ObjectiveTo explore the preparation method, physical and chemical properties, and biocompatibility of a conductive composite scaffold based on polypyrrole/silk fibroin (PPy/SF) fiber with " shell-core” structure, and to provide a preliminary research basis for the application in the field of tissue engineered neuroscience.Methods The conductive fibers with " shell-core” structure were prepared by three-dimensional printing combined with in-situ polymerization. PPy/SF fiber-based conductive composite scaffolds were formed by electrospinning. In addition, core-free PPy conductive fibers and SF electrospinning fibers were prepared. The stability, biomechanics, electrical conductivity, degradation performance, and biological activity of each material were tested to analyze the comprehensive properties of fiber-based conductive composite scaffolds.ResultsCompared with pure core-free PPy conductive fibers and SF electrospinning fibers, the PPy/SF fiber-based conductive composite scaffolds with " shell-core” structure could better maintain the stability performance, enhance the mechanical stretchability of the composite scaffolds, maintain long-term electrical activity, and improve the anti-degradation performance. At the same time, PPy/SF conductive composite scaffolds were suitable for NIH3T3 cells attachment, conducive to cell proliferation, and had good biological activity.ConclusionPPy/SF fiber-based conductive composite scaffolds meet the needs of conductivity, stability, and biological activity of artificial nerve grafts, and provide a new idea for the development of a new generation of high-performance and multi-functional composite materials.
Objective To review the details of the current effortsto reconstruct or replace the meniscus.Methods Three kinds of proceduresof reconstructing or replacing the meniscus were analyzed and evaluated by an extensive review of the latest literatures concerned. Results Three kinds of techniques were established to reconstruct the meniscus clinically, i.e., the allograft of the meniscus, meniscal reconstruction with the autotendon, and the meniscus scaffold. There were still a few defects in the meniscal replacement, and so the curative techniques would still be investigated. Conclusion Many efforts have been made to reconstruct the meniscus after its injury or its resection so as to prevent degeneration of the knee joint. The meniscal replacement has been employed for many years, but it has not worked so well. The establishment of an ideal replacement of the meniscus requires further studies. Therefore, reconstruction of the meniscus function is still a challenging problem to the surgeons concerned.
OBJECTIVE: To investigate the feasibility of the chitosan-collagen membrane (CCM) as a dermal substitute. METHODS: Fresh bovine tendo calcaneus collagen was dispersed in 0.5 mol/L acetic acid, co-precipitated with chitosan and lyophilized. Dry membranes were cross-linked in 0.05% glutaraldehyde for 24 hours. In vitro its degrading rate was measured by use of collagenase degrading test. The chitosan-collagen membrane was implanted to subcutaneous dorsal sites of SD rats. After implantation, histocompatibility, vascularity and degradation were observed in vivo. RESULTS: The chitosan-collagen membrane was yellowish, translucent, and porous. Pore size ranged 50-250 microns, and collagen fiber bundles were reticular arrangement in the membrane. It had slower degradation than pure collagen membrane by collagenase in vitro. Subcutaneous implantation test showed the minimal inflammation, good histocompatibility and earlier vascularization. The membrane degradation was slower in vivo. Eight weeks after implantation, organized collagen structure was retained. CONCLUSION: The chitosan-collagen membrane has better physical and biological properties, ideal histocompatibility, earlier vascularization and slower degradation. Therefore, It is an optimum substitute for dermal scaffold.
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.
ObjectiveTo construct large block of engineered liver tissue by co-culture of fibroblasts and hepatocytes on collagen hydrogels in vitro and do in vivo implantation research. MethodsSilastic mould was prepared using three-dimensional printing technology. The collagen hydrogel scaffold was prepared by collagen hydrogel gel in the silicone mould and was removed. Sprague Dawley rat lung fibroblasts were co-cultured with primary hepatocytes at a ratio of 0.4:1 on the collagen hydrogel scaffold to construct large block of engineered liver tissue in vitro (group B), and primary hepatocytes cultured on the collagen hydrogel scaffold served as control group (group A). The cell morphology was observed, and the liver function was tested at 1, 3, 7, 14, and 21 days after culture. The rat model (n=24) of hepatic cirrhosis was made by subcutaneous injection of carbon tetrachloride. And in vivo implantation study was carried in cirrhosis rat model. The phenotypic characteristics and functional expression of hepatocytes were evaluated at 3, 7, 14, 21, and 28 days after implantation. ResultsIn vitro results indicated that hepatocytes in group B exhibited compact polyhedral cells with round nuclei and high expression of liver function. Moreover, cells aggregated to the most at 7 days. Album production and urea synthesis incresed significantly when compared with group A (P<0.05). In vivo results showed hepatocytes in group B survived for 28 days, and albumin production and urea synthesis were significantly increased. In addition, hepatocytes showed an aggregated distribution and cord-like structures, which was similar to normal liver tissue. ConclusionThe large block of engineered liver tissue constructed by co-cultured cells can form tissue similar to normal liver tissue in vivo, and survive for a long time, laying foundations for building more complete engineered liver tissue in the future.
Objective To investigate the effect of dynamic compression and rotation motion on chondrogenesis of the 3rd passage cell-loaded three-dimensional scaffold in a joint-specific bioreactor in vitro so as to provide theoretical basis of the autologous chondrocyte transplantation in clinical practice. Methods Primary chondrocytes were isolated and cultured from the knee cartilage of 3-4 months old calves. The 3rd passage cells were seeded onto fibrin-polyurethane scaffolds (8 mm × 4 mm). Experiment included 5 groups: unloaded culture for 2 weeks (group A), direct load for 2 weeks (group B), unloaded culture for 4 weeks (group C), direct load for 4 weeks (group D), and unload for 2 weeks followed by load for 2 weeks (group E). The cell-scaffold was incubated in incubator (unload) or in a joint-specific bioreactor (load culture). At different time points, the samples were collected for DNA and glycosaminoglycan (GAG) quantification detect; mRNA expressions of chondrogenic marker genes such as collagen type I, collagen type II, Aggrecan, cartilage oligomeric matrix protein (COMP), and superficial zone protein (SZP) were detected by real-time quantitative PCR; and histology observations were done by toluidine blue staining and immunohistochemistry staining. Results No significant difference was found in DNA content, GAG content, and the ratio of GAG to DNA among 5 groups (P gt; 0.05). After load, there was a large number of GAG in the medium, and the GAG significantly increased with time (P lt; 0.05). The mRNA expression of collagen type I showed no significant difference among 5 groups (P gt; 0.05). The mRNA expression of collagen type II in group B was significantly increased when compared with group A (P lt; 0.01), and groups D and E were significantly higher than group C (P lt; 0.01); the mRNA expression of Aggrecan in groups D and E were significantly increased when compared with group C (P lt; 0.01), and group E was significantly higher than group D (P lt; 0.01); the mRNA expression of COMP in group B was significantly increased when compared with group A (P lt; 0.01), and group E was significantly higher than group C (P lt; 0.01); and the mRNA expression of SZP in group E was significantly increased when compared with groups C and D (P lt; 0.05). The toluidine blue staining and immunohistochemistry staining displayed that synthesis and secretion of GAG could be enhanced after load; no intensity changes of collagen type I and collagen type II were observed, but intensity enhancement of Agrrecan was seen in groups D and E. Conclusion Different dynamic loads can promote chondrogenesis of the 3rd passage chondrocytes. Culture by load after unload may be the best culture for chondrogenesis, while the 3rd passage chondrocytes induced by mechanical load hold less capacity of chondrogenesis.
ObjectiveTo explore the possibility of constructing tissue engineered adipose by adipose tissue derived extracellular vesicles (hAT-EV) combined with decellularized adipose tissue (DAT) scaffolds, and to provide a new therapy for soft tissue defects.MethodsThe adipose tissue voluntarily donated by the liposuction patient was divided into two parts, one of them was decellularized and observed by HE and Masson staining and scanning electron microscope (SEM). Immunohistochemical staining and Western blot detection for collagen type Ⅰ and Ⅳ and laminin were also employed. Another one was incubated with exosome-removed complete medium for 48 hours, then centrifuged to collect the medium and to obtain hAT-EV via ultracentrifugation. The morphology of hAT-EV was observed by transmission electron microscopy; the nanoparticle tracking analyzer (NanoSight) was used to analyze the size distribution; Western blot was used to analyse membrane surface protein of hAT-EV. Adipose derived stem cells (ADSCs) were co-cultured with PKH26 fluorescently labeled hAT-EV, confocal fluorescence microscopy was used to observe the uptake of hAT-EV by ADSCs. Oil red O staining was used to evaluate adipogenic differentiation after hAT-EV and ADSCs co-cultured for 15 days. The DAT was scissored and then injected into the bilateral backs of 8 C57 mice (6-week-old). In experimental group, 0.2 mL hAT-EV was injected weekly, and 0.2 mL PBS was injected weekly in control group. After 12 weeks, the mice were sacrificed, and the new fat organisms on both sides were weighed. The amount of new fat was evaluated by HE and peri-lipoprotein immunofluorescence staining to evaluate the ability of hAT-EV to induce adipogenesis in vivo.ResultsAfter acellularization of adipose tissue, HE and Masson staining showed that DAT was mainly composed of loosely arranged collagen with no nucleus; SEM showed that no cells and cell fragments were found in DAT, and thick fibrous collagen bundles could be seen; immunohistochemical staining and Western blot detection showed that collagen type Ⅰ and Ⅳ and laminin were retained in DAT. It was found that hAT-EV exhibited a spherical shape of double-layer envelope, with high expressions of CD63, apoptosis-inducible factor 6 interacting protein antibody, tumor susceptibility gene 101, and the particle size of 97.9% hAT-EV ranged from 32.67 nmto 220.20 nm with a peak at 91.28 nm. Confocal fluorescence microscopy and oil red O staining showed that hAT-EV was absorbed by ADSCs and induced adipogenic differentiation. In vivo experiments showed that the wet weight of fat new organisms in the experimental group was significantly higher than that in the control group (t=2.278, P=0.048). HE staining showed that the structure of lipid droplets in the experimental group was more than that in the control group, and the collagen content in the control group was higher than that in the experimental group. The proportion of new fat in the experimental group was significantly higher than that in the control group ( t=4.648, P=0.017).ConclusionDAT carrying hAT-EV can be used as a new method to induce adipose tissue regeneration and has a potential application prospect in the repair of soft tissue defects.
【Abstract】 Objective To design a novel small-cal iber vascular graft using a decellularized allogeneic vascularscaffold pre-loaded with bFGF. Methods The decellularized canine common carotid were obtained by a detergent-enzymatic procedure, then the scaffolds were covalently l inked with heparin and pre-loaded with bFGF, the amount of binding bFGF and releasing curve were assayed by ELISA. Canine BMSCs expanded in vitro were seed on the scaffolds to observe the effects of binding bFGF on prol iferation. Both bFGF pre-loaded and non-pre-loaded decellularized grafts were implanted in canines as carotid artery interposition for 8 weeks, the patency was examined by digital subtraction angiography and histological method. Results Histology and electron microscopic examination of the decellularized scaffolds showed that cellular components were removed completely and that the extracellular matrix structure remained intact. The amount of binding bFGF positively related to the concentration of bFGF. There was a significant difference in the amount of binding bFGF between two different scaffoldsthroughout all bFGF concentrations(P lt; 0.05), and up to 100 ng/mL, the local and sustained release of bFGF from the heparin treated scaffolds were assayed up to 20 days. Additionally, MTT test showed the bFGF-preloaded scaffolds significantly enhanced the prol iferation of seeded BMSCs in vitro compared with non-bFGF-preloaded scaffolds at 3 days after seeding and thereafter(P lt; 0.01). Furthermore, in vivo canine experiments revealed that all 8 bFGF-pre-loaded scaffolds remained patent after 8 weeks of implantation, and host cell l ined the lumen and populated the wall. Only 1 non-bFGF-pre-loaded scaffold was patent, and the other 7 grafts were occluded because of thrombsus formation. Conclusion This study provides a new strategy to develop a small diameter vascular graft with excellent biocompatibil ity and high patency rate.
Objective To observe whether Cyclo-RGDfK (Arg-Gly-Asp-D-Phe-Lys) could enhance the adhesion of myofibroblast to decellularized scaffolds and upregulate the expression of Integrin αVβ3 gene. Methods Myofibroblast from the rat thoracic aorta was acquired by primary cell culture. The expression of Vimentin and α-smooth muscle actin(α-SMA) has been detected by immunoflurescent labeling. Decellularized valves have been randomly divided into three groups (each n=7). Group A (blank control): valves do not receive any pretreatment; Group B: valves reacted with linking agent NEthylN(3dimethylaminopropyl)carbodiimide hydrochloride (EDC) for 36 hours before being seeded; Experimental group: Cyclo-RGD peptide has been covalently immobilized onto the surface of scaffolds by linking agent EDC. The fifth generation of myofibroblast has been planted on the scaffolds of each group. The adhesion of myofibroblast to the scaffolds was evaluated by HE staining and electron scanning microscope. The expression of Integrin αVβ3 was quantified by halfquantitative reverse transcriptionpolymerase china reaction (RT-PCR). Results We can see that myofibroblast has exhibited b positive staining for Vimentin and α-SMA. Besides, it has been shown that the expression of Integrin αVβ3 was much higher in the experimental group than that of the group A and group B(Plt;0.05). There was no statistically difference in group A and group B (P=0.900). Conclusion RGD pretreatment does enhance the adhesive efficiency of seeding cells to the scaffolds and this effect may be related to the upregulation of Integrin αVβ3.
Objective To develop three-dimensional (3D) porous nanofiber scaffold of PLGA-silk fibroincollagen and to investigate its cytocompatibil ity in vitro. Methods Method of electrostatic spinning was used to prepare 3D porous nanofiber scaffold of PLGA-silk fibroin-collagen (the experimental group) and 3D porous nanofiber scaffold of PLGA (the control group). The scaffold in each group was observed by scanning electron microscope (SEM). The parameters of scaffold fiber diameter, porosity, water absorption rate, and tensile strength were detected. SC harvested from the bilateral brachial plexus and sciatic nerve of 8 SD suckl ing rats of inbred strains were cultured. SC purity was detected by S-100 immunohistochemistry staining. The SCs at passage 4 (5 × 104 cells/mL) were treated with the scaffold extract of each group at a concentration of 25%, 50%, and 100%, respectively; the cells treated with DMEM served as blank control group. MTT method was used to detect absorbance (A) value 1, 3, 5, and 7 days after culture. The SC at passage 4 were seeded on the scaffold of the experimental and the control group, respectively. SEM observation was conducted 2, 4, and 6 days after co-culture, and laser scanning confocal microscope (LSCM) observation was performed 4 days after co-culture for the growth condition of SC on the scaffold. Results SEM observation: the scaffold in two groups had interconnected porous network structure; the fiber diameter in the experimental and the control group was (141 ± 9) nm and (205 ± 11) nm, respectively; the pores in the scaffold were interconnected; the porosity was 87.4% ± 1.1% and 85.3% ± 1.3%, respectively; the water absorption rate was 2 647% ± 172% and 2 593% ± 161%, respectively; the tensile strength was (0.32 ± 0.03) MPa and (0.28 ± 0.04) MPa, respectively. S-100 immunohistochemistry staining showed that the SC purity was 96.5% ± 1.3%. MTT detection: SC grew well in the different concentration groups and the control group, the absorbance (A) value increased over time, significant differences were noted among different time points in the same group (P lt; 0.05), and there was no significant difference between the different concentration groups and the blank control group at different time points (P gt; 0.05). SEM observation: in the experimental group, SC grew well on the scaffold, axon connection occurred 4 days after co-culture, the cells prol iferated massively and secreted matrix 6 days after co-culture, and the growth condition of the cells was better than the control group. The condition observed by LSCM 4 days after co-culture was the same as that of SEM. Conclusion The 3D porous nanofiber scaffoldof PLGA-silk fibroin-collagen prepared by the method of electrostatic spinning is safe, free of toxicity, and suitable for SC growth, and has good cytocompatibil ity and proper aperture and porosity. It is a potential scaffold carrier for tissue engineered nerve.