CN105310794A - Method for preparing porous artificial nerve conduit with orientation structures on inner walls - Google Patents
Method for preparing porous artificial nerve conduit with orientation structures on inner walls Download PDFInfo
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Abstract
The invention belongs to the field of medical biological materials capable of being implanted in human bodies, and relates to tissue engineering nerve graft for repairing injured nerves and a method for preparing the tissue engineering nerve graft. The tissue engineering nerve graft and the method have the advantages that micro-pattern techniques and freeze-dry molding processes are combined with one another, accordingly, an artificial nerve conduit favorable for adhesion and growth of nerve cells can be provided, orientation stripe structures are arranged on the inner walls of the conduit, the walls of the conduit are of loose porous structures, and suture or adhesion of the side walls of the conduit can be omitted during usage; the method for preparing the nerve conduit is simple and feasible and is applicable to mass production.
Description
Technical field
The invention belongs to the biomaterial for medical purpose field in human implantable, be specifically related to a kind of tissue engineering nerve conduit for repairing nerve damage and preparation method thereof.
Background technology
In China, peripheral nerve injury patient populations is in the trend increased year by year.Although peripheral nerve has certain self-regeneration function, be difficult to realize complete self-regeneration (particularly long distance neurologic defect), therefore need to repair by means of various Nerve grafting.Although Autologous support is the goldstandard repairing peripheral nerve defection, be but faced with donor source limited, size is not mated and can be caused the problems such as permanent injury to position of drawing materials.At present, people mainly by the various tissue engineering nerve bridge material be prepared from by the natural or synthesising biological material with better biocompatibility and biological degradability to realize CO2 laser weld.But these artificial nerve grafts promote that the speed of peripheral nerve regeneration is still difficult to meet clinical needs, particularly be difficult to the neurologic defect repairing longer distance (>3cm), therefore, exploitation comparatively fast can promote peripheral nerve regeneration and can realize the new type nerve graft of longer distance neurologic defect reparation, disclose material with the interaction relationship between neuranagenesis and inherent molecular mechanism simultaneously, for the design and clinical practice instructing peripheral nerve graft of new generation, there is very important scientific meaning.
Material surface pattern technology can construct the surface with regular figureization distribution, and accurately can control width and the degree of depth of figure, having higher controllability and repeatability, providing good thinking for solving the problem.Research finds, the biomaterial surface micrographics that two dimensional surface builds is conducive in vitro study figure to the regulation and control of cell and related mechanism.Orientation growth and the Acceleration of nerve regeneration of neurocyte can effectively be induced and regulate and control to the artificial nerve graft of graphical distribution as carinate in ditch, and the width of ditch ridge communicates with the orientation of effect of depth neurocyte and cell-ECM.Other graphical distribution such as column and round platform then can the differentiation of Effective Regulation neurocyte.Applicant finds under study for action, and migration and the orientation of Scs can be induced and regulate and control to the patterned chitosan of striated preferably, and can not affect the original physiological function of cell.Therefore, above-mentioned research shows, pattern technology has most important theories and application value for the reparation of regulation and control nerve regeneration and acceleration peripheral nerve defection.
From three-D space structure design with build there is the artificial nerve graft (stent/catheter) of different topology structure, make it have study hotspot and difficult point that the ability of carrying out bioelectric detecting to neurocyte and nerve regeneration becomes peripheral nerve regeneration implanting device in recent years.Tubular structure materials processing is become to provide suitable space and guiding function for neuranagenesis as adopted lyophilizing method of molding and electrostatic spinning technique, but, because common nerve trachea inwall is without any modification, also urge the implant of CO2 laser weld in pipe, its function of repairing peripheral nerve defection is very limited.Therefore, more reasonably must design (as orientation inwall) the internal structure of conduit, can to construct grow and urge the microenvironment of neuranagenesis by inducing nerve cell better.In recent ten years, various physico-chemical method is adopted to change nerve trachea interior wall construction (as inwall orientation, multi-channel type) or adding tube inner stuffing (as built-in fabric support, built-in gel or various Summing Factor cell), functional thus promote that neuranagenesis becomes study hotspot better to strengthen conduit own biological.That prepares as adopted method of molding has adhesion and the activity that multichannel PCL/ collagen nerve trachea obviously can promote Scs, and has good mechanical property.Subsequently the collagenous fiber bundle of laminin modified is filled in PCL/ collagen catheter chamber, successfully achieves the reparation of the longer distance Sciatic of Canis familiaris L..And the fibre bundle of various short nerve growth migration or filament are also filled in conduit to promote CO2 laser weld.In addition, also have researcher to combine to adopt the method for micrographics technology and electrostatic spinning first electrospinning go out to have the PHBV-PLGA fiber of orientation, and then wrap up orientation fiber with the PHBV-PLGA film of the surperficial pattern prepared by same material, finally tube wall side stitches is become inwall and have orientation and the nerve trachea simultaneously with orientation fiber filled, this conduit is realizing having potential using value in repairing of neural injury fast.As can be seen here, the appropriate design of conduit and pipe inner stuffing can promote CO2 laser weld better.But still there is certain difficulty in the structure with the pipe inner wall of particular space form (orientation).Although method of molding easily prepares conduit, be difficult to obtain the conduit that inwall has orientation, mainly because peel off difficulty.Method of electrostatic spinning can prepare the spinning fibre film of orientation arrangement, then is carried out by film curlingly can forming the conduit that inwall has orientation, but conduit side needs by sew up or bonding method realizes closed, thus can increase inflammation odds; Directly spinning can also be spun on columned receiving system in addition, but combine with mould relatively tight due to prepared conduit, when stripping, pipe inner wall easily damages.Micrographics technology can build the two-dimentional biomaterial surface that surface has orientation very easily, then material can be curled into catheter-like, but conduit side also needs to realize closing by stitching or bonding method, adds inflammation odds equally.
Summary of the invention
From the angle of design of material and the optimization of conduit biological function, urge the ability of neuranagenesis to improve artificial nerve catheter further, exploitation inwall there is orientation topological structure and can rapid induction neural cell adhesion and growth without the need to sew up or bonding artificial nerve graft (conduit/support) has very important Theory and applications meaning for the repairing of neural injury of peripheral nerve injury patient.For this problem, at present, micrographics technology and lyophilizing method of molding creatively combine by applicant, a kind of artificial nerve catheter being conducive to neural cell adhesion, growth is provided, this pipe inner wall has orientation striated structure, catheter wall is loose and porous structure, without the need to sew up duct wall or bonding during use.In order to prepare this nerve trachea, the present invention also provides a kind of preparation method of simple, applicable large-scale production.
Technical scheme of the present invention is as follows:
A kind of inwall has the porous artificial nerve catheter of orientation structure, it is characterized in that: described pipe inner wall surface has orientation striated structure, described striated structure is made up of zastrugi, the surface of ditch is concave surface, the surface of ridge is convex surface, the width 5-50 micron of ditch, the width of ridge is 5-50 micron, and the vertical dimension between the surface of ditch and the surface of ridge is 1-10 micron.
The catheter wall of described conduit is loose and porous structure.
The material of preparing of described conduit contains at least one in natural biologic material or synthesising biological material, and wherein said natural biologic material comprises at least one in chitosan, collagen, and described synthesising biological material comprises at least one in PCL, PLGA, PLA.
Described conduit also can contain biomolecule or somatomedin, and described biomolecule or somatomedin comprise at least one in laminin, fibronectin, hyaluronic acid, peptide sequence, NGF, BDNF, GDNF.
The internal diameter of described conduit is 1-5 millimeter, and conduit wall thickness is 1-2 millimeter.
Described catheter length is 10-80 millimeter.
Described duct wall is without the need to manual suture or bonding.
The present invention also provides the preparation method of above-mentioned artificial nerve catheter, and the method comprises:
Tinsel builds the micro-pattern of ditch ridge of micron-scale, then paillon foil is rolled into cylinder, now the inwall of cylinder has the micro-pattern of groove, then polydimethylsiloxane (PDMS) is built in cylinder, stripping metal paillon foil after PDMS curing molding, the PDMS cylinder that outer wall has the micro-pattern of groove is obtained after cutting, then at the concentric round jacket cylinder of PDMS cylinder additional, close wherein one end, the solution being dissolved with tube material is added between PDMS cylinder and outer sleeve, round jacket cylinder and PDMS cylinder is peeled off after lyophilization, obtain the artificial conduit that inwall has orientation structure.
