical suture thread manufacture method of claim 2, it is characterized in that, cross-linking agent is the glutaraldehyde that concentration is 0.25%.
4. according to the controlled degradable surgical suture thread manufacture method of claim 3, it is characterized in that, method prepared by collagen is: get fresh mammiferous tendon, remove fascia, fat, frozen section, with 37 ℃ of digestion 36h of 0.5% pancreatin, 0.5 mol/L acetic acid swelling for the tendon sheet by digestion, mix, and adds saturated NaCl precipitating collagen, dialysis precipitating liquid, purification collagen.
5. according to the controlled degradable surgical suture thread manufacture method of claim 3, it is characterized in that, method prepared by collagen is: get fresh mammiferous skin, washing, unhairing, defat, be cut into the fritter of 1～3cm, add appropriate pepsin and acetum, place 3～5 days for 4 ℃, intermittent stirring, after extracting liquid filtering, add NaCl to ultimate density be 10%, the 1500rpm centrifugalize obtains the collagen precipitation, it is used to the 0.5mol/L acetate dissolution, and the TrisHCI buffer of pH7.5 and distilled water be dialysis alternately, until inspection does not measure Cl
-till, obtain collagen purification solution.
6. according to the controlled degradable surgical suture thread manufacture method of claim 3, it is characterized in that, outside chitin fiber, the method for bread one deck collagen is: at ambient temperature, prepare saturated collagen solution, after putting into chitin fiber immersion 3min, dry, with the glutaraldehyde cross-linking of concentration 0.25%, distilled water wash, gradient ethanol, acetone dehydration, after drying, by repeating immersion, dry step increase collagen layer thickness.
7. according to the controlled degradable surgical suture thread manufacture method of claim 3, it is characterized in that, method at coated outside one deck carboxymethyl chitosan of chitin fiber collagen coating is: under heating condition, prepare saturated carboxymethyl chitosan sugar juice, after being cooled to room temperature, after putting into the chitin fiber immersion 3min of collagen coating, dry, the glutaraldehyde cross-linking that is 0.25% by concentration, distilled water wash, gradient ethanol, acetone dehydration, after drying, increase carboxymethyl chitosan thickness by repeatedly soaking to dry.
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| CN102552964B (en) * | 2012-01-09 | 2014-04-09 | 李育强 | Nano silver chitosan composite antibacterial composition, adhesive bandage and preparation method of adhesive bandage |
| CN104069541B (en) * | 2013-12-04 | 2017-02-22 | 江西龙腾生物高科技有限公司 | Preparation method of collagen suture line |
| CN104173083B (en) * | 2014-09-03 | 2016-10-26 | 杭州爱普医疗器械股份有限公司 | A kind of medical treatment suture and preparation method thereof |
| CN105770978A (en) * | 2016-03-21 | 2016-07-20 | 江苏广达医材集团有限公司 | Biodegradable medical abdominal surgical suture material |
| CN108273119B (en) * | 2018-03-08 | 2020-11-20 | 戴庆涛 | Surgical suture for gastrointestinal surgery and manufacturing method thereof |
| CN108642858B (en) * | 2018-04-26 | 2020-08-21 | 海斯摩尔生物科技有限公司 | Preparation method of controllable degradable medical suture |
| CN108660737B (en) * | 2018-04-26 | 2020-08-25 | 东华大学 | Preparation method of high-strength medical suture |
| CN108853562A (en) * | 2018-09-13 | 2018-11-23 | 王传强 | A kind of absorbable pre-knotted operation suture thread of thoracic surgery sustained antiinfective |
| CN111134746A (en) * | 2019-12-30 | 2020-05-12 | 山东省肿瘤防治研究院（山东省肿瘤医院） | Surgical suture for gastrointestinal surgery and manufacturing method thereof |
| CN111790001A (en) * | 2020-07-30 | 2020-10-20 | 山东中医药大学 | Method for manufacturing absorbable surgical suture with three-layer annular structure for healing promotion and infection resistance |
| CN112301496A (en) * | 2020-11-03 | 2021-02-02 | 上海普平生物科技有限公司 | Preparation method of controllable degradation surgical suture |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5618312A (en) * | 1995-10-31 | 1997-04-08 | Bio-Engineering Laboratories, Ltd. | Medical materials and manufacturing methods thereof |
| CN1403163A (en) * | 2002-10-23 | 2003-03-19 | 东南大学 | Absorbable fiber reinforced multilayer film material and its prepn |
| CN1552466A (en) * | 2003-06-03 | 2004-12-08 | 天津市久康生物工程开发有限公司 | Absorbable medical chitin suture lines and their production |
| CN101250759A (en) * | 2008-04-07 | 2008-08-27 | 宁阳华兴海慈新材料有限公司 | Medical chitosan fibre and preparation method thereof |
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| CN201533923U (en) * | 2009-11-18 | 2010-07-28 | 中国人民解放军第二炮兵总医院 | Controllably degraded surgery suture |
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5618312A (en) * | 1995-10-31 | 1997-04-08 | Bio-Engineering Laboratories, Ltd. | Medical materials and manufacturing methods thereof |
| CN1403163A (en) * | 2002-10-23 | 2003-03-19 | 东南大学 | Absorbable fiber reinforced multilayer film material and its prepn |
| CN1552466A (en) * | 2003-06-03 | 2004-12-08 | 天津市久康生物工程开发有限公司 | Absorbable medical chitin suture lines and their production |
| CN101250759A (en) * | 2008-04-07 | 2008-08-27 | 宁阳华兴海慈新材料有限公司 | Medical chitosan fibre and preparation method thereof |
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