CN115230142A - Nanofiber surface porous bone repair scaffold and preparation method thereof - Google Patents
Nanofiber surface porous bone repair scaffold and preparation method thereof Download PDFInfo
- Publication number
- CN115230142A CN115230142A CN202210853278.8A CN202210853278A CN115230142A CN 115230142 A CN115230142 A CN 115230142A CN 202210853278 A CN202210853278 A CN 202210853278A CN 115230142 A CN115230142 A CN 115230142A
- Authority
- CN
- China
- Prior art keywords
- printing
- bone repair
- porous bone
- temperature
- nanofiber surface
- 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.)
- Pending
Links
- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 125
- 239000002121 nanofiber Substances 0.000 title claims abstract description 100
- 230000008439 repair process Effects 0.000 title claims abstract description 97
- 238000002360 preparation method Methods 0.000 title claims abstract description 32
- 238000007639 printing Methods 0.000 claims abstract description 155
- WYURNTSHIVDZCO-UHFFFAOYSA-N Tetrahydrofuran Chemical compound C1CCOC1 WYURNTSHIVDZCO-UHFFFAOYSA-N 0.000 claims abstract description 82
- ZMXDDKWLCZADIW-UHFFFAOYSA-N N,N-Dimethylformamide Chemical compound CN(C)C=O ZMXDDKWLCZADIW-UHFFFAOYSA-N 0.000 claims abstract description 70
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 claims abstract description 62
- 238000005266 casting Methods 0.000 claims abstract description 61
- 239000000243 solution Substances 0.000 claims abstract description 53
- 239000011259 mixed solution Substances 0.000 claims abstract description 49
- QORWJWZARLRLPR-UHFFFAOYSA-H tricalcium bis(phosphate) Chemical compound [Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O QORWJWZARLRLPR-UHFFFAOYSA-H 0.000 claims abstract description 49
- 229920000747 poly(lactic acid) Polymers 0.000 claims abstract description 46
- 239000004626 polylactic acid Substances 0.000 claims abstract description 46
- 238000010146 3D printing Methods 0.000 claims abstract description 44
- YLQBMQCUIZJEEH-UHFFFAOYSA-N tetrahydrofuran Natural products C=1C=COC=1 YLQBMQCUIZJEEH-UHFFFAOYSA-N 0.000 claims abstract description 41
- 239000011780 sodium chloride Substances 0.000 claims abstract description 31
- 238000001816 cooling Methods 0.000 claims abstract description 22
- 239000012528 membrane Substances 0.000 claims abstract description 16
- 238000002156 mixing Methods 0.000 claims abstract description 14
- 239000007788 liquid Substances 0.000 claims abstract description 13
- 238000005406 washing Methods 0.000 claims abstract description 5
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 136
- 238000002791 soaking Methods 0.000 claims description 83
- 239000008367 deionised water Substances 0.000 claims description 48
- 229910021641 deionized water Inorganic materials 0.000 claims description 48
- 238000003756 stirring Methods 0.000 claims description 18
- 238000001125 extrusion Methods 0.000 claims description 14
- 239000011148 porous material Substances 0.000 claims description 13
- 238000000034 method Methods 0.000 claims description 9
- 230000001737 promoting effect Effects 0.000 abstract description 14
- 230000004069 differentiation Effects 0.000 abstract description 12
- 230000012010 growth Effects 0.000 abstract description 11
- 230000009286 beneficial effect Effects 0.000 abstract description 6
- 239000000835 fiber Substances 0.000 abstract description 6
- 238000002145 thermally induced phase separation Methods 0.000 abstract description 6
- 238000005516 engineering process Methods 0.000 abstract description 4
- 230000000052 comparative effect Effects 0.000 description 31
- 210000004027 cell Anatomy 0.000 description 23
- 230000007547 defect Effects 0.000 description 12
- 238000003860 storage Methods 0.000 description 11
- 230000006698 induction Effects 0.000 description 6
- 238000010899 nucleation Methods 0.000 description 6
- 238000001228 spectrum Methods 0.000 description 5
- 238000001000 micrograph Methods 0.000 description 4
- 230000011164 ossification Effects 0.000 description 4
- 230000008569 process Effects 0.000 description 4
- 238000010186 staining Methods 0.000 description 4
- 238000006243 chemical reaction Methods 0.000 description 3
- 210000004748 cultured cell Anatomy 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- BHPQYMZQTOCNFJ-UHFFFAOYSA-N Calcium cation Chemical compound [Ca+2] BHPQYMZQTOCNFJ-UHFFFAOYSA-N 0.000 description 2
- 206010061218 Inflammation Diseases 0.000 description 2
- 206010031264 Osteonecrosis Diseases 0.000 description 2
- 239000012237 artificial material Substances 0.000 description 2
- 229910001424 calcium ion Inorganic materials 0.000 description 2
- 238000004113 cell culture Methods 0.000 description 2
- 230000010261 cell growth Effects 0.000 description 2
- 239000003153 chemical reaction reagent Substances 0.000 description 2
- 239000002131 composite material Substances 0.000 description 2
- 238000002513 implantation Methods 0.000 description 2
- 230000004054 inflammatory process Effects 0.000 description 2
- 208000014674 injury Diseases 0.000 description 2
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 238000002844 melting Methods 0.000 description 2
- 230000008018 melting Effects 0.000 description 2
- 239000000203 mixture Substances 0.000 description 2
- 238000000465 moulding Methods 0.000 description 2
- 235000015097 nutrients Nutrition 0.000 description 2
- 230000009818 osteogenic differentiation Effects 0.000 description 2
- 108090000623 proteins and genes Proteins 0.000 description 2
- 239000002994 raw material Substances 0.000 description 2
- 238000001878 scanning electron micrograph Methods 0.000 description 2
- 230000008733 trauma Effects 0.000 description 2
- 208000020084 Bone disease Diseases 0.000 description 1
- 206010049824 Bone infarction Diseases 0.000 description 1
- OYPRJOBELJOOCE-UHFFFAOYSA-N Calcium Chemical compound [Ca] OYPRJOBELJOOCE-UHFFFAOYSA-N 0.000 description 1
- 102000012422 Collagen Type I Human genes 0.000 description 1
- 108010022452 Collagen Type I Proteins 0.000 description 1
- 208000024779 Comminuted Fractures Diseases 0.000 description 1
- 102000015775 Core Binding Factor Alpha 1 Subunit Human genes 0.000 description 1
- 108010024682 Core Binding Factor Alpha 1 Subunit Proteins 0.000 description 1
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- 101001086210 Homo sapiens Osteocalcin Proteins 0.000 description 1
- 206010028851 Necrosis Diseases 0.000 description 1
