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.
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.
Objective To explore an experimental method of transfecting the marrow stromal stem cells (MSCs) with the reconstructed PGL3-t ransforming growth factor-β1 (TGF-β1) gene and to evaluate the feasibility of selfinduction of MSCs to the chondrocytes in vitro so as to provide a scientific and experimental basis for a further “gene enhanced tissue engineering” research. Methods The rabbit MSCs was transfected with the reconstructed PGL3-TGF-β1gene by the Liposo mesMethod, the growth of the cells were observed, and the growth curve was drawn. The living activity of the transfected cells in the experimental group was evalua ted by MTT, and the result was significantly different when compared with that in the control group. By the immunohistochemistry method (SABC), the antigens of TGF-β1 and collagen Ⅱ were examined at 2 and 7 days of the cell culture afte r transfe ction with PGL3-TGF-β1gene. The pictures of the immunohistochemistry slice were analyzed with the analysis instrument, and the statistical analysis was perfor med with the software of the SPSS 11.0, compared with the control group and the blank group. Results Transfection of the cultured rabbit MSCs in vitro with the reconstructed PGL3-TGF-β1gene by the Liposomes Method achie ved a success, with a detection of the Luceraferase activity. The result was significantly different from that in the control group (Plt;0.01). Tested by MTT, the living acti vity of the transfected cells was proved to be significantly decreased (Plt;0.01 vs. the control group). By the immunohistochemistry method (SABC) to study TGF-β1 positive particles were detected in the experimental group，but there were no positive particles in the control and the blank groups. There was a significant difference between the two groups of the experiment and the control group based on the analysis of the ttest (Plt;0.01). By the immunohistochemistry me thod (SABC) to study collagen Ⅱ, there were more positive particles in the transfected cells in t he experimental group than in the control and the blank groups, and there was a significant difference between the experimental group and the two other groups based on the t-test (Plt;0.01). Conclusion Transfection of the rabbit MSCs with the reconstructed PGL3-TGF-β1 gene by the Liposomes Method is successful. There may be some damage to the cells when transfection is performed. The transfecte d BMS cells with PGL3-TGF-β1 gene can express and excrete TGF-β1when cultured in vitro. The transfected MSCs that secret TGF-β1 can be self-induced into the chondrocytes after being infected for 7 days when cultured in vitro.
ObjectiveTo explore the clinical application and effectiveness of a personalized tissue engineered cartilage with seed cells derived from ear or nasal septal cartilage and poly-glycolic acid (PGA)/poly-lactic acid (PLA) as scaffold in patients with nasal reconstruction. MethodsBetween March 2014 and October 2015, 4 cases of acquired nasal defects and 1 case of congenital nasal deformity were admitted. The patient with congenital nasal deformity was a 4-year-old boy, and the source of seed cells was nasal septal cartilage. The other 4 patients were 3 males and 1 female, aged 24-33 years, with an average of 28.5 years. They all had multