Objective To review research progress of corneal tissueengineering.Methods The recent articles on corneal tissue engineering focus on source and selection of corneal cells, the effects of growth factors on culture of corneal cells in vitro. The preparation and selection of three-dimensional biomaterial scaffolds and their b and weak points were discussed. Results The corneal tissue engineering cells come from normal human corneal cells. The embryo corneal cell was excellent. Several kinds of growth factors play important roles in culture, growth and proliferation of corneal cell, and incroporated into matrix.Growth factors including basic fibroblast growth factor, keratinocyte growth factor, transforming growth factor β1 and epidermal growth factor was favor to corneal cell. Collagen, chitosan and glycosaninoglycans were chosen as biomaterial scaffolds. Conclusion Human tissue engineering cornea can be reconstructed and transplanted. It has good tissue compatibility and can be used as human corneal equivalents.
Objective To study the adhesion characteristic in vitrobetween porous biphasic calcium phosphate(BCP) nanocomposite and bone marrow mesenchymal stem cells (MSCs) that have been induced and proliferated. Methods MSCs obtained from SD ratbone marrow were in vitro induced and proliferated. After their osteoblastic phenotype were demonstrated, MSCs were seeded onto prepared porous BCP nanocomposite(experiment group)and common porous hydroxyapatite (control group). Their adhesion situation was analyzed by scanning electron microscope. The initial optimal cell seeding density was investigated between new pattern porous BCP nanocomposite and MSCs by MTT automated colormetric microassay method. Results The differentiation of MSCs to osteoblastic phenotype were demonstrated by the positive staining of mineralized node, alkaline phosphatase (ALP) and collagen typeⅠ, the most appropriate seeding density between them was 2×106／ml. The maximal number which MSCs could adhere to porous BCP nanocomposite was 1.28×107/cm3. Conclusion MSCs can differentiate to osteoblastic phenotype.The MSCs were well adhered to porous BCP nanocomposite.
OBJECTIVE: To prepare chitosan-gelatin/hydroxyapatite (CS-Gel/HA) composite scaffolds, and to investigate the influence of components and preparing conditions to their micromorphology. METHODS: The CS-Gel/HA composite scaffolds were prepared by phase-separation method. Micromorphology and porosity were detected by using scanning electron microscope and liquid displacement method respectively. RESULTS: Porous CS-Gel/HA composite scaffolds could be prepared by phase-separation method, and their density and porosity could be controlled by adjusting components and quenching temperature. CONCLUSION: The study suggests the feasibility of using CS-Gel/HA composite scaffolds for the transplantation of autogenous osteoblasts to regenerate bone tissue.
ObjectiveTo fabricate the bionic scaffolds of rat spinal cord by combining three dimensional (3D) printer and 3D software, so as to lay the foundation of theory and technology for the manufacture of scaffolds by using biomaterials. MethodsThree female Sprague Dawley rats were scanned by 7.0T MRI to obtain the shape and position data of the cross section and gray matter of T8 to T10 spinal cord. Combined with data of position and shape of nerve conduction beam, the relevant data were obtained via Getdata software. Then the 3D graphics were made and converted to stereolithography (STL) format by using SolidWorks software. Photosensitive resin was used as the materials of spinal cord scaffolds. The bionic scaffolds were fabricated by 3D printer. ResultsMRI showed that the section shape of T8 to T10 segments of the spinal cord were approximately oval with a relatively long sagittal diameter of (2.20±0.52) mm and short transverse diameter of (2.05±0.24) mm, and the data of nerve conduction bundle were featured in the STL format. The spinal cord bionic scaffolds of the target segments made by 3D printer were similar to the spinal cord of rat in the morphology and size, and the position of pores simulated normal nerve conduction of rat spinal cord. ConclusionSpinal cord scaffolds produced by 3D printer which have similar shape and size of normal rat spinal cord are more bionic, and the procedure is simple. This technology combined with biomaterials is also promising in spinal cord repairing after spinal cord injury.
Objective To investigate the feasibility oftissue engineered intervertebral disc for regeneration of discs. Methods A three-dimensional porous poly(L-lactic-co-glycolic acid) (PLGA) scaffold was fabricated by temperature induced phase separation method. Human fetal disc cells were isolated and cultured in vitro. The disc cells labeledwith a PKH-26 fluorescent dye were seeded into a threedimensional porous scaffold. The proliferation of disc cells with PKH-26 fluorescent labels was assessed by using MTT uptake, laser fluorescence microscopy and SEM. Results Human fetal disc cells displayed a polygonal shape in primary monolayer culture. A regular arrangement and microtubules orientationstructure scaffold with 50-300 μm in diameter was fabricated by thermal-induced phase separation technique. MTT uptake and fluorescent microscopy examination indicated that the seeded disc cells were viable and showed proliferation activity within a porous scaffold. Conclusion The above findings support potential applications of tissue engineered disc in treatment of disc degenerative diseases.
OBJECTIVE: To explore the possibility to bridge peripheral nerve defects by xenogeneic acellular nerve basal lamina scaffolds. METHODS: Thirty SD rats were randomly divided into 5 groups; in each group, the left sciatic nerves were bridged respectively by predegenerated or fresh xenogeneic acellular nerve basal lamina scaffolds, autogenous nerve grafting, fresh xenogeneic nerve grafting or without bridging. Two kinds of acellular nerve basal lamina scaffolds, extracted by 3% Triton X-100 and 4% deoxycholate sodium from either fresh rabbit tibial nerves or predegenerated ones for 2 weeks, were transplanted to bridge 15 mm rat sciatic nerve gaps. Six months after the grafting, the recovery of function was evaluated by gait analysis, pinch test, morphological and morphometric analysis. RESULTS: The sciatic nerve function indexes (SFI) were -30.7% +/- 6.8% in rats treated with xenogeneic acellular nerve, -36.2% +/- 9.7% with xenogeneic predegenerated acellular nerve, and -33.9% +/- 11.3% with autograft respectively (P gt; 0.05). The number of regenerative myelinated axons, diameter of myelinated fibers and thickness of myelin sheath in acellular xenograft were satisfactory when compared with that in autograft. Regenerated microfascicles distributed in the center of degenerated and acellular nerve group. The regenerated nerve fibers had normal morphological and structural characters under transmission electron microscope. The number and diameter of myelinated fibers in degenerated accellular nerve group was similar to that of autograft group (P gt; 0.05). Whereas the thickness of myelin sheath in degenerated accellular nerve group was significantly less than that of autograft group (P lt; 0.05). CONCLUSION: The above results indicate that xenogeneic acellular nerve basal lamina scaffolds extracted by chemical procedure can be successfully used to repair nerve defects without any immunosuppressants.
ObjectiveTo assess the suitability of P (3HB-co-4HB) combined with embryonic stem cells (ESCs) for myocardial patch formation and whether adding vitamin C would improve inductivity or not. Method We extracted mouse embryonic fibrous cell from three clean female white Kunming mouses at a mean body weight of 37.5 grams. We recovered and cultured mouse ESCs. Those mouse embryonic stem cells were obtained from Shanghai Institutes of Biological Sciences. We took pendant-drop method to form embryonic bodies (EBs) and co-cultured them with myocardial patch. The experimental group were cultured in the substate with vitamin C while the control group were cultured in the substate without vitamin C. We immunostained the myocardial patch and observed them by scanning electron microscope. We calculated the differentiation efficiency and mapped the distribution curve of induction time. ResultsThe scattergram showed that the differentiation efficiency increased gradually. The differentiation efficiency of the group with vitamin C was 71.1% and the group without vitamin C was 17.8%. There was a statistical difference between the two groups (P < 0.05). ConclusionOn the biological patch of P (3HB-co-4HB), ESCs could grow, proliferate, and differentiate into myocardial cell and adding vitamin C into it could improve the differentiation efficiency.
Objective To locate sinoatrial node (SAN) in suckl ing pigs, to develop a rel iable method for isolation, purification and cultivation of SAN cells and to observe the compatibil ity of SAN cells and Col I fiber scaffold. Methods Five newborn purebred ChangBaiShan suckl ing pigs (male and female), aged less than 1-day-old and weighing 0.45-0.55 kg, wereused. Multi-channels electrophysiological recorder was appl ied to detect the original site of atrial waves. Primary SAN cells harvested from that area were cultured by the conventional culture method and the purification culture method including differential velocity adherent technique and 5-BrdU treatment, respectively. Atrial myocytes isolated from the left atrium underwent purified culture. Cell morphology, time of cell attachment, time of unicellular pulsation, and pulsation frequency were observed using inverted microscope. The purified cultured SAN cells (5 × 105 cells/mL) were co-cultured with prewetted Col I fiber scaffold for 5 days, and then the cells were observed by HE staining and scanning electron microscope (SEM). Results The atrial waves occurred firstly at the area of SAN. The purified cultured SAN cells were spindle, triangular, and irregular in morphology, and the spindle cells comprised the greatest proportion. Atrial myocytes were not spindle-shaped, but primarily triangular and irregular. The proportion of spindle cells in the conventional cultured SAN cells was decreased from 73.0% ± 2.9% in the purified cultured SAN cells, to 44.7% ± 2.3% (P lt; 0.01), and the proportion of irregular cells increased from 7.0% ± 1.7% in the purified cultrued SAN cells to 36.1% ± 2.6% (P lt; 0.01) . The proportion of the triangular cells in the purified and the conventional cultured SAN cells was 20.0% ± 2.1% and 19.2% ± 2.5%, respectively (P gt; 0.05). At 5 days after co-culture, HE staining displayed lots of SAN cells in Col I fiber scaffold, and SEM demonstrated conglobate adherence of the cells to the surface and lateral pore wall of scaffold, mutual connections of the cell processes, or attachment of cells to lateral pore wall of scaffold through pseudopodia. Conclusion With accurate SAN location, the purification culture method containing differential velocity adherent technique and 5-BrdU treatment can increase the proportion of spindle cells and is a rel iable method for the purification and cultivation of SAN cells. The SAN cells and Col I fiber scaffold have a good cellular compatibil ity.
Objective To develop a novel porous three-dimensional scaffold and to investigate its physico-chemical properties for tissue engineering cartilage.Methods Refined 88% deacetylation degree chitosan was prepared and dissolved in 0.2 mol/L acetate acid and fully mixed with highly purified porcine type Ⅱcollagen in 0.5 mol/L acetate acid solution in a ratio of 4 to 1 (wt/wt). Freeze-drying process was employed to fabricate the composite scaffold. The construct wascross-linked by use of 1-ethyl-3(3-dimethyl aminopropyl) carbodiimide (EDC) and Nhydroxysuccinimide (NHS). A mechanical tester was utilized to determine the tensilestrength change before and after cross-linking. The microstructure was observed via scanning electron microscopy (SEM). The lysozyme degradation was performedto evaluate the degradability of the scaffold in vitro. Results A bulk scaffold with desired configuration was obtained. The mechanical test showed that the crosslinking treatment could enhance the mechanical strength of the scaffold. The SEM results revealed that the two constituents evenly distributed in the scaffold and that the matrix was porous, sponge-like with interconnected pore sizing 100250 μm. In vitro lysozyme degradation indicated that crosslinked or uncross-linked composite scaffolds had faster degradation rate than the chitosan matrix. Conclusion Chitosan and typeⅡcollagen can be developed into a porous three-dimensional scaffold. The related physico-chemical tests suggest that the composite socaffold meets requirements for tissue engineered scaffold and may serve as an alternative cellcarrier for tissue engineering cartilage.
Objective To comment on the recent advances of production and application of the bio-derived scaffold in the tissue engineered peripheral nerve. Methods The recent articles were systematically analyzed, and then the production methods of the bio-derived scaffold and its application to the tissue engineered peripheral nerve were evaluated and prospected. Results B iological tissues were processed by some methods to produce the bio-derived materials. These mat erials could maintain the structure and components of the tissues. Moreover, the immunogenicity of these materials was reduced. Conclusion Application of the bio-derived materials is a trend in the fabricating scaffold of the tissue en gineered peripheral nerve.