- 208000002565 Open Fractures Diseases 0.000 description 1
- 102100031475 Osteocalcin Human genes 0.000 description 1
- 208000034530 PLAA-associated neurodevelopmental disease Diseases 0.000 description 1
- 208000037273 Pathologic Processes Diseases 0.000 description 1
- 102000040945 Transcription factor Human genes 0.000 description 1
- 108091023040 Transcription factor Proteins 0.000 description 1
- 230000006578 abscission Effects 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 238000003556 assay Methods 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 210000002449 bone cell Anatomy 0.000 description 1
- 239000011575 calcium Substances 0.000 description 1
- 229910052791 calcium Inorganic materials 0.000 description 1
- 229910000389 calcium phosphate Inorganic materials 0.000 description 1
- 239000001506 calcium phosphate Substances 0.000 description 1
- 230000004663 cell proliferation Effects 0.000 description 1
- 238000012512 characterization method Methods 0.000 description 1
- 238000011960 computer-aided design Methods 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 230000003111 delayed effect Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 230000004064 dysfunction Effects 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 230000035876 healing Effects 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 239000004310 lactic acid Substances 0.000 description 1
- 235000014655 lactic acid Nutrition 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000017074 necrotic cell death Effects 0.000 description 1
- 231100000252 nontoxic Toxicity 0.000 description 1
- 230000003000 nontoxic effect Effects 0.000 description 1
- 230000009054 pathological process Effects 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 238000005191 phase separation Methods 0.000 description 1
- 229910052698 phosphorus Inorganic materials 0.000 description 1
- 239000011574 phosphorus Substances 0.000 description 1
- -1 phosphorus ions Chemical class 0.000 description 1
- 229920000642 polymer Polymers 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 239000002904 solvent Substances 0.000 description 1
- 239000007921 spray Substances 0.000 description 1
- 238000005728 strengthening Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 238000002054 transplantation Methods 0.000 description 1
- 238000012795 verification Methods 0.000 description 1
Images
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
- B29C64/10—Processes of additive manufacturing
- B29C64/106—Processes of additive manufacturing using only liquids or viscous materials, e.g. depositing a continuous bead of viscous material
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
- B29C64/30—Auxiliary operations or equipment
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
- B29C64/30—Auxiliary operations or equipment
- B29C64/307—Handling of material to be used in additive manufacturing
- B29C64/314—Preparation
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y10/00—Processes of additive manufacturing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y40/00—Auxiliary operations or equipment, e.g. for material handling
- B33Y40/10—Pre-treatment
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y40/00—Auxiliary operations or equipment, e.g. for material handling
- B33Y40/20—Post-treatment, e.g. curing, coating or polishing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y70/00—Materials specially adapted for additive manufacturing
- B33Y70/10—Composites of different types of material, e.g. mixtures of ceramics and polymers or mixtures of metals and biomaterials
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y80/00—Products made by additive manufacturing
Landscapes
- Chemical & Material Sciences (AREA)
- Engineering & Computer Science (AREA)
- Materials Engineering (AREA)
- Manufacturing & Machinery (AREA)
- Physics & Mathematics (AREA)
- Mechanical Engineering (AREA)
- Optics & Photonics (AREA)
- Ceramic Engineering (AREA)
- Civil Engineering (AREA)
- Composite Materials (AREA)
- Structural Engineering (AREA)
- Materials For Medical Uses (AREA)
Abstract
A nanofiber surface porous bone repair scaffold and a preparation method thereof are disclosed, wherein the preparation method comprises the following steps: mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution; adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1) to obtain a membrane casting solution; step (3) cooling the 3D printing platform in advance, then taking the casting film liquid obtained in the step (2) as printing ink, and performing 3D printing in the 3D printing platform according to printing parameters to obtain a printing support; and (4) cooling and washing the printing support obtained in the step (3) to obtain the nanofiber surface porous bone repair support. The scaffold forms a micro-nano-grade fiber porous structure by utilizing a low-temperature thermally induced phase separation technology, and the nano-fiber surface porous bone repair scaffold has good biocompatibility, can simultaneously have a good bone differentiation promoting effect, and is beneficial to generation and growth of bone tissues.
Description
Technical Field
The invention relates to the technical field of nanofiber materials, in particular to a nanofiber surface porous bone repair support and a preparation method thereof.
Background
Bone deficiency due to trauma or surgery is called bone defect. Due to the presence of bone defects, nonunion, delayed or no healing of the resulting bone, and localized dysfunction are often caused. Bone defects caused in pathological processes, such as comminuted fracture, open fracture and massive bone tissue defect caused by trauma, inflammation, bone diseases and other factors, osteonecrosis and abscission and separation caused by inflammation, and defects caused by massive osteonecrosis caused by bone infarction or osteoischemic necrosis, belong to bone defects caused by diseases. The bone defect caused by the operation is caused by artificial factors.
The artificial material transplantation is carried out in an important means for clinically treating large-area bone defects. However, the artificial materials are generally lack of biocompatibility and surface activity, the seed cells are difficult to adhere and grow, and the channels for exchanging tissue nutrients are lacked, so that the occurrence of peripheral micro-blood vessels is not facilitated.
