Objective To evaluate the feasibility and the value of the layered cylindric collagenhydroxyapatite composite as a scaffold for the cartilage tissue engineering after an observation of how it absorbs the chondrocytes and affe cts the cell behaviors. Methods The chondrocytes were isolated and multiplied in vitro, and then the chondrocytes were seeded onto the porous collagen／h ydro xyapatite composite scaffold and were cultured in a three-dimensional environme n t for 3 weeks. The effects of the composite scaffold on the cell adhesivity, proliferation, morphological changes, and synthesis of the extracellular matrix were observed by the phase-contrast microscopy, histology, scanning electron micros copy, and immunohistochemistry. Results The pore diameter of the upper layer of the collagen-hydroxyapatite composite scaffold was about 147 μm. and the porosity was 89%; the pore diameter of the bottom layer was about 85 μm and the porosity was 85%. The layered cylindric collagenhydroxyapatite composite scaffold had good hydrophilia. The chondrocytes that adhered to the surface of the scaffold, proliferated and migrated into the scaffold after 24 hours. The chondrocytesattached to the wall of the microholes of the scaffold maintained a rounded morphology and could secrete the extracellular matrix on the porous scaffold. Conclusion The layered cylindric collagenhydroxyapatite composite scaffold has a good cellular compatibility, and it is ber in the mechanical property than the pure collagen. It will be an ideal scaffold for the cartilage tissue enginee ring.
Objective To study the outcomes of nerve defect repair with the tissue engineered nerve, which is composed of the complex of SCs, 30% ECM gel, bFGF-PLGA sustained release microspheres, PLGA microfilaments and permeable poly (D, L-lacitic acid) (PDLLA) catheters. Methods SCs were cultured and purified from the sciatic nerves of 1-day-old neonatal SD rats. The 1st passage cells were compounded with bFGF-PLGA sustained release microspheres andECM gel, and then were injected into permeable PDLLA catheters with PLGA microfilaments inside. In this way, the tissueengineered nerve was constructed. Sixty SD rats were included. The model of 15-mm sciatic nerve defects was made, and then the rats were randomly divided into 5 groups, with 12 rats in each. In group A, autograft was adopted. In group B, the blank PDLLA catheters with PBS inside were used. In group C, PDLLA catheters, with PLGA microfilaments and 30% ECM gel inside, were used. In group D, PDLLA catheters, with PLGA microfilaments, SCs and 30% ECM gel inside, were used. In group E, the tissue engineered nerve was appl ied. After the operation, observation was made for general conditions of the rats. The sciatic function index (SFI) analysis was performed at 12, 16, 20 and 24 weeks after the operation, respectively. Eelectrophysiological detection and histological observation were performed at 12 and 24 weeks after the operation, respectively. Results All rats survived to the end of the experiment. At 12 and 16 weeks after the operation, group E was significantly different from group B in SFI (P lt; 0.05). At 20 and 24 weeks after the operation, group E was significantly different from groups B and C in SFI (P lt; 0.05). At 12 weeks after the operation, electrophysiological detection showed nerve conduct velocity (NCV) of group E was bigger than that of groups B and C (P lt; 0.05), and compound ampl itude (AMP) as well as action potential area (AREA） of group E were bigger than those of groups B, C and D (P lt; 0.05). At 24 weeks after the operation, NCV, AMP and AREA of group E were bigger than those of groups B and C (Plt; 0.05). At 12 weeks after the operation, histological observation showed the area of regenerated nerves and the number of myel inated fibers in group E were significantly differents from those in groups A, B and C (Plt; 0.05). The density and diameter of myel inated fibers in group E were smaller than those in group A (Plt; 0.05), but bigger than those in groups B, C and D (P lt; 0.05). At 24 weeks after the operation, the area of regenerative nerves in group E is bigger than those in group B (P lt; 0.05); the number of myel inated fibers in group E was significantly different from those in groups A, B, C (P lt; 0.05); and the density and diameter of myel inated fibers in group E were bigger than those in groups B and C (Plt; 0.05). Conclusion The tissue engineered nerve with the complex of SCs, ECM gel, bFGF-PLGA sustained release microspheres, PLGA microfilaments and permeables PDLLA catheters promote nerve regeneration and has similar effect to autograft in repair of nerve defects.
