CN103654999B - Nerve rehabilitating tube support of multiple structure and preparation method thereof - Google Patents
Nerve rehabilitating tube support of multiple structure and preparation method thereof Download PDFInfo
- Publication number
- CN103654999B CN103654999B CN201310639284.4A CN201310639284A CN103654999B CN 103654999 B CN103654999 B CN 103654999B CN 201310639284 A CN201310639284 A CN 201310639284A CN 103654999 B CN103654999 B CN 103654999B
- Authority
- CN
- China
- Prior art keywords
- solution
- tube
- support
- poly
- lactic acid
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Abstract
This nerve rehabilitating tube support providing a kind of multiple structure and preparation method thereof, to meet the needs of neural tissue engineering.Three structures of the inner tube, the tube and the outer tube being divided on nerve rehabilitating tube supporting structure, the material composition of its each of the configurations is incomplete same, and interior pipe is poly-dl-lactide, and middle pipe is lactic acid caprolactone copolymer, and outer tube is Poly-L-lactic acid.Nerve rehabilitating tube support is characterised by, support has certain mechanical performance, flexible, can extrude, and its hot strength is 10 ~ 15 MPa;Stretch-proof shape becomes 5 ~ 13%.When support is bent or after squeezing action, original form can be returned to.
Description
Technical field
The present invention relates to a kind of Biodegradable high-molecular nerve rehabilitating tube support with multiple structure and preparation method thereof, belong to neural tissue engineering field.
Background technology
After peripheral nerve injury, the replacement reparation of defect is always up a global problem.The current clinical main autologous neural transplantation reparation peripheral nerve defection that adopts, but there is autologous neural transplantation existence and patient will be brought secondary damage, and operating difficulty is big, and patient is difficult to problems such as returning to one's perfect health.Artificial nerve graft is used to repair, as support, the study hotspot that peripheral nerve defection is peripheral nerve field in recent years, it is desirable to substitute nerve autograft and repair peripheral nerve defection, but occur currently without desirable product.
Research at present thinks that rational CO2 laser weld support should meet following requirement:
(1) the material biodegradable of support, and degradation rate should be able to regulate；
(2) support has certain mechanical performance, it is possible to provide enough growing spaces and mechanical strength for nerve；
(3) there is good biocompatibility, it is impossible to affect tissue activity and function.
Big quantity research shows, Poly-L-lactic acid, poly-dl-lactide and lactic acid caprolactone copolymer, there is good biocompatibility, three kinds of materials are combined the performance that can effectively regulate material, Poly-L-lactic acid and poly-dl-lactide can reinforcing material intensity, lactic acid caprolactone copolymer can reinforcing material toughness and elastic modelling quantity.
Degradation rate can be realized by the degradable macromolecule tubular bracket prepared by electrostatic spinning technique should be able to regulate, polymeric membrane as simple is compared, energy analog cell outer surface substrate microscopic appearance and structure, good biocompatibility, reach the adhesion of cell and the purpose of growth.But owing to electrostatic spinning lacks necessary mechanical strength, this cultivates at implant inner anterior quadrant to such support and makes troubles with implant surgery operation.Although incorporating other biological material, but all can not fully meet enough mechanical strengths and Growth of Cells space.
So, it is presently required a kind of ability that can play supporting and space and can have again plantation and the propagation of the tissue relevant cell that loose structure provides rational three dimensions to be easy to nerve injury.
Summary of the invention
In order to overcome the deficiencies in the prior art, the present invention provides nerve rehabilitating tube support with three-decker prepared by a kind of biodegradable macromolecule and preparation method thereof, applies to neural tissue engineering field.
The nerve rehabilitating tube support of a kind of multiple structure, it is characterised in that nerve rehabilitating tube support has inner tube, the tube and the outer tube three-decker, the macromolecular material composition difference of its each of the configurations, interior pipe is poly-dl-lactide, and middle pipe is lactic acid caprolactone copolymer, and outer tube is Poly-L-lactic acid.
The weight average molecular weight of poly-dl-lactide component is than for Poly-L-lactic acid: dextrorotation polylactic acid=7:3, and the weight average molecular weight of lactic acid caprolactone copolymer component is than for Poly-L-lactic acid: polycaprolactone=7:3.
The internal diameter of nerve rehabilitating tube support is 2～4 millimeters, and external diameter is 2.2～4.2 millimeters, and length is 10～200 millimeters.
Interior tube thickness is 0.6～0.8 millimeter, and the thickness of middle pipe is 0.1～0.2 millimeter, and the thickness of outer tube is 0.1～0.4 millimeter.
The average fibre diameter of middle pipe is 240～450 nanometers, and the average fibre diameter of outer tube is 1.1～1.4 microns.
The preparation method of the nerve rehabilitating tube support of a kind of multiple structure, it is characterised in that comprise the steps:
(1) being dissolved in dichloromethane by poly-dl-lactide, heating condensing reflux dissolve, and form solution A；
(2) by dissolved for lactic acid caprolactone copolymer solution in dichloromethane with N-dimethylformamide mixed solvent, solution B is formed；
(3) by dissolved for Poly-L-lactic acid solution in dichloromethane and N-dimethylformamide mixed solvent in, form solution C；
(4) inserting in above-mentioned solution A with bar molds, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10 centimetres with reception device distance；The solution B obtained in step (2) is loaded in syringe, interior pipe and bar molds is vertically fixed on metal rotation device, rotating collection electrostatic spinning；
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10 centimetres with reception device distance；The solution C obtained in step (3) is loaded in syringe, interior pipe and bar molds is vertically fixed on metal rotation device, rotating collection electrostatic spinning；
(7) lyophilization processes 12 hours, is soaked 10 minutes through bubble by support, can be separated with bar molds by support in 40 DEG C of warm water.
In solution A, solution B and solution C, the concentration range of macromolecular material is followed successively by 10～25%, 1～1.5% and 1～1.5%；In solution B and solution C, dichloromethane is 7:3 with the volume ratio of N-dimethylformamide.
Bar molds diameter is 2～3 millimeters.
When adopting tubular construction in electrostatic spinning technique preparation, injection rate is 0.4mL/h, injection volume 0.5～1 milliliter.
When adopting electrostatic spinning technique to prepare outer tube structure, injection rate is 0.4mL/h, injection volume 0.5～1 milliliter.
Material used by nerve rehabilitating tube support provided by the invention is the Polymer materialspreparation that biology can be degradable, has good biocompatibility, and the relative rate of increase of cell (RGR) is 1 grade；Support has independent interior China and foreign countries three layers tubular structure, and interior pipe is solid Poly-L-lactic acid, strengthens the mechanical strength of support, recovers original form after can keeping support extruding or Bending Deformation；The different size of fiber of middle pipe and outer tube provides the space of necessity for cell attachment and growth.
Preparation technology provided by the invention is simple, it is not necessary to special large-scale instrument, and with low cost, preparation time is short.
Accompanying drawing explanation
Fig. 1 is the perspective view of nerve rehabilitating tube support prepared by the present invention.1 is outer tube, and 2 is middle pipe, and 3 is interior pipe.
Fig. 2 is the three-decker schematic diagram of nerve rehabilitating tube support prepared by the present invention.1 is the micrometer fibers structure of outer tube, and 2 is the nanofibrous structures of middle pipe, and 3 is the solid construction of interior pipe.
Detailed description of the invention
Embodiment 1:
Step is as follows:
(1) weighing 3g poly-dl-lactide and be dissolved in the dichloromethane of 20ml, heating condensing reflux dissolve 1 hour, form solution A；
(2) weighing 0.3g lactic acid caprolactone copolymer and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution B；
(3) weighing 0.6g Poly-L-lactic acid and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution C；
(4) inserting in above-mentioned solution A with the stainless steel bar that diameter is 3mm, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution B obtained in step (2) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 0.5mL, obtains the middle pipe of nanofiber composition.
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution C obtained in step (3) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 0.7mL, obtains the outer tube of micrometer fibers composition.
(7) lyophilization processes 12h, through bubble, support is soaked in 40 DEG C of warm water 10min, can be separated with stainless steel bar by support.