Therefore, it is necessary to provide a nanofiber surface porous bone repair scaffold and a preparation method thereof to solve the defects of the prior art.
Disclosure of Invention
One of the purposes of the invention is to provide a preparation method of a nanofiber surface porous bone repair scaffold to avoid the defects of the prior art. The nanofiber surface porous bone repair scaffold can be prepared by the preparation method, has good biocompatibility, can simultaneously have good bone differentiation promoting effect, and is beneficial to generation and growth of bone tissues.
The above object of the present invention is achieved by the following technical measures:
provides a preparation method of a nanofiber surface porous bone repair scaffold, which comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1) to obtain a membrane casting solution;
step (3) cooling the 3D printing platform in advance, then taking the casting film liquid obtained in the step (2) as printing ink, and performing 3D printing in the 3D printing platform according to printing parameters to obtain a printing support;
and (4) cooling and washing the printing support obtained in the step (3) to obtain the nanofiber surface porous bone repair support.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 50% -75%;
sodium chloride: 5% -20%;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
beta-tricalcium phosphate: 2% -15%;
polylactic acid: 20 to 40 percent.
Further, in the mixed solution, the weight ratio is:
tetrahydrofuran (tetrahydrofuran): 60% -70%;
sodium chloride: 8 to 12 percent;
n, N-dimethylformamide: and the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 4% -7%;
polylactic acid: 25 to 32 percent.
Furthermore, in the mixed solution, the weight ratio is as follows:
tetrahydrofuran (tetrahydrofuran): 67.5 percent;
sodium chloride: 22.5 percent;
n, N-dimethylformamide: the balance;
in the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 5 percent;
polylactic acid: 30 percent.
Preferably, in the step (2), the beta-tricalcium phosphate and the polylactic acid are added into the mixed solution obtained in the step (1), the stirring speed is 450-550 rpm, the temperature is 35-45 ℃, and the stirring time is 18-24 hours, so as to obtain the membrane casting solution.
Preferably, the step (3) is specifically to reduce the temperature of the 3D printing platform to-20-4 ℃ in advance, and then perform 3D printing on the casting solution obtained in the step (2) as printing ink according to printing parameters to obtain a printing support;
the printing parameters comprise that the temperature of the storage bin and the printing nozzle is 30-60 ℃, the moving speed of the printing nozzle is 2-3 mm/s, and the extrusion pressure of the printing nozzle is 4.3-6 bar.
Preferably, the step (4) includes:
step 4.1, cooling the printing support obtained in the step 3 to below-20 ℃, standing for 6-24 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is more than or equal to 4 and less than or equal to 10, is an integer, and t is more than or equal to 2 ℃ and less than or equal to 5 ℃, so as to obtain the nanofiber surface porous bone repair support.
Preferably, the step 4.2 is to soak the printing support in water with the temperature t, and replace the original soaking water with deionized water with the temperature t every other alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2 nd hour period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein t is more than or equal to 2 ℃ and less than or equal to 5 ℃, alpha is 10min, beta is 20min, and gamma is 30min.
Preferably, the pore diameter of the nanofiber surface porous bone repair scaffold is 390.63 μm +/-35.42 μm.
Preferably, the tensile strength of the nanofiber surface porous bone repair scaffold is 2.0MPa-2.1MPa.
Another object of the present invention is to provide a nanofiber surface porous bone repair scaffold which avoids the disadvantages of the prior art. The nanofiber surface porous bone repair scaffold has good biocompatibility, can simultaneously have good effect of promoting bone differentiation, and is beneficial to generation and growth of bone tissues.
The above object of the present invention is achieved by the following technical measures:
the nanofiber surface porous bone repair scaffold is prepared by the preparation method of the nanofiber surface porous bone repair scaffold.
The invention relates to a nanofiber surface porous bone repair scaffold and a preparation method thereof, wherein the preparation method comprises the following steps: mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution; adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1) to obtain a membrane casting solution; step (3) cooling the 3D printing platform in advance, then taking the casting film liquid obtained in the step (2) as printing ink, and performing 3D printing in the 3D printing platform according to printing parameters to obtain a printing support; and (4) cooling and washing the printing support obtained in the step (3) to obtain the nanofiber surface porous bone repair support. The nanofiber surface porous bone repair scaffold forms a micro-nano-grade fiber porous structure by using a low-temperature thermally induced phase separation technology, has good biocompatibility, can simultaneously have a good bone differentiation promoting effect, and is beneficial to generation and growth of bone tissues.
Drawings
The invention is further illustrated by means of the attached drawings, the content of which is not in any way limiting.
FIG. 1 is a scanning electron microscope image of the nanofiber surface porous bone repair scaffold of example 3.
Fig. 2 is a spectrum diagram of the nanofiber surface porous bone repair scaffold of example 3.
Fig. 3 is a scanning electron microscope image of the nanofiber surface porous bone repair scaffold of example 8.
FIG. 4 is a scanning electron micrograph of a stent of comparative example 1.
FIG. 5 is an energy spectrum of the stent of comparative example 1.
FIG. 6 is a cell seeding map of the nanofiber surface porous bone repair scaffold of example 3.
Fig. 7 is a staining pattern of living cells of the nanofiber surface porous bone repair scaffold of example 3 after cell seeding.
FIG. 8 is a diagram of scaffold seeded cells of comparative example 1.
FIG. 9 is a graph showing staining of viable cells after cell seeding in comparative example 1.
FIG. 10 is a graph showing the growth of the nanofiber surface porous bone repair scaffold of example 3 after being seeded with cells, and the growth of the conventional two-dimensional cultured cells, compared to the scaffold of comparative example 1.
FIGS. 11, 12 and 13 are comparative graphs showing the detection of osteogenic differentiation-related genes after induction culture of cells of the scaffolds of comparative example 1 and the scaffolds for nanofiber surface porous bone repair of example 3, respectively.
Detailed Description
The technical solution of the present invention is further illustrated by the following examples.