Described tinsel can be titanium foil, aluminium foil, native gold, preferred titanium foil.
The described micro-pattern of ditch ridge, the width 5-50 micron of ditch, the width of ridge is 5-50 micron ditch, and the surface of ditch is concave surface, and the surface of ridge is convex surface, and the vertical dimension between the surface of ditch and the surface of ridge is 1-10 micron.
Described barrel bore is 1-10 micron.
Described PDMS solution is that the dimethylsiloxane monomer of 10:1 and cross-linking agent are formulated by volume ratio.
The material of preparing of described conduit contains at least one in natural biologic material or synthesising biological material, also biomolecule or somatomedin can be contained, wherein said natural biologic material comprises at least one in chitosan, collagen, described synthesising biological material comprises at least one in PCL, PLGA, PLA, described biomolecule or somatomedin comprise at least one in laminin, fibronectin, hyaluronic acid, peptide sequence, NGF, BDNF, GDNF.
The conduit of preparation method of the present invention and preparation has the following advantages:
1, described artificial nerve catheter is without the need to sew up catheter wall or bonding;
2, inwall has the complete candy strip of rule, is conducive to neural cell adhesion, growth;
3, catheter wall is loose and porous structure, is beneficial to the exchange of the transport of nutrient substance and the metabolism thing of cell, and the various somatomedin also urging neuranagenesis for load in addition provide good platform;
4, conduit is easily peeled off, simple, the applicable large-scale production of preparation method.
Detailed description of the invention
Below in conjunction with specific embodiment, set forth the present invention further.Should be understood that these embodiments are only not used in for illustration of the present invention to limit the scope of the invention.In addition should be understood that those skilled in the art can make various changes or modifications the present invention, and these equivalent form of values fall within the application's appended claims limited range equally after the content of having read the present invention's instruction.
Embodiment 1
(1) design of micrographics size and the preparation of pure titanium foil sheet motherboard
Dimension of picture: ditch/ridge width is 5um/5um, 10um/10um, 20um/20um, 30um/30um, 50um/50um, graphics depth is 1um, 2um, 4um, 6um, 10 μm.Adopt the carinate micro-pattern of ditch of laser microscopic carvings lithography above-mentioned dimension of picture of carve on pure titanium foil sheet, engraving area is 10cm × 10cm.
(2) outer wall has the Preparation and characterization of the PDMS cylinder elastomeric stamp of orientation figure
Along striped orientation, pure titanium foil sheet is curled into the different inner diameters (1mm that inwall has micrographics, 3mm, 5mm, 7mm, cylinder 10mm), PDMS(monomer by preparing under room temperature: cross-linking agent=10:1(volume ratio)) be cast to there is (micrographics is at pure titanium foil sheet pipe inner wall) in the pure titanium foil sheet catheter mold of certain micrographics size, then put it into evacuation in vacuum drying oven and get rid of bubble, and carry out dry solidification, be finally cured rear stripping and namely obtain the PDMS cylinder elastomeric stamp that outer wall has the different-diameter of the carinate micrographics distribution of ditch.Scanning electron microscope is adopted to detect the ditch ridge dimension of picture of PDMS cylinder elastomeric stamp and the degree of depth.
(3) sidewall is without the need to sew up and inwall has the preparation of the porous nerve trachea of orientation micrographics
Micrographics technology and lyophilizing method of molding is adopted to prepare sidewall without the need to sew up and inwall has the porous nerve trachea of orientation micrographics.First certain density chitosan/collagen mixed solution is prepared, then this solution is filled in the catheter mold of the PDMS cylinder elastomeric stamp composition with the carinate graphical distribution of outer wall ditch, evacuation removes bubble, after lyophilization, complete for conduit stripping can be obtained sidewall without the need to sew up and inwall has the porous artificial nerve catheter of orientation micrographics, and tube wall is intact bad.