The nerve rehabilitating tube support of gained has inner tube, the tube and the outer tube three-decker, is hollow tubular structures.Stent length is 200mm, it is possible to bending and stretching, has stronger toughness and enabling capabilities, and its hot strength is 15MPa;Stretch-proof shape becomes 13%.Adopting vernier caliper measurement, its interior diameter is about 3.1mm, and external diameter is about 4.3mm.Scanned electron microscope observation, interior tube thickness is about 0.8mm, and the thickness of middle pipe is about 0.15mm, and the thickness of outer tube is about 0.25mm；The average fibre diameter of outer tube is 1.1 μm, and the average fibre diameter of middle pipe is 430nm.
Embodiment 2:
Step is as follows:
(1) weighing 2g poly-dl-lactide and be dissolved in the dichloromethane of 20ml, heating condensing reflux dissolve 1 hour, form solution A；
(2) weighing 0.3g lactic acid caprolactone copolymer and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution B；
(3) weighing 0.6g Poly-L-lactic acid and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution C；
(4) inserting in above-mentioned solution A with the stainless steel bar that diameter is 3mm, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution B obtained in step (2) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 1mL, obtains the middle pipe of nanofiber composition.
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution C obtained in step (3) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 0.2mL, obtains the outer tube of micrometer fibers composition.
(7) lyophilization processes 12h, through bubble, support is soaked in 40 DEG C of warm water 10min, can be separated with stainless steel bar by support.
The nerve rehabilitating tube support of gained has inner tube, the tube and the outer tube three-decker, is hollow tubular structures.Stent length is 100mm, it is possible to bending and stretching, has stronger toughness and enabling capabilities, and its hot strength is 12MPa;Stretch-proof shape becomes 11%.Adopting vernier caliper measurement, its interior diameter is about 3.0mm, and external diameter is about 3.8mm.Scanned electron microscope observation, interior tube thickness is about 0.6mm, and the thickness of middle pipe is about 0.1mm, and the thickness of outer tube is about 0.1mm；The average fibre diameter of outer tube is 1.1 μm, and the average fibre diameter of middle pipe is 430nm.
Embodiment 3:
Step is as follows:
(1) weighing 3g poly-dl-lactide and be dissolved in the dichloromethane of 20ml, heating condensing reflux dissolve 1 hour, form solution A；
(2) weighing 0.2g lactic acid caprolactone copolymer and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution B；
(3) weighing 0.8g Poly-L-lactic acid and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution C；
(4) inserting in above-mentioned solution A with the stainless steel bar that diameter is 2mm, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution B obtained in step (2) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 0.5mL, obtains the middle pipe of nanofiber composition.
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution C obtained in step (3) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 0.7mL, obtains the outer tube of micrometer fibers composition.
(7) lyophilization processes 12h, through bubble, support is soaked in 40 DEG C of warm water 10min, can be separated with stainless steel bar by support.
The nerve rehabilitating tube support of gained has inner tube, the tube and the outer tube three-decker, is hollow tubular structures.Stent length is 100mm, it is possible to bending and stretching, has stronger toughness and enabling capabilities, and its hot strength is 10MPa;Stretch-proof shape becomes 11%.Adopting vernier caliper measurement, its interior diameter is about 2.0mm, and external diameter is about 4.2mm.Scanned electron microscope observation, interior tube thickness is about 0.8mm, and the thickness of middle pipe is about 0.1mm, and the thickness of outer tube is about 0.3mm；The average fibre diameter of outer tube is 1.4 μm, and the average fibre diameter of middle pipe is 240nm.
Embodiment 4:
Step is as follows:
(1) weighing 5g poly-dl-lactide and be dissolved in the dichloromethane of 20ml, heating condensing reflux dissolve 1 hour, form solution A；
(2) weighing 0.2g lactic acid caprolactone copolymer and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution B；
(3) weighing 0.8g Poly-L-lactic acid and be dissolved in the dichloromethane of 10ml with N-dimethylformamide (volume ratio is 7:3) mixed solvent, heating condensing reflux dissolve 1 hour, form solution C；
(4) inserting in above-mentioned solution A with the stainless steel bar that diameter is 3mm, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution B obtained in step (2) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 1mL, obtains the middle pipe of nanofiber composition.
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10cm with reception device distance.The solution C obtained in step (3) being loaded in syringe, be vertically fixed on metal rotation device by interior pipe and stainless steel bar, the speed of 50rpm rotates.Injection rate is 0.4mL/h, injection volume 1mL, obtains the outer tube of micrometer fibers composition.