The experimental procedures in the following examples are conventional unless otherwise specified. The raw materials, reagent materials and the like used in the following examples can be purchased from conventional biochemical reagent stores or pharmaceutical operation companies unless otherwise specified. Wherein, the beta-tricalcium phosphate and the polylactic acid are respectively purchased from the Jinan Dai handle biotech GmbH; the cells of the present invention were 3T3 cells, and 3T3 cells were purchased from Yuan-Jing Biotechnology Ltd
Example 1.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps: mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1) to obtain a membrane casting solution;
step (3) cooling the 3D printing platform in advance, then taking the casting film liquid obtained in the step (2) as printing ink, and performing 3D printing in the 3D printing platform according to printing parameters to obtain a printing support;
and (4) cooling and washing the printing support obtained in the step (3) to obtain the nanofiber surface porous bone repair support.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 50% -75%;
sodium chloride: 5% -20%;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 2% -15%;
polylactic acid: 20 to 40 percent.
It should be noted that, because the 3D printing ink is stored in the printing bin and extruded through the nozzle, β -tricalcium phosphate and polylactic acid in the casting solution may gradually solidify with volatilization of tetrahydrofuran, causing nozzle blockage; and the printing ink with the too strong fluidity of the casting solution is difficult to be rapidly molded on a printing platform after being extruded, and the mechanical strength of the molded bracket is not enough when the molded bracket is used for implantation.
The concentration of tetrahydrofuran and N, N-dimethylformamide in the mixed solution is in the range, and the weight ratio of beta-tricalcium phosphate to polylactic acid in the casting solution is in the range, so that the spray head can be prevented from being blocked by volatilization of tetrahydrofuran, and the smoothness of the extrusion process is ensured; meanwhile, the composite material can be quickly molded after being extruded. The sodium chloride is added to improve the cohesive force, so that the mechanical strength of the printing support is improved, and the printing support is convenient to implant into a loaded bone defect part.
Specifically, the step (2) of the invention is to add beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), wherein the stirring speed is 450-550 rpm, the temperature is 35-45 ℃, and the stirring time is 18-24 h, so as to obtain the membrane casting solution.
It should be noted that, the temperature in the preparation process of the casting solution needs to be controlled between 35 ℃ and 45 ℃, because too high temperature can cause volatilization of a mixture system in the heating process, so that the yield of the casting solution is reduced, and the obtained casting solution is difficult to form when the fluidity of the casting solution is too strong for printing; if the temperature is too low, the beta-tricalcium phosphate and the polylactic acid are difficult to dissolve in the mixed liquid, and printing ink cannot be formed. In addition, the mixture splashes due to the fact that the stirring speed is too high in the process, and the dissolving efficiency is influenced by the fact that the stirring speed is too low.
Specifically, the step (3) is that the temperature of the 3D printing platform is reduced to-20-4 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters, and the printing support is obtained.
The printing parameters of the invention include that the temperature of the storage bin and the printing nozzle is 30-60 ℃, the moving speed of the printing nozzle is 2-3 mm/s, and the extrusion pressure of the printing nozzle is 4.3-6 bar.
Wherein, step (4) includes:
step 4.1, cooling the printing support obtained in the step 3 to below-20 ℃, standing for 6-24 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is more than or equal to 4 and less than or equal to 10, is an integer, and t is more than or equal to 2 ℃ and less than or equal to 5 ℃, so as to obtain the nanofiber surface porous bone repair support.
Specifically, the step 4.2 is to soak the printing support in water with the temperature t, and replace the original soaking water with deionized water with the temperature t every other alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within a time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein t is more than or equal to 2 ℃ and less than or equal to 5 ℃, alpha is 10min, beta is 20min, and gamma is 30min.
It should be noted that, the printing support is soaked in water, tetrahydrofuran inside the printing support is gradually replaced with water, and in the experimental process, it is found that the replacement speed of tetrahydrofuran is fast in the front and slow in the back, so that the soaking water needs to be quickly replaced in the front in a period from the starting point to delta hours, and the printing support is prevented from being soaked in the soaking water containing replaced tetrahydrofuran for a long time, and the structure of the printing support is damaged due to tetrahydrofuran. After replacing tetrahydrofuran, a fiber sample micro-morphology of about 1 micron is formed on the surface of the printing support.
The pore diameter of the nanofiber surface porous bone repair scaffold is 390.63 microns +/-35.42 microns. The tensile strength of the porous bone repair bracket on the surface of the nano fiber is 2.0MPa-2.1MPa.
Polylactic acid (PLA), also called polylactide, is a polymer polymerized from lactic acid as a main raw material, and has excellent biodegradability and biocompatibility. Beta-tricalcium phosphate (beta-TCP) also has excellent biodegradability, and calcium and phosphorus ions degraded in the implanted body can enter a body circulation system to stimulate the osteogenesis process. Polylactic acid and beta-tricalcium phosphate are dissolved and then used as printing ink, a high-precision complex bracket structure is obtained through 3D printing, complex porous materials with micro-nano scale are formed by combining a low-temperature thermally induced phase separation technology, and the polylactic acid and beta-tricalcium phosphate composite material has good biocompatibility and good bone promoting effect.
In addition, the low-temperature thermally induced phase separation technique means that the temperature of the casting solution is lower than the melting points of the beta-tricalcium phosphate and the polylactic acid. In the step (2), the temperature of the mixed solution is lower than the melting points of the beta-tricalcium phosphate and the polylactic acid and is higher than the cloud point temperature of the casting solution, and the temperature of the 3D printing platform is obviously lower than the cloud point temperature of the casting solution. Thus, when the casting solution enters the 3D printing platform, a thermally-induced phase separation mechanism and a non-solvent-induced phase separation mechanism occur simultaneously, thereby forming a porous structure.