(4) inwall of load bioactive molecule has the preparation of the porous chitosan/collagen nerve trachea of orientation micrographics
Under room temperature, certain density (5 μ g/mL, 10 μ g/mL, 50 μ g/mL) had the biomolecule (laminin, fibronectin, hyaluronic acid, the peptide sequence (YIGSR that promote neuranagenesis function, or the various factor (NGF of short nerve growth IKVAV), BDNF, GDNF etc.) first with the abundant blending reaction of chitosan/collagen mixed solution 2 hours, then adopt micrographics technology and lyophilizing method of molding that the solution after blended is prepared into the thin film of the carinate micrographics distribution of surperficial ditch; Or adopt the method (covalent bond or electrostatic interaction) of grafting to be directly fixed on the porous membrane of surperficial pattern by certain density bioactive molecule, thus realize bioactive molecule fixing in the orientation distribution and conduit loose structure of pipe inner wall respectively.
Claims (13)
1. an inwall has the porous artificial nerve catheter of orientation structure, it is characterized in that: described pipe inner wall surface has orientation striated structure, described striated structure is made up of zastrugi, the surface of ditch is concave surface, the surface of ridge is convex surface, the width 5-50 micron of ditch, the width of ridge is 5-50 micron, and the vertical dimension between the surface of ditch and the surface of ridge is 1-10 micron.
2. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, and it is characterized in that, the catheter wall of described conduit is loose and porous structure.
3. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, it is characterized in that, the material of preparing of described conduit contains at least one in natural biologic material or synthesising biological material, wherein said natural biologic material comprises at least one in chitosan, collagen, and described synthesising biological material comprises at least one in PCL, PLGA, PLA.
4. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, it is characterized in that, described conduit also can contain biomolecule or somatomedin, described biomolecule or somatomedin comprise laminin, fibronectin, hyaluronic acid, peptide sequence, NGF, at least one in BDNF, GDNF.
5. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, and it is characterized in that, the internal diameter of described conduit is 1-5 millimeter, and conduit wall thickness is 1-2 millimeter.
6. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, and it is characterized in that, described catheter length is 10-80 millimeter.
7. inwall as claimed in claim 1 has the porous artificial nerve catheter of orientation structure, and it is characterized in that, described duct wall is without the need to manual suture or bonding.
8. an inwall has the preparation method of the porous artificial nerve catheter of orientation structure, it is characterized in that the method comprises: the micro-pattern of ditch ridge building micron-scale on tinsel, then paillon foil is rolled into cylinder, now the inwall of cylinder has the micro-pattern of groove, then polydimethylsiloxane (PDMS) is built in cylinder, stripping metal paillon foil after PDMS curing molding, the PDMS cylinder that outer wall has the micro-pattern of groove is obtained after cutting, then at the concentric round jacket cylinder of PDMS cylinder additional, close wherein one end, the solution being dissolved with tube material is added between PDMS cylinder and outer sleeve, round jacket cylinder and PDMS cylinder is peeled off after lyophilization, obtain the artificial conduit that inwall has orientation structure.
9. inwall as claimed in claim 8 has the porous artificial nerve catheter of orientation structure, and it is characterized in that, described tinsel can be titanium foil, aluminium foil, native gold, preferred titanium foil.
10. inwall as claimed in claim 8 has the porous artificial nerve catheter of orientation structure, it is characterized in that, the described micro-pattern of ditch ridge, the width 5-50 micron of ditch, the width of ridge is 5-50 micron ditch, the surface of ditch is concave surface, and the surface of ridge is convex surface, and the vertical dimension between the surface of ditch and the surface of ridge is 1-10 micron.
11. inwalls as claimed in claim 8 have the porous artificial nerve catheter of orientation structure, and it is characterized in that, described barrel bore is 1-10 micron.
12. inwalls as claimed in claim 8 have the porous artificial nerve catheter of orientation structure, it is characterized in that, described PDMS solution is that the dimethylsiloxane monomer of 10:1 and cross-linking agent are formulated by volume ratio.
13. inwalls as claimed in claim 8 have the porous artificial nerve catheter of orientation structure, it is characterized in that the material of preparing of described conduit contains at least one in natural biologic material or synthesising biological material, also biomolecule or somatomedin can be contained, wherein said natural biologic material comprises chitosan, at least one in collagen, described synthesising biological material comprises PCL, PLGA, at least one in PLA, , described biomolecule or somatomedin comprise laminin, fibronectin, hyaluronic acid, peptide sequence, NGF, BDNF, at least one in GDNF.
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Cited By (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106236323A (en) * | 2016-08-05 | 2016-12-21 | 浙江大学 | A kind of nerve trachea with contact guiding function and preparation method thereof and device |
| CN108310461A (en) * | 2018-02-09 | 2018-07-24 | 武汉纺织大学 | Porous fibroin spinal cord rack with targeted release function and preparation method thereof prepares mold and application |
| CN108525013A (en) * | 2018-03-23 | 2018-09-14 | 南通大学 | A kind of preparation method of tissue-engineering graft constructed of the surface with micron-nano topological geometry |
| CN109938875A (en) * | 2019-03-07 | 2019-06-28 | 宁波光远致信生物科技有限公司 | A kind of nerve prosthesis and its preparation method and application |
| CN110507857A (en) * | 2019-08-30 | 2019-11-29 | 江南大学 | A kind of engineered nerve graft and preparation method thereof |
| CN111317867A (en) * | 2020-02-06 | 2020-06-23 | 清华大学 | Nerve conduit and preparation method thereof |
| WO2021035679A1 (en) * | 2019-08-30 | 2021-03-04 | 江南大学 | Tissue engineered nerve graft and preparation method therefor |
| CN113150321A (en) * | 2021-04-09 | 2021-07-23 | 南通大学 | Preparation method of hydrogel with different elastic chitosan/acrylamide micro-nano topological structures |
| CN114507916A (en) * | 2022-04-18 | 2022-05-17 | 中国科学院苏州纳米技术与纳米仿生研究所 | Chitosan microfiber with groove topological structure and preparation method and application thereof |
| CN114870095A (en) * | 2022-05-06 | 2022-08-09 | 南通大学 | Method for constructing tissue engineering graft with surface having anisotropic nano topological structure |
Citations (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1449850A (en) * | 2002-04-11 | 2003-10-22 | 财团法人工业技术研究院 | Multi-channel type biological absorptive nerve regeneration conduit and mfg method thereof |
| US6855329B1 (en) * | 1998-01-20 | 2005-02-15 | Massachusetts Institute Of Technology | Surface coating spatially controlled patterns |
| CN1654028A (en) * | 2005-01-21 | 2005-08-17 | 清华大学 | Tissue engineering complex grid shape stent forming method base on core dissolving technology |
| CN101433475A (en) * | 2008-12-03 | 2009-05-20 | 南通大学 | Artificial nerve implant with path for guiding growth |
| WO2010017496A1 (en) * | 2008-08-07 | 2010-02-11 | Purdue Research Foundation | Biodegradable nerve scaffold conduit for the treatment of nerve injuries |
| CN102048595A (en) * | 2010-12-21 | 2011-05-11 | 东华大学 | Degradable nerve conduit with highly-oriented tube-in-tube structure and manufacturing method thereof |
| CN103127548A (en) * | 2013-01-31 | 2013-06-05 | 东南大学 | Manufacture method of artificial nerve conduit for promoting nerve defect repair |
| CN103230622A (en) * | 2013-04-19 | 2013-08-07 | 南通纺织职业技术学院 | Conduit for tissue-engineered nerve transplanting and preparation method thereof |
| CN103432630A (en) * | 2013-09-06 | 2013-12-11 | 烟台隽秀生物科技有限公司 | Preparation method of dual-network-interweaved compound nerve conduit |
| CN203829090U (en) * | 2014-04-16 | 2014-09-17 | 烟台隽秀生物科技有限公司 | Nanofiber neural graft |
| CN104056306A (en) * | 2014-06-09 | 2014-09-24 | 南京师范大学 | Nerve conduit material having topological structure and modified by CNT/conducting polymer composite coating and preparation method of nerve conduit material |
-
2015
- 2015-02-14 CN CN201510078070.3A patent/CN105310794B/en not_active Expired - Fee Related
Patent Citations (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6855329B1 (en) * | 1998-01-20 | 2005-02-15 | Massachusetts Institute Of Technology | Surface coating spatially controlled patterns |
| CN1449850A (en) * | 2002-04-11 | 2003-10-22 | 财团法人工业技术研究院 | Multi-channel type biological absorptive nerve regeneration conduit and mfg method thereof |
| CN1654028A (en) * | 2005-01-21 | 2005-08-17 | 清华大学 | Tissue engineering complex grid shape stent forming method base on core dissolving technology |
| WO2010017496A1 (en) * | 2008-08-07 | 2010-02-11 | Purdue Research Foundation | Biodegradable nerve scaffold conduit for the treatment of nerve injuries |
| CN101433475A (en) * | 2008-12-03 | 2009-05-20 | 南通大学 | Artificial nerve implant with path for guiding growth |
| CN102048595A (en) * | 2010-12-21 | 2011-05-11 | 东华大学 | Degradable nerve conduit with highly-oriented tube-in-tube structure and manufacturing method thereof |
| CN103127548A (en) * | 2013-01-31 | 2013-06-05 | 东南大学 | Manufacture method of artificial nerve conduit for promoting nerve defect repair |
| CN103230622A (en) * | 2013-04-19 | 2013-08-07 | 南通纺织职业技术学院 | Conduit for tissue-engineered nerve transplanting and preparation method thereof |
| CN103432630A (en) * | 2013-09-06 | 2013-12-11 | 烟台隽秀生物科技有限公司 | Preparation method of dual-network-interweaved compound nerve conduit |
| CN203829090U (en) * | 2014-04-16 | 2014-09-17 | 烟台隽秀生物科技有限公司 | Nanofiber neural graft |
| CN104056306A (en) * | 2014-06-09 | 2014-09-24 | 南京师范大学 | Nerve conduit material having topological structure and modified by CNT/conducting polymer composite coating and preparation method of nerve conduit material |
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106236323A (en) * | 2016-08-05 | 2016-12-21 | 浙江大学 | A kind of nerve trachea with contact guiding function and preparation method thereof and device |
| CN106236323B (en) * | 2016-08-05 | 2017-11-17 | 浙江大学 | A kind of nerve trachea with contact guiding function and preparation method thereof and device |
| CN108310461A (en) * | 2018-02-09 | 2018-07-24 | 武汉纺织大学 | Porous fibroin spinal cord rack with targeted release function and preparation method thereof prepares mold and application |
| CN108310461B (en) * | 2018-02-09 | 2021-07-06 | 武汉纺织大学 | Porous silk fibroin spinal cord stent with directional release function, and preparation method, preparation mold and application thereof |
| CN108525013A (en) * | 2018-03-23 | 2018-09-14 | 南通大学 | A kind of preparation method of tissue-engineering graft constructed of the surface with micron-nano topological geometry |
| CN109938875A (en) * | 2019-03-07 | 2019-06-28 | 宁波光远致信生物科技有限公司 | A kind of nerve prosthesis and its preparation method and application |
| CN110507857A (en) * | 2019-08-30 | 2019-11-29 | 江南大学 | A kind of engineered nerve graft and preparation method thereof |
| WO2021035679A1 (en) * | 2019-08-30 | 2021-03-04 | 江南大学 | Tissue engineered nerve graft and preparation method therefor |
| CN111317867A (en) * | 2020-02-06 | 2020-06-23 | 清华大学 | Nerve conduit and preparation method thereof |
| CN113150321A (en) * | 2021-04-09 | 2021-07-23 | 南通大学 | Preparation method of hydrogel with different elastic chitosan/acrylamide micro-nano topological structures |
| CN114507916A (en) * | 2022-04-18 | 2022-05-17 | 中国科学院苏州纳米技术与纳米仿生研究所 | Chitosan microfiber with groove topological structure and preparation method and application thereof |
| CN114870095A (en) * | 2022-05-06 | 2022-08-09 | 南通大学 | Method for constructing tissue engineering graft with surface having anisotropic nano topological structure |
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