(7) lyophilization processes 12h, through bubble, support is soaked in 40 DEG C of warm water 10min, can be separated with stainless steel bar by support.
The nerve rehabilitating tube support of gained has inner tube, the tube and the outer tube three-decker, is hollow tubular structures.Stent length is 100mm, it is possible to bending and stretching, has stronger toughness and enabling capabilities, and its hot strength is 11MPa;Stretch-proof shape becomes 10%.Adopting vernier caliper measurement, its interior diameter is about 3.2mm, and external diameter is about 4.4mm.Scanned electron microscope observation, interior tube thickness is about 0.6mm, and the thickness of middle pipe is about 0.2mm, and the thickness of outer tube is about 0.4mm；The average fibre diameter of outer tube is 1.4 μm, and the average fibre diameter of middle pipe is 240nm.
Embodiment 5:
Nerve rehabilitating tube support prepared in embodiment 1 ~ 4 is carried out Study on biocompatibility.
Nerve rehabilitating tube support scalpel prepared in embodiment 1 ~ 4 is cut into the segment that length is about 0.5cm.Ultraviolet sterilization is individually positioned in 48 orifice plates after processing.Every hole inoculates 10 respectively5Individual HMS cell, cultivates 24 hours in cell culture incubator, with CCK-8(days roots of cytoactive test kit, China) carry out cytoactive test, the OD value under the optical filter of 450nm wavelength has reacted cell gross activity.105After individual HMS cell is seeded in a hole, it does not have the cell of support and equal number cultivate in incubator 24 hours be matched group.Calculate the relative rate of increase of cell (RGR) below equation:
RGR (%)=(sample OD/ compares OD) * 100%
The relative rate of increase of cell and toxic reaction classification are in Table 1.
The table 1 nerve rehabilitating tube relative rate of increase of support cell and toxic reaction classification
Note: toxic reaction classification: according to RGR by as follows for the toxic reaction classification of material: 0 grade is RGR >=100%;1 grade is 80% ~ 99%;2 grades is 50% ~ 79%;3 grades is 30% ~ 49%;4 grades is 0% ~ 29%
As seen from the above table, the relative rate of increase RGR(% of cell of the support in embodiment 1 ~ embodiment 4) it is all I level, biocompatibility reaction is good.
Claims (3)
1. the nerve rehabilitating tube support of a multiple structure, it is characterized in that, nerve rehabilitating tube support has inner tube, the tube and the outer tube three-decker, interior pipe is solid construction, and middle pipe is nanofibrous structures, and outer tube is micrometer fibers structure, the macromolecular material composition difference of its each of the configurations, interior pipe is poly-dl-lactide, and middle pipe is lactic acid caprolactone copolymer, and outer tube is Poly-L-lactic acid；
The weight average molecular weight of poly-dl-lactide component is than for Poly-L-lactic acid: dextrorotation polylactic acid=7:3, and the weight average molecular weight of lactic acid caprolactone copolymer component is than for Poly-L-lactic acid: polycaprolactone=7:3；
Nerve rehabilitating tube support has certain mechanical performance, it is possible to bending and stretching, has stronger toughness and support force, and its hot strength is 10MPa, 11MPa, 12MPa and 15MPa, and stretch-proof shape becomes 10%, 11% and 13%；
The internal diameter of nerve rehabilitating tube support is 2～4 millimeters, and external diameter is 2.2～4.2 millimeters, and length is 10～200 millimeters；
Interior tube thickness is 0.6～0.8 millimeter, and the thickness of middle pipe is 0.1～0.2 millimeter, and the thickness of outer tube is 0.1～0.4 millimeter；
The average fibre diameter of middle pipe is 240～450 nanometers, and the average fibre diameter of outer tube is 1.1～1.4 microns.
2. the preparation method of the nerve rehabilitating tube support of multiple structure according to claim 1, it is characterised in that comprise the steps:
(1) being dissolved in dichloromethane by poly-dl-lactide, heating condensing reflux dissolve, and form solution A；
(2) by dissolved for lactic acid caprolactone copolymer solution in dichloromethane with N-dimethylformamide mixed solvent, solution B is formed；
(3) by dissolved for Poly-L-lactic acid solution in dichloromethane and N-dimethylformamide mixed solvent in, form solution C；
(4) inserting in above-mentioned solution A with bar molds, vertically take out after being slightly agitated at once, be upside down in ventilation and place, room temperature volatilizees more than 6 hours, obtains interior pipe；
(5) building jet deck I, syringe needle is No. 5 straight angle syringe needles, and needle point is 10 centimetres with reception device distance；The solution B obtained in step (2) is loaded in syringe, interior pipe and bar molds is vertically fixed on metal rotation device, rotating collection electrostatic spinning；
(6) building jet deck II, syringe needle is No. 10 straight angle syringe needles, and needle point is 10 centimetres with reception device distance；The solution C obtained in step (3) is loaded in syringe, interior pipe and bar molds is vertically fixed on metal rotation device, rotating collection electrostatic spinning；
(7) lyophilization processes 12 hours, is soaked 10 minutes through bubble by support, can be separated with bar molds by support in 40 DEG C of warm water；
In solution A, solution B and solution C, the concentration range of macromolecular material is followed successively by 10～25%, 1～1.5% and 1～1.5%；In solution B and solution C, dichloromethane is 7:3 with the volume ratio of N-dimethylformamide；
When adopting tubular construction in electrostatic spinning technique preparation, injection rate is 0.4mL/h, injection volume 0.5～1 milliliter；
When adopting electrostatic spinning technique to prepare outer tube structure, injection rate is 0.4mL/h, injection volume 0.5～1 milliliter.
3. the preparation method of the nerve rehabilitating tube support of multiple structure according to claim 2, it is characterised in that bar molds diameter is 2～3 millimeters.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310639284.4A CN103654999B (en) | 2013-12-04 | 2013-12-04 | Nerve rehabilitating tube support of multiple structure and preparation method thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310639284.4A CN103654999B (en) | 2013-12-04 | 2013-12-04 | Nerve rehabilitating tube support of multiple structure and preparation method thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN103654999A CN103654999A (en) | 2014-03-26 |
| CN103654999B true CN103654999B (en) | 2016-07-20 |
Family
ID=50294579
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201310639284.4A Expired - Fee Related CN103654999B (en) | 2013-12-04 | 2013-12-04 | Nerve rehabilitating tube support of multiple structure and preparation method thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN103654999B (en) |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105477690B (en) * | 2014-09-17 | 2019-02-15 | 上海微创医疗器械（集团）有限公司 | A kind of degradable tubing of multilayer, bracket and preparation method thereof |
| CN105012050A (en) * | 2015-07-16 | 2015-11-04 | 清华大学 | Method and special mould for preparing tissue and organ precursor with multi-branch channels |
| CN106963991A (en) * | 2017-03-02 | 2017-07-21 | 天津索玛科技有限公司 | A kind of modified degradable support and preparation method thereof |
| CN109124822B (en) * | 2018-06-25 | 2021-07-16 | 上海理工大学 | Pre-bending and shaping mold for thoracic aorta stent ring |
| IL264006A (en) * | 2018-12-27 | 2020-06-30 | Tenne Reshef | Nanocomposites of biodegradable polymers and inorganic nanoparticles, methods of preparation and uses thereof |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101474423A (en) * | 2008-10-24 | 2009-07-08 | 清华大学 | Nerve conduit stent and preparation method thereof |
| CN101912318A (en) * | 2010-07-30 | 2010-12-15 | 东华大学 | Three-layer electrostatic spinning ordered fiber nerve conduit and preparation and application thereof |
| CN102688076A (en) * | 2011-03-25 | 2012-09-26 | 广州迈普再生医学科技有限公司 | Nerve conduit and preparation method thereof |
| CN102961783A (en) * | 2012-04-20 | 2013-03-13 | 南开大学 | Construction method of anticoagulant artificial blood vessel scaffold material |