Objective To observe effects of the direct impaction onthe cell survival and the bone formation of the tissue engineered bone modified by the adenovirus mediated human bone morphogenetic protein 2 (Adv-hBMP2) gene and to verify the feasibility of the impacted grafting with it. Methods The marrow stromal cells (MSCs) were separated from the canine bone marrow and were cultured. MSCs were transfected with the Adv-hBMP2 gene and combined with the freeze-dried cancellous bone (FDB) to form the tissue engineered bone. Four days after the combination, the tissue engineered bone was impacted in a simulated impactor in vitro and implanted in the mouse. The cell survivals were evaluated with SEM 1 and 4 days after the combination, immediately after the impaction, and 1 and 4 days after the impaction, respectively. The bone formation and the allograft absorption were histologically evaluated respectively. Results There were multiple layers of the cells and much collagen on FDB before the impaction. Immediately after the impaction, most of the cells on the direct contact area disappearedand there was much debris on the section. Some of the cells died and separatedfrom the surface of FDB at 1 day, the number of the cells decreased but the collagen increased on the surface at 4 days. Histologically, only the fibrous tissue was found in FDB without the cells, the bone formation on FDB was even in distribution and mass in appearance before the impaction, but declined and was mainly on the periphery after the impaction in the AdvhBMP2 modified tissue-engineered bone. Conclusion The simulated impaction can decrease the cells survival and the bone formation of the AdvhBMP-2 modified tissue-engineered bone. The survival cells still function well.It is feasible to use the tissue engineered bone in the impaction graft.
ObjectiveTo investigate the early effects of acellular xenogeneic nerve combined with adipose-derived stem cells (ADSCs) and platelet rich plasma (PRP) in repairing facial nerve injury in rabbits.MethodsThe bilateral sciatic nerves of 15 3-month-old male Sprague-Dawley rats were harvested and decellularized as xenografts. The allogeneic ADSCs were extracted from the neck and back fat pad of healthy adult New Zealand rabbits with a method of digestion by collagenase type Ⅰ and the autologous PRP was prepared by two step centrifugation. The 3rd generation ADSCs with good growth were labelled with CM-Dil living cell stain, and the labelling and fluorescence attenuation of the cells were observed by fluorescence microscope. Another 32 New Zealand rabbits were randomly divided into 4 groups and established the left facial nerve defect in length of 1 cm (n=8). The nerve defects of groups A, B, C, and D were repaired with CM-Dil-ADSCs composite xenogeneic nerve+autologous PRP, CM-Dil-ADSCs composite xenogeneic nerve, xenogeneic nerve, and autologous nerve, respectively. At 1 and 8 weeks after operation, the angle between the upper lip and the median line of the face (angle θ) was measured. At 4 and 8 weeks after operation, the nerve conduction velocity was recorded by electrophysiological examination. At 8 weeks after operation, the CM-Dil-ADSCs at the distal and proximal ends of regenerative nerve graft segment in groups A and B were observed by fluorescence microscopy; after toluidine blue staining, the number of myelinated nerve fibers in regenerated nerve was calculated; the structure of regenerated nerve fibers was observed by transmission electron microscope.ResultsADSCs labelled by CM-Dil showed that the labelling rate of cells was more than 90% under fluorescence microscope, and the labelled cells proliferated well, and the fluorescence attenuated slightly after passage. All the animals survived after operation, the incision healed well and no infection occurred. At 1 week after operation, all the animals in each group had different degrees of dysfunction. The angle θ of the left side in groups A, B, C, and D were (53.4±2.5), (54.0±2.6), (53.7±2.4), and (53.0±2.1)°, respectively; showing significant differences when compared with the healthy sides (P<0.05). At 8 weeks after operation, the angle θ of the left side in groups A, B, C, and D were (61.9±4.7), (56.8±4.2), (54.6±3.8), and (63.8±5.8)°, respectively; showing significant differences when compared with the healthy sides and with the values at 1 week (P<0.05). Gross observation showed that the integrity and continuity of regenerated nerve in 4 groups were good, and no neuroma and obvious enlargement was found. At 4 and 8 weeks after operation, the electrophysiological examination results showed that the nerve conduction velocity was significantly faster in groups A and D than in groups B and C (P<0.05), and in group B than in group C (P<0.05); no significant difference was found between groups A and D (P>0.05). At 8 weeks after operation, the fluorescence microscopy observation showed a large number of CM-Dil-ADSCs passing through the distal and proximal transplants in group A, and relatively few cells passing in group B. Toluidine blue staining showed that the density of myelinated nerve fibers in groups A and D were significantly higher than those in groups B and C (P<0.05), and in group B than in group C (P<0.05); no significant difference was found between groups A and D (P>0.05). Transmission electron microscope observation showed that the myelinated nerve sheath in group D was large in diameter and thickness in wall. The morphology of myelin sheath in group A was irregular and smaller than that in group D, and there was no significant difference between groups B and C.ConclusionADSCs can survive as a seed cell in vivo, and can be differentiated into Schwann-like cells under PRP induction. It can achieve better results when combined with acellular xenogeneic nerve to repair peripheral nerve injury in rabbits.
OBJECTIVE: To explore a new method of preparing the composite of DL-polylactic acid (PDLLA), hydroxyapatite(HA), decalcium bone matrix (DBM), and to observe the degradation characteristics of PDLLA/HA/DBM in vitro. METHODS: An emulsion blend method was developed to prepare the composite of PDLLA/HA/DBM based on the weight rate of PDLLA:HA:DBM = 1.5-2:1-1.5:1. The characteristics of the particles was observed by scanning electron microscope. In vitro, PDLLA/HA/DBM and PDLLA were put into PBS(pH7.4) respectively; the pH value, weight and biomechanics of them were determined during the degradation. RESULTS: Without heating, the emulsion blend method could be developed to prepare PDLLA/HA/DBM. Scanning electron microscope showed that the gap diameter in the compound material was 100 to 400 microns, and the porosity was 71.3%; During degradation, the pH value of PDLLA decreased little within 2 weeks, then decreased obviously and decreased to 4.0 at the end of the 4th week; while the pH value of PDLLA/HA/DBM kept quite steady and was 6.4 at the end of the 12th week. The weight of PDLLA decreased little within 4 weeks, then decreased obviously and remained 50% of its prime weight at the end of the 12th week; while the weight of PDLLA/HA/DBM decreased little within 5 weeks, then decreased obviously and remained 60% of the prime at the end of the 12th week. The prime biomechanical strength was 1.33 MPa in PDLLA and 1.71 MPa in PDLLA/HA/DBM. There was significant difference between them (P lt; 0.05). The strength of PDLLA decreased little within 3 weeks, then decrease obviously and was 0.11 MPa at the end of the 12th week; the strength of PDLLA/HA/DBM decreased little within 4 weeks, then decrease obviously and was 0.21 MPa at the end of the 12th week. CONCLUSION: The emulsion blend method is a new method to prepare bone repair materials. As a new bone repair material, PDLLA/HA/DBM is suitable for bone tissue engineering for its good characteristics of porosity and degeneration.
ObjectiveTo explore the feasibility of three-dimensional (3D) bioprinted adipose-derived stem cells (ADSCs) combined with gelatin methacryloyl (GelMA) to construct tissue engineered cartilage.MethodsAdipose tissue voluntarily donated by liposuction patients was collected to isolate and culture human ADSCs (hADSCs). The third generation cells were mixed with GelMA hydrogel and photoinitiator to make biological ink. The hADSCs-GelMA composite scaffold was prepared by 3D bioprinting technology, and it was observed in general, and observed by scanning electron microscope after cultured for 1 day and chondrogenic induction culture for 14 days. After cultured for 1, 4, and 7 days, the composite scaffolds were taken for live/dead cell staining to observe cell survival rate; and cell counting kit 8 (CCK-8) method was used to detect cell proliferation. The composite scaffold samples cultured in cartilage induction for 14 days were taken as the experimental group, and the composite scaffolds cultured in complete medium for 14 days were used as the control group. Real-time fluorescent quantitative PCR (qRT-PCR) was performed to detect cartilage formation. The relative expression levels of the mRNA of cartilage matrix gene [(aggrecan, ACAN)], chondrogenic regulatory factor (SOX9), cartilage-specific gene [collagen type Ⅱ A1 (COLⅡA1)], and cartilage hypertrophy marker gene [collagen type ⅩA1 (COLⅩA1)] were detected. The 3D bioprinted hADSCs-GelMA composite scaffold (experimental group) and the blank GelMA hydrogel scaffold without cells (control group) cultured for 14 days of chondrogenesis were implanted into the subcutaneous pockets of the back of nude mice respectively, and the materials were taken after 4 weeks, and gross observation, Safranin O staining, Alcian blue staining, and collagen type Ⅱ immunohistochemical staining were performed to observe the cartilage formation in the composite scaffold.ResultsMacroscope and scanning electron microscope observations showed that the hADSCs-GelMA composite scaffolds had a stable and regular structure. The cell viability could be maintained at 80%-90% at 1, 4, and 7 days after printing, and the differences between different time points were significant (P<0.05). The results of CCK-8 experiment showed that the cells in the scaffold showed continuous proliferation after printing. After 14 days of chondrogenic induction and culture on the composite scaffold, the expressions of ACAN, SOX9, and COLⅡA1 were significantly up-regulated (P<0.05), the expression of COLⅩA1 was significantly down-regulated (P<0.05). The scaffold was taken out at 4 weeks after implantation. The structure of the scaffold was complete and clear. Histological and immunohistochemical results showed that cartilage matrix and collagen type Ⅱ were deposited, and there was cartilage lacuna formation, which confirmed the formation of cartilage tissue.ConclusionThe 3D bioprinted hADSCs-GelMA composite scaffold has a stable 3D structure and high cell viability, and can be induced differentiation into cartilage tissue, which can be used to construct tissue engineered cartilage in vivo and in vitro.
ObjectiveTo investigate the bone regeneration potential of cell-tissue engineered bone constructed by human bone marrow mesenchymal stem cells (hBMSCs) expressing the transduced human bone morphogenetic protein 2 (hBMP-2) gene stably.
MethodsThe full-length hBMP-2 gene was cloned from human muscle tissues by RT-PCR and connected into a vector to consturct a eukaryotic expression system. And then the gene expression system was transduced to hBMSCs with lipidosome. hBMSCs were transfected by hBMP-2 gene (experimental group) and by empty plasmid (negative control group), untransfected hBMP-2 served as blank control group. RT-PCR, dot-ELISA, immunohistochemical analysis and ALP activity were performed to compare and evaluate the situation of hBMP-2 expression and secretion after transfection. hBMSCs transfected by hBMP-2 gene were seeded on hydroxyapatite (HA) and incubated for 4 days to construct the hBMP-2 gene modified tissue engineered bone, and then the tissue engineered bone was observed by the inverted phase contrast microscope and scanning electron microscope. Then the hBMP-2 gene modified tissue engineered bone (group A, n=3), empty plasmid transfected hBMSCs seeded on HA (group B, n=3), hBMSCs suspension transfected by hBMP-2 gene (group C, n=3), and hBMP-2 plasmids and lipidosome (group D, n=3) were implanted into bilateral back muscles of nude mice. The osteogenic activity was detected by HE staining and alcian blue staining after 4 weeks.
ResultsAt 48 hours and 3 weeks after transfection, RT-PCR and dot-ELISA results indicated that the transfected hBMSCs could express and secrete active and exogenous hBMP-2 stably. The immunohistochemical staining was positive, and the ALP activity in the transfected hBMSCs was significantly higher than that in two control groups (P < 0.05). The transfected hBMSCs had a good attaching and growing on the three-demension suface of HA under inverted phase contrast microscope and scanning electron microscope. In vivo study indicated that a lot of new bone formation was obviously found at 4 out of 6 sides of back muscles in group A. Some new bone formation at both sides of back muscles was observed in 1 of 3 mice in group B. No new bone formation was found in group C. A few new bone formation was observed at one side of back muscles in group D.
ConclusionThe tissue engineered bone constructed by hBMP-2 gene modified hBMSCs and HA is able to express and secrete active hBMP2 stably and can promote new bone formation effectively in muscles of nude mice.
Objective To observe the clinical effect of the human tissue engineered activeskin (ActivSkin) with full thickness on the donor site of the split thickness skin graft. Methods Nine patients with 18 wounds of the donor sites, and every p atient had 2 wounds. The wounds of each patient were randomly assigned to the therapy group and the control group. Autocontrol observation was performed. Nine donor sites of the split thickness skin graft were repaired with ActivSkin in the therapy group. Nine donor sites of the split thickness skin graft were repaired with the vash oil gauze in the control group. The wound pain, the time to complete closure, and the ratio of the complete healing in the ActivSkin therapy gro up was measured and compared with those in the control group. The donor sites of the split thickness skin graft were assessed at 180 days of the follow-up visit . Results The wound pain was obviously reduced after the harvest ing of the skin grafts in the therapy group. The time to complete closure on the donor sites of the split thickness skin graft was significantly shorter in the ActivSkin therap y group than in the control group (9.67±2.92 d vs.16.56±2.96 d, Plt;0.05 ). Both the ratios of the complete healing in the ActivSkin therapy group and the control group were 100%（Pgt;0.05）. The subsequent results showed that neit her the blister nor the residual wound occurred with an alleviated scar after the Ac tivSkin treatment. Conclusion ActivSkin can promote wound closure, prevent blister and residual wound, and alleviate scarring on the donor sites of the splitthickness skin graft after the ActivSkin treatment.
Objective
To review the decellularized methods for obtaining extracellular matrix (ECM) and the applications of decellularized ECM scaffold in tissue engineering.
Methods
Recent and related literature was extensively and comprehensively reviewed. The decellularized methods were summarized and classified. The effects of different sterilization methods on decellularized scaffolds were analyzed; the evaluation criterion of extent of decellularization was put forward; and the application of decellularized ECM scaffold in different tissues and organs engineering field was summarized.
Results
The decellularized methods mainly include physical methods, chemical methods, and biological methods, and different decellularization methods have different effects on the extent of cell removal and ECM composition and structure. Therefore, the best decellularization method will be chosen according to the characteristics of the tissues and decellularization methods to achieve the ideal result.
Conclusion
It is very important to choose the appropriate decellularized method for preparing the biological materials desired by tissue engineering. The biological scaffolds prepared by decellularized methods will play an important role in tissue engineering and regenerative medicine.
Objective To study the differentiation of the human osteoblasts during the construction of the tissue engineered periosteum with the human acellular amniotic membrane(HAAM).Methods To construct the tissue engineered periosteum (n=60) with HAAM, the human fetal osteoblasts were used. The fetal osteoblasts were cultured for 2, 4, 6, 8, and10 days, and then their total RNA was extracted, which were reversely transcripted to cDNA. The realtime PCR analysis was used to reveal Cbfal and Osterix, and the cycle threshold (Ct) was also measured. The simplycultured osteoblasts were used as the control group (n=20).Results The expression of Cbfa1 was higher in the experimental group on the 2nd day when compared with that on the 4th, 6th, and 8th day(P＜0.05). The same result existed on the 10th day when compared with that on the 4th and 8th day. The expression of Osterix increased and was highest on the 8th day when compared with the other results(P＜0.05). Both of the 2 gene expressions were decreased in the control group when compared with those in the experimental group, but with no significant difference(P＞0.05). Conclusion Cbfa1 and Osterix can be normally expressed by the osteoblasts after their integration with HAAM. As a scaffold, HAAM can be used to keep the osteoblast phenotype and differentiation with an osteoconductive ability. Such a cell-scaffold complex may provide a basis for the osteogenesis.