The preparation method of the nanofiber surface porous bone repair scaffold has the following beneficial effects:
(1) Through computer aided design and direct molding by 3D printing, the molding structure is consistent with the design structure, the structure and the mechanical property of the bracket can be ensured to be matched with the height of a defect part, and no pollution is caused by cutting;
(2) The micro-nano level fiber porous structure is formed by a low-temperature thermally induced phase separation technology, the surface of the bracket has high porosity and strong adsorbability, and the pores are communicated with each other, so that the adhesive growth of seed cells, the growth of blood vessels and the exchange of nutrient substances after implantation are facilitated;
(3) The biocompatibility is good, and meanwhile, the bone formation promoting effect is good;
(4) The preparation method is simple and convenient, the preparation process is stable, and the preparation method is non-toxic and pollution-free.
Example 2.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), wherein the stirring speed is 480-500 rpm, the temperature is 38-42 ℃, and the stirring time is 20-22 h, so as to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-15-0 ℃ in advance, then the casting solution obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise the temperature of a storage bin and a printing nozzle of 40-50 ℃, the moving speed of the printing nozzle of 2.3-2.7 mm/s, and the extrusion pressure of the printing nozzle of 5-5.8 bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-21 ℃, standing for 10 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to the time within delta hours, wherein delta is 6 and t is 3 ℃ to obtain the nanofiber surface porous bone repair support.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every other alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta, and obtaining the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 60% -70%;
sodium chloride: 8 to 12 percent;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 4 to 7 percent;
polylactic acid: 25 to 32 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore diameter, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 3.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 490rpm and the temperature of 45 ℃ for 20 hours to obtain the membrane casting solution.
Step (3), the temperature of a 3D printing platform is reduced to-20 ℃ in advance, then the casting solution obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperatures of a storage bin and a printing nozzle are 41 ℃, the moving speed of the printing nozzle is 2.4mm/s, and the extrusion pressure of the printing nozzle is 5.2bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-20 ℃, standing for 5 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to the time within delta hours, wherein delta is 5 and t is 4 ℃ to obtain the porous bone repair support on the surface of the nanofiber.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every other alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 67.5 percent;
sodium chloride: 22.5 percent;
n, N-dimethylformamide: and the balance.
In the casting solution, the mass volume ratio is as follows:
beta-tricalcium phosphate: 5 percent;
polylactic acid: 30 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore size, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 4.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 450rpm and the temperature of 35 ℃ for 18 hours to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-20 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise the temperatures of a storage bin and a printing nozzle of 40 ℃, the moving speed of the printing nozzle of 2mm/s, and the extrusion pressure of the printing nozzle of 4.3bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-25 ℃, standing for 6 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and is 4; and t is 2 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature t every gamma minute within the 3-hour time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta, and obtaining the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 50 percent;
sodium chloride: 5 percent;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 15 percent;
polylactic acid: 20 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore diameter, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 5.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 550rpm at the temperature of 45 ℃ for 24 hours to obtain a membrane casting solution.
Step (3), reducing the temperature of the 3D printing platform to 4 ℃ in advance, then using the casting film liquid obtained in the step (2) as printing ink and carrying out 3D printing according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperatures of a storage bin and a printing nozzle are 60 ℃, the moving speed of the printing nozzle is 3mm/s, and the extrusion pressure of the printing nozzle is 6bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-21 ℃, standing for 24 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and delta is 10; t is 1 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every other alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2 nd hour period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 75 percent;
sodium chloride: 20 percent;
n, N-dimethylformamide: and the balance.
In the casting solution, the mass volume ratio is as follows:
β -tricalcium phosphate: 2 percent;
polylactic acid: 40 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore diameter, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 6.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 500rpm and the temperature of 40 ℃ for 20 hours to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-10 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperature of a storage bin and a printing nozzle is 50 ℃, the moving speed of the printing nozzle is 2.5mm/s, and the extrusion pressure of the printing nozzle is 5.5bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-22 ℃, standing for 8 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and is 7; and t is 4 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2 nd hour period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta, and obtaining the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 60 percent;
sodium chloride: 12 percent;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 4 percent;
polylactic acid: 25 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore size, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 7.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 500rpm and the temperature of 40 ℃ for 20 hours to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-10 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperature of a storage bin and a printing nozzle is 50 ℃, the moving speed of the printing nozzle is 2.5mm/s, and the extrusion pressure of the printing nozzle is 5.5bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-22 ℃, standing for 8 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and is 7; and t is 4 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta, and obtaining the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 70 percent;
sodium chloride: 8 percent;
n, N-dimethylformamide: and the balance.
In the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 7 percent;
polylactic acid: 32 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore diameter, tensile strength, biocompatibility and bone differentiation promoting effect.
Example 8.
A preparation method of a nanofiber surface porous bone repair scaffold comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 490rpm and the temperature of 45 ℃ for 20 hours to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to 4 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperatures of a storage bin and a printing nozzle are 41 ℃, the moving speed of the printing nozzle is 2.4mm/s, and the extrusion pressure of the printing nozzle is 5.2bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-20 ℃, standing for 5 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to the time within delta hours, wherein delta is 5 and t is 4 ℃ to obtain the porous bone repair support on the surface of the nanofiber.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature t every gamma minute within the 3-hour time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 67.5 percent;
sodium chloride: 22.5 percent;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
beta-tricalcium phosphate: 5 percent;
polylactic acid: 30 percent.
Compared with the embodiment 1, the nanofiber surface porous bone repair scaffold obtained in the embodiment has better pore diameter, tensile strength, biocompatibility and bone differentiation promoting effect.
Comparative example 1.
Mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
and (2) adding polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 500rpm and the temperature of 45 ℃ for 20 hours to obtain a casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-20 ℃ in advance, then the casting solution obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperature of a storage bin and a printing nozzle is 50 ℃, the moving speed of the printing nozzle is 2.5mm/s, and the extrusion pressure of the printing nozzle is 5.5bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-22 ℃, standing for 5 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and is 7; and t is 4 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature of t every gamma minute within the 3 h time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the stent of the comparative example 1, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 67.5 percent;
sodium chloride: 10 percent;
n, N-dimethylformamide: and (4) the balance.
In the casting solution, the mass-to-volume ratio is as follows:
polylactic acid: 30 percent.
In comparison with example 3, comparative example 1 did not add β -tricalcium phosphate and the other reaction conditions were the same.
Comparative example 2.
Step (1), mixing tetrahydrofuran and N, N-dimethylformamide to obtain a mixed solution;
and (2) adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 500rpm and the temperature of 45 ℃ for 20 hours to obtain the membrane casting solution.
Step (3), the temperature of the 3D printing platform is reduced to-20 ℃ in advance, then the casting film liquid obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support, wherein the printing parameters comprise that the temperature of a storage bin and a printing nozzle is 50 ℃, the moving speed of the printing nozzle is 2.5mm/s, and the extrusion pressure of the printing nozzle is 5.5bar;
the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to-22 ℃, standing for 5 hours, and entering the step 4.2;
step 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is an integer and is 7; and t is 4 ℃, and the porous bone repair scaffold with the nanofiber surface is obtained.
Specifically, step 4.2, soaking the printing support in water with the temperature t, and replacing the original soaking water with deionized water with the temperature t every alpha minutes within the 1 st hour period; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2 nd hour period; replacing the original soaking water with deionized water at the temperature t every gamma minute within the 3-hour time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within the time period from delta-3 hours to delta to obtain the stent of the comparative example 2, wherein alpha is 10min, beta is 20min, and gamma is 30min.
In the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 75 percent;
n, N-dimethylformamide: the balance;
in the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 5 percent;
polylactic acid: 30 percent.
In comparison with example 3, in comparative example 2, the sample of comparative example 2 was obtained without adding sodium chloride, and the ratio of tetrahydrofuran to N, N-dimethylformamide was different, and the other reaction conditions were the same.
Verification and conclusion
1. Micro-nanofiber surface characterization
The nanofiber surface porous bone repair scaffold prepared in the examples 3 to 8, the scaffold in the comparative example 1 and the scaffold in the comparative example 2 are characterized under a scanning electron microscope,
wherein the nanofiber surface porous bone repair scaffold prepared in the embodiments 3 to 8 respectively have the fiber scaffold pore diameter of 390.63 +/-35.42 mu m and uniform fiber distribution.
FIG. 1 is a scanning electron microscope image of the nanofiber surface porous bone repair scaffold of example 3, and the scale bar is 4 μm.
Fig. 2 is a spectrum diagram of the nanofiber surface porous bone repair scaffold of example 3.
FIG. 3 is a scanning electron microscope image of the scaffold 1 for the nanofiber surface porous bone repair of example 8, which is scaled to 2 μm.
FIG. 4 is a scanning electron micrograph of a stent of comparative example 1, which is scaled to 4 μm.
FIG. 5 is an energy spectrum of the stent of comparative example 1. From the comparison of fig. 2 and 5, a calcium ion peak appears in the energy spectrum of fig. 2, but a calcium ion peak does not appear in fig. 5, thus demonstrating that beta-calcium phosphate is loaded into the nanofiber surface porous bone repair scaffold of the present invention.
Meanwhile, comparing fig. 3 with fig. 1, the difference of the surface structures of the two is not great, thereby showing that the precooling temperature of the printing platform at-20 ℃ and-4 ℃ has no obvious influence on the forming of the microstructure of the printing support.
2. Biocompatibility
The nanofiber surface porous bone repair scaffold prepared in examples 3 to 8, the scaffold of comparative example 1 and the scaffold of comparative example 2 were immersed in 95% alcohol and soaked for 12 hours, respectively, and then irradiated under an ultraviolet lamp for 12 hours, and finally cells were inoculated and culture induced.
Wherein, FIG. 6 is a cell seeding map of the nanofiber surface porous bone repair scaffold of example 3, and the scale bar is 50 μm.
FIG. 7 is a staining pattern of viable cells of the nanofiber surface porous bone repair scaffold of example 3 after cell seeding, and the scale bar is 500 μm.
Fig. 8 is a graph of the scaffold seeded cells of comparative example 1, with scale bar =50 μm.
Fig. 9 is a graph of staining of viable cells after seeding the cells of comparative example 1, with scale bar =500 μm.
FIG. 10 is a graph showing the growth of the nanofiber surface porous bone repair scaffold of example 3 after being seeded with cells, and the growth of the conventional two-dimensional cultured cells, compared with the scaffold of comparative example 1.
FIGS. 11, 12 and 13 are comparison graphs of osteogenic differentiation-related gene assays after induction culture of cells of the scaffold of comparative example 1 and the nanofiber surface porous bone repair scaffold of example 3, respectively.
As can be seen from fig. 6, 7, 8 and 9, in comparative example 1, no β -tricalcium phosphate was added, the other reaction conditions were the same, and after no β -tricalcium phosphate was added in comparative example 1, the surface of the extruded scaffold still had a significant nanofiber microporous structure, and the biocompatibility was good.
It can be seen from fig. 10 that the cell growth rate of both example 3 and comparative example 1 is much higher than that of the conventional two-dimensional cultured cells, and that the cell growth rate of example 3 with β -tricalcium phosphate is higher than that of comparative example 1 without addition of β -tricalcium phosphate after 7 days of growth.
Runx2, COL-I and OCN of FIGS. 11 to 13 are all common bone cell-specific transcription factors. The two-dimensional culture is a traditional cell culture mode, the non-two-dimensional culture (PLA and PLA/beta-TCP) is cell culture on a scaffold, wherein the PLA/beta-TCP is the nanofiber surface porous bone repair scaffold in example 3, the PLA is the scaffold in comparative example 1, the non-induction of the two-dimensional culture refers to induction culture by using an osteogenesis induction medium under the traditional culture condition, the induction of the two-dimensional culture refers to the use of a normal medium, and the PLA/beta-TCP in figures 11 to 13 are all high-expression, which shows that the bone strengthening is realized, namely, the nanofiber surface porous bone repair scaffold is more beneficial to osteogenesis.
The results show that after the scaffold prepared in examples 3 to 8 is inoculated with cells, the biocompatibility is good, the cell proliferation speed is high compared with that of the traditional two-dimensional culture, and the effect of promoting bone differentiation is obvious.
3. Tensile strength
The nanofiber surface porous bone repair scaffold prepared in examples 3 to 8 and the scaffold of comparative example 2 were subjected to mechanical property correlation tests, respectively.
The nanofiber surface porous bone repair scaffold prepared in examples 3 to 8 measured tensile strength of 2.0Mpa to 2.1Mpa.
The stent of comparative example 2, to which no sodium chloride was added, had a tensile strength of less than 2.0Mpa, and the mechanical strength of the stent after extrusion was insufficient.
Finally, it should be noted that the above embodiments are only used for illustrating the technical solutions of the present invention and not for limiting the protection scope of the present invention, and although the present invention is described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention.
Claims (10)
1. A preparation method of a nanofiber surface porous bone repair scaffold is characterized by comprising the following steps: the method comprises the following steps:
mixing tetrahydrofuran, N-dimethylformamide and sodium chloride to obtain a mixed solution;
adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1) to obtain a membrane casting solution;
step (3) cooling the 3D printing platform in advance, then taking the casting film liquid obtained in the step (2) as printing ink, and performing 3D printing in the 3D printing platform according to printing parameters to obtain a printing support;
and (4) cooling and washing the printing support obtained in the step (3) to obtain the nanofiber surface porous bone repair support.
2. The method for preparing the nanofiber surface porous bone repair scaffold according to claim 1, wherein in the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 50% -75%;
sodium chloride: 5% -20%;
n, N-dimethylformamide: the balance;
in the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 2% -15%;
polylactic acid: 20 to 40 percent.
3. The method for preparing the nanofiber surface porous bone repair scaffold according to claim 2, wherein in the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 60% -70%;
sodium chloride: 8 to 12 percent;
n, N-dimethylformamide: the balance;
in the casting solution, the mass-to-volume ratio is as follows:
β -tricalcium phosphate: 4% -7%;
polylactic acid: 25 to 32 percent.
4. The method for preparing the nanofiber surface porous bone repair scaffold according to claim 3, wherein in the mixed solution, the weight ratio is as follows:
tetrahydrofuran: 67.5 percent;
sodium chloride: 22.5 percent;
n, N-dimethylformamide: the balance;
in the casting solution, the mass volume ratio is as follows:
beta-tricalcium phosphate: 5 percent;
polylactic acid: 30 percent.
5. The preparation method of the nanofiber surface porous bone repair scaffold according to any one of claims 1 to 4, wherein: and (2) specifically, adding beta-tricalcium phosphate and polylactic acid into the mixed solution obtained in the step (1), stirring at the speed of 450-550 rpm at the temperature of 35-45 ℃, and stirring for 18-24 h to obtain the membrane casting solution.
6. The preparation method of the nanofiber surface porous bone repair scaffold according to any one of claims 1 to 4, wherein: the step (3) is specifically that the temperature of the 3D printing platform is reduced to-20-4 ℃ in advance, then the casting solution obtained in the step (2) is used as printing ink, and 3D printing is carried out according to printing parameters to obtain a printing support;
the printing parameters comprise the temperature of the stock bin and the printing nozzle is 30-60 ℃, the moving speed of the printing nozzle is 2-3 mm/s, and the extrusion pressure of the printing nozzle is 4.3-6 bar.
7. The preparation method of the nanofiber surface porous bone repair scaffold according to any one of claims 1 to 4, wherein: the step (4) comprises the following steps:
step 4.1, cooling the printing support obtained in the step 3 to below minus 20 ℃, standing for 6-24 hours, and entering the step 4.2;
and 4.2, soaking the printing support in water with the temperature t, starting timing, and replacing the soaking water for multiple times from the starting point to a time period within delta hours, wherein delta is more than or equal to 4 and less than or equal to 10, is an integer, and t is more than or equal to 2 ℃ and less than or equal to 5 ℃, so as to obtain the nanofiber surface porous bone repair support.
8. The preparation method of the nanofiber surface porous bone repair scaffold according to claim 7, characterized in that: the step 4.2 is to soak the printing support in water with the temperature t, and in the 1 st hour period, replace the original soaking water with deionized water with the temperature t every other alpha minutes; replacing the original soaking water with deionized water at the temperature of t every other beta minutes within the 2h time period; replacing the original soaking water with deionized water at the temperature t every gamma minute within the 3-hour time period; and replacing the original soaking water with deionized water at the temperature t every 1 hour within a time period from delta-3 hours to delta to obtain the nanofiber surface porous bone repair scaffold, wherein t is more than or equal to 2 ℃ and less than or equal to 5 ℃, alpha is 10min, beta is 20min, and gamma is 30min.
9. The preparation method of the nanofiber surface porous bone repair scaffold according to any one of claims 1 to 4, wherein: the pore diameter of the porous bone repair scaffold on the surface of the nanofiber is 390.63 microns +/-35.42 microns;
the tensile strength of the porous bone repair scaffold with the nanofiber surface is 2.0-2.1 MPa.
10. The nanofiber surface porous bone repair scaffold is characterized in that: the nanofiber surface porous bone repair scaffold is prepared by the preparation method of any one of claims 1 to 9.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN202210853278.8A CN115230142A (en) | 2022-07-20 | 2022-07-20 | Nanofiber surface porous bone repair scaffold and preparation method thereof |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CN202210853278.8A CN115230142A (en) | 2022-07-20 | 2022-07-20 | Nanofiber surface porous bone repair scaffold and preparation method thereof |
Publications (1)
Publication Number | Publication Date |
---|---|
CN115230142A true CN115230142A (en) | 2022-10-25 |
Family
ID=83673615
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CN202210853278.8A Pending CN115230142A (en) | 2022-07-20 | 2022-07-20 | Nanofiber surface porous bone repair scaffold and preparation method thereof |
Country Status (1)
Country | Link |
---|---|
CN (1) | CN115230142A (en) |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN106730026A (en) * | 2017-03-01 | 2017-05-31 | 北京大学第三医院 | A kind of tissue engineering bone/cartilage compound rest and preparation method |
WO2018078130A1 (en) * | 2016-10-28 | 2018-05-03 | Paul Gatenholm | Preparation and applications of 3d bioprinting bioinks for repair of bone defects, based on cellulose nanofibrils hydrogels with natural or synthetic calcium phosphate particles |
CN109364304A (en) * | 2018-10-16 | 2019-02-22 | 南京邦鼎生物科技有限公司 | A kind of method that 3D printing prepares degradable homogeneity multifunctional bio biomimetic scaffolds |
CN111068110A (en) * | 2019-11-25 | 2020-04-28 | 中国科学院长春应用化学研究所 | 3D printing degradable composite stent, preparation method thereof and loading composite stent |
CN113370533A (en) * | 2021-04-25 | 2021-09-10 | 中国人民解放军空军军医大学 | Preparation method of 3D printing shapeable guide bone regeneration membrane |
CN113858610A (en) * | 2021-09-06 | 2021-12-31 | 江苏卓见医疗用品有限公司 | Medical fibrous surface dressing and preparation method and application thereof |
-
2022
- 2022-07-20 CN CN202210853278.8A patent/CN115230142A/en active Pending
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2018078130A1 (en) * | 2016-10-28 | 2018-05-03 | Paul Gatenholm | Preparation and applications of 3d bioprinting bioinks for repair of bone defects, based on cellulose nanofibrils hydrogels with natural or synthetic calcium phosphate particles |
CN106730026A (en) * | 2017-03-01 | 2017-05-31 | 北京大学第三医院 | A kind of tissue engineering bone/cartilage compound rest and preparation method |
CN109364304A (en) * | 2018-10-16 | 2019-02-22 | 南京邦鼎生物科技有限公司 | A kind of method that 3D printing prepares degradable homogeneity multifunctional bio biomimetic scaffolds |
CN111068110A (en) * | 2019-11-25 | 2020-04-28 | 中国科学院长春应用化学研究所 | 3D printing degradable composite stent, preparation method thereof and loading composite stent |
CN113370533A (en) * | 2021-04-25 | 2021-09-10 | 中国人民解放军空军军医大学 | Preparation method of 3D printing shapeable guide bone regeneration membrane |
CN113858610A (en) * | 2021-09-06 | 2021-12-31 | 江苏卓见医疗用品有限公司 | Medical fibrous surface dressing and preparation method and application thereof |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CN101461963B (en) | Multiplex composite bone tissue engineering bracket material capable of degrading gradiently and preparation method thereof | |
Solchaga et al. | A rapid seeding technique for the assembly of large cell/scaffold composite constructs | |
US20030082808A1 (en) | Composite biodegradable polymer scaffold | |
CN106581762B (en) | 3D printing biological ink, preparation method and 3D printing forming method | |
CN111097068B (en) | Bionic hydroxyapatite powder/gelatin/sodium alginate composite 3D printing support and preparation method thereof | |
Li et al. | From 2D to 3D: The morphology, proliferation and differentiation of MC3T3-E1 on silk fibroin/chitosan matrices | |
CN110540404B (en) | Calcium phosphate bone cement with hollow through structure, preparation method and application thereof | |
CN110947031B (en) | Bone tissue engineering scaffold material with high biological activity and preparation method and application thereof | |
CN110075361A (en) | A kind of preparation method of high-intensity and high-tenacity cartilage frame | |
CN104958785A (en) | Composite bone repairing material of two-stage three-dimensional structure and preparing method of composite bone repairing material | |
CN112791239B (en) | Preparation method of super-bionic soft and hard tissue composite scaffold | |
JP2005160669A (en) | Manufacturing method of biological tissue prosthesis | |
CN114014647B (en) | Zinc silicate composite tricalcium phosphate ceramic support and preparation method and application thereof | |
CN101703807B (en) | Polylactic acid/chitosan composite nano fiber scaffold, preparation method and application thereof | |
CN102145193A (en) | Cuttlebone conversion series porous biological ceramics | |
CN114042191A (en) | Cell-printed osteogenic functional scaffold and preparation method and application thereof | |
CN111249523B (en) | Bone-like composite material support and preparation method thereof | |
CN115230142A (en) | Nanofiber surface porous bone repair scaffold and preparation method thereof | |
CN111187069B (en) | Titanium dioxide and magnesium oxide composite biomedical ceramic material and preparation method thereof | |
CN103480036A (en) | Preparation method for porous nano-composite support material of bone tissue engineering | |
CN115463263A (en) | Injectable double-network hydrogel system and preparation method and application thereof | |
Li et al. | 3D printed hydroxyapatite/silk fibroin/polycaprolactone artificial bone scaffold and bone tissue engineering materials constructed with double-transfected bone morphogenetic protein-2 and vascular endothelial growth factor mesenchymal stem cells to repair rabbit radial bone defects | |
Tan et al. | Research on the osteogenesis and biosafety of ECM–Loaded 3D–Printed Gel/SA/58sBG scaffolds | |
JP2006230817A (en) | Biological tissue compensation material, and method of manufacturing the same | |
CN110624129B (en) | Corrosion-resistant osteoinductive silk fibroin/hydroxyapatite/magnesium oxide gel sponge and preparation method thereof |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PB01 | Publication | ||
PB01 | Publication | ||
SE01 | Entry into force of request for substantive examination | ||
SE01 | Entry into force of request for substantive examination |