| CN103169555A (en) * | 2011-12-22 | 2013-06-26 | 上海纳米技术及应用国家工程研究中心有限公司 | Biodegradable macromolecular intravascular stent and manufacturing method thereof |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7615373B2 (en) * | 1999-02-25 | 2009-11-10 | Virginia Commonwealth University Intellectual Property Foundation | Electroprocessed collagen and tissue engineering |
-
2013
- 2013-12-04 CN CN201310639284.4A patent/CN103654999B/en not_active Expired - Fee Related
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101474423A (en) * | 2008-10-24 | 2009-07-08 | 清华大学 | Nerve conduit stent and preparation method thereof |
| CN101912318A (en) * | 2010-07-30 | 2010-12-15 | 东华大学 | Three-layer electrostatic spinning ordered fiber nerve conduit and preparation and application thereof |
| CN102688076A (en) * | 2011-03-25 | 2012-09-26 | 广州迈普再生医学科技有限公司 | Nerve conduit and preparation method thereof |
| CN103169555A (en) * | 2011-12-22 | 2013-06-26 | 上海纳米技术及应用国家工程研究中心有限公司 | Biodegradable macromolecular intravascular stent and manufacturing method thereof |
| CN102961783A (en) * | 2012-04-20 | 2013-03-13 | 南开大学 | Construction method of anticoagulant artificial blood vessel scaffold material |
Also Published As
| Publication number | Publication date |
|---|---|
| CN103654999A (en) | 2014-03-26 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN103654999B (en) | Nerve rehabilitating tube support of multiple structure and preparation method thereof | |
| Huang et al. | Electrospun poly (butylene succinate)/cellulose nanocrystals bio-nanocomposite scaffolds for tissue engineering: Preparation, characterization and in vitro evaluation | |
| Sant et al. | Hybrid PGS–PCL microfibrous scaffolds with improved mechanical and biological properties | |
| Kim et al. | Effect of nanofiber content on bone regeneration of silk fibroin/poly (ε-caprolactone) nano/microfibrous composite scaffolds | |
| Huang et al. | Electrospun collagen–chitosan–TPU nanofibrous scaffolds for tissue engineered tubular grafts | |
| Su et al. | 3D electrospun synthetic extracellular matrix for tissue regeneration | |
| Jeffries et al. | Highly elastic and suturable electrospun poly (glycerol sebacate) fibrous scaffolds | |
| Wang et al. | Fabrication and properties of the electrospun polylactide/silk fibroin-gelatin composite tubular scaffold | |
| JP5622009B2 (en) | Scaffolds for prosthetic heart valves and vascular structures | |
| Yang et al. | Biomimetic nanofibers can construct effective tissue-engineered intervertebral discs for therapeutic implantation | |
| Kruse et al. | Electro-spun membranes as scaffolds for human corneal endothelial cells | |
| Stefani et al. | Development of an in-process UV-crosslinked, electrospun PCL/aPLA-co-TMC composite polymer for tubular tissue engineering applications | |
| Kuppan et al. | Interaction of human smooth muscle cells with nanofibrous scaffolds: effect of fiber orientation on cell adhesion, proliferation, and functional gene expression | |
| CN103656757A (en) | Double-layer intravascular stent carrying heparin and preparation method thereof | |
| CN109876186A (en) | A kind of biological medical degradable double-layer scaffold and preparation method thereof for neural restoration | |
| CN102102278A (en) | Preparation method of silk fibroin-poly(hydroxybutyrate-hydroxyvalerate) composite fiber membrane | |
| CN103751839A (en) | Polylactic acid-chitosan composite nerve conduit and preparation method thereof | |
| Zhang et al. | Composite fibrous membrane comprising PLA and PCL fibers for biomedical application | |
| CN101653624A (en) | Preparation method of composite nanometer fiber small-diameter intravascular tissue engineering stent material | |
| Yuan et al. | Mechanical property and biological performance of electrospun silk fibroin-polycaprolactone scaffolds with aligned fibers | |
| Meng et al. | Heterogeneous porous PLLA/PCL fibrous scaffold for bone tissue regeneration | |
| Zhang et al. | Characterization and cell response of electrospun R ana chensinensis skin collagen/poly (l‐lactide) scaffolds with different fiber orientations | |
| Rediguieri et al. | The effect of ozone gas sterilization on the properties and cell compatibility of electrospun polycaprolactone scaffolds | |
| Mendibil et al. | Bioresorbable and mechanically optimized nerve guidance conduit based on a naturally derived medium chain length polyhydroxyalkanoate and poly (ε-caprolactone) blend | |
| Arnaud Bopenga Bopenga et al. | Characterization of extracts from the bark of the gabon hazel tree (Coula edulis baill) for antioxidant, antifungal and anti-termite products |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20160720 Termination date: 20181204 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |