Scaffold is one of the key elements required for tissue engineering. Porous scaffolds have several special advantages for muscle tissue engineering, and they are beneficial to cell survival, myogenic differentiation, and vascular ingrowth. The performance of porous scaffolds is closely related to the property of the biomaterials used. Additionally, the pore size and porosity may affect cell adhesion, proliferation, and differentiation. This review focuses on the application of porous scaffolds in muscle tissue engineering, including their categories, application, and advantages.
ObjectiveTo review the research progress of tissue engineered scaffolds and stromal-derived factor 1 (SDF-1) composite graft. MethodsThe recent papers about SDF-1 with different kinds of tissue engineered scaffolds were reviewed and analyzed. The primary mechanism of SDF-1 homing function for stem cells was retrospected. The results of different kinds of tissue engineered scaffolds carrying SDF-1 for repairing the injured tissues and organs were reviewed. ResultsIt is shown that SDF-1 combined with tissue engineered scaffolds will play a role of multipotent stem cells chemotaxis, however, the exact chemotaxis mechanism has not been fully understood. It still needs more researches of SDF-1 effects in vivo. ConclusionAlthough some research progress has been made in regeneration in situ of tissue engineered scaffolds combined with SDF-1, it will need to further study on the mechanism of chemotactic functions of SDF-1 and its influence on proliferation and differentiation of cells.
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.
Objective To establish a model for studying on mechanical responses of osteoblasts seeded in 3 dimensional(3D) scaffold. Methods Fifty pieces of bioderived cancellous bones, whose holes were 500 to 800 μm and density was 0.36 to 0.45g/cm3, were obtained as the scaffolds. They were cultured with the third passage suspension of Wistar rat. Twenty-four of the 50 scaffolds were constructed under apparent strain sine waveform with amplitude of 1 000 με, frequency of 3 Hz, and duration of 3 min/d, as experimental group. The other scaffolds were control group. After 3day coculture, osteoblasts were observed with scanning electron microscope. The proliferation of the osteoblasts was checked by MTT on scheduled date. Results Scanning electron microscopic observation showed that osteoblasts ttached and spread on the trabeculae, which presented the validity of the model under proper mechanical condition. Experiment showed that mechanical environment promoted theproliferation of osteoblasts. The observation of proliferation of osteoblasts showed that the quantity of osteoblasts in the experimental group was higher than that in the control group 1,4,8,12,16,20,24, and 28 days after culturing. Therewas significant difference between the two groups 12,16,20,24,and 28 days afterculturing(P＜0.05). Conclusion The establishment of the model can facilitate the study of mechanical responses of osteoblasts under different conditions.
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.
Objective To explore the preparing methods in vitro and test the cl inical appl icabil ity of implantation in vivo of bone marrow stromal stem cells (BMSCs)-biphasic scaffold to repair defects of cartilage and subchondral bone and tocompare the differences in repaired outcomes of composite, single biphasic scaffold and rabbits themselves. Methods The upper chondral phase and the lower osseous phase of the plugs, using poly-lactic-co-glycol ic acid (PLGA), hydroxyapatite (HA), and other biomaterials, were fused into carrier scaffold, on which collagen type I (Col I) was coated. The surface and inner structure of bi phasic scaffold were observed under scanning electron microscope (SEM). BMSCs was isolated from the bone marrow of tibia and femurs of young New Zealand rabbits using centrifuging and washing, and their morphologies and adherences were observed everyday. Then BMSCs were inoculated on the surface of scaffold to form BMSCs-scaffold composites. Osteochondral defects were surgically created on articular surface of femoral intercondyles of 30 New Zealand rabbits, which were divided into groups A, B and C. In group A, a bi phasic osteochondral composite were implanted into defect, BMSCs and biphasic cyl indrical porous plug of PLGA-HA-Col I in group B, and group C was used as a control without implant. Specimens were harvested to make macroscopic and histological observations at the 1st, 3rd, 6th, and 9th months after operation respectively; meanwhile immunohistological and micro-computed tomography (micro CT) examinations were performed and graded at the 9th month after operation. Results SEM showed an excellent connection of holes in the biphasic scaffold infiltrated by Col I. Optical microscopy and SEM showed a good growth of BMSCs in scaffold without obvious cellular morphological changes and an accumulation in the holes. Macroscopic samples showed a resistant existence of defects of group C within 9 months; the scaffold completely degenerated and chondral-l ike tissue formed on articular surface with partly collapses and irregular defects in group A; and smoother surface without collapses and approach to normal with texture of new regeneration in group B. There were statistically significant differences in macroscopic results (P lt; 0.001), group B was superior to group A, and group C was the worst. The micro CT showed good repairs and reconstruction of subchondral bone, with a acceptable integration with newborn chondral-l ike tissue and host bone in group B. Quantificational analysis of relevantparameters showed no significant differences. Histological results showed inflammations located in defects at the 1st month, new tissue grew into scaffold at the 3rd month; new chondral-l ike tissue crept on the margin of defects and biphasic scaffold degenerated completely at the 6th month, and lots of collagen formed in subchondral bone with major fibrocartilage on chondralarea at the 9th month after surgery in groups A and B. In groups A and B, immunohistological observations were weak positive for Col II and positive for Col I. Conclusion Biphasic scaffold implanted in body can induce and accelerate repair of defects of articular cartilages which are mainly filled with fibrocartilage, especially for subchondral bone. Scaffold combined with BMSCs has the best repairing effects 9 months after implantation.
Objective To review the research progress of graphene and its derivatives in repair of peripheral nerve defect. Methods The related literature of graphene and its derivatives in repair of peripheral nerve defect in recent years was extensively reviewed. Results It is confirmed by in vitro and in vivo experiments that graphene and its derivatives can promote cell adhesion, proliferation, differentiation and neurite growth effectively. They have good electrical conductivity, excellent mechanical properties, larger specific surface area, and other advantages when compared with traditional materials. The three-dimensional scaffold can improve the effect of nerve repair. Conclusion The metabolic pathways and long-term reaction of graphene and its derivatives in the body are unclear. How to regulate their biodegradation and explain the electric coupling reaction mechanism between cells and materials also need to be further explored.
Objective To compare the effect of fabricating decellularized scaffold of homograft bioprosthetic tube valved (HBTV) with two kinds of cell detergents and to provide a homograft bioprosthetic scaffold for fabrication of tissueengineering heart valve (TEHV). Methods The active cells in the HBTV, which conserved by liquid nitrogen, were decellularized by low osmotic pressure of Tris buffer, in which containing sodium dodecylsulphate (SDS) and deoxycholic acid (DOA) respectively. The leaflets or aortic wall was fixed with fixative and stained with hematoxylin and eosin, collagen fibers or elastic fibers for observation and photographs by light microscope or by scanning electron microscope (SEM) after decellularized. Results When the leaflets of HBTV were incubated togetherwith 0.03% SDS or 0.5% DOA of Tris buffer respectively for 48 hours, the activeendothelial cells (ECs) in the leaflets were not only decellularized completely, but also reserved the collagen fibers or elastic fibers integrally, which is two of the main components of extracellular matrix (ECM). A part of fibroblast inthe center leaflets was reserved. The morphologic structure of leaflets after decellularized was not significantly different from that before decellularized. The concentration of SDS was increased to 0.1% when decellularized the cells of aortic wall, but DOA was still kept 0.5%. Conclusion The better decellularizedscaffold of HBTV obtained was disposed by 0.03%-0.1% SDS or 0.5% DOA, which wasadvantageous to adhesiveness and amplification of implantation cells on the decellularized scaffold of HBTV in order that HBV reendothelialized or for the TEHVfabricated in vitro.
Spinal cord injury (SCI), especially the complete SCI, usually results in complete paralysis below the level of the injury and seriously affects the patient’s quality of life. SCI repair is still a worldwide medical problem. In the last twenty years, Professor DAI Jianwu and his team pioneered complete SCI model by removing spinal tissue with varied lengths in rodents, canine, and non-human primates to verify therapeutic effect of different repair strategies. Moreover, they also started the first clinical study of functional collagen scaffold on patients with acute complete SCI on January 16th, 2015. This review mainly focusses on the possible mechanisms responsible for complete SCI. In common, recovery of some sensory and motor functions post complete SCI include the following three contributing reasons. ① Regeneration of long ascending and descending axons throughout the lesion site to re-connect the original targets; ② New neural circuits formed in the lesion site by newly generated neurons post injury, which effectively re-connect the transected stumps; ③ The combined effect of ① and ②. The numerous studies have confirmed that neural circuits rebuilt across the injury site by newborn neurons might be the main mechanisms for functional recovery of animals from rodents to dogs. In many SCI model, especially the complete spinal cord transection model, many studies have convincingly demonstrated that the quantity and length of regenerated long descending axons, particularly like CST fibers, are too few to across the lesion site that is millimeters in length to realize motor functional recovery. Hence, it is more feasible in guiding neuronal relays formation by bio-scaffolds implantation than directing long motor axons regeneration in improving motor function of animals with complete spinal cord transection. However, some other issues such as promoting more neuronal relays formation, debugging wrong connections, and maintaining adequate neural circuits for functional recovery are urgent problems to be addressed.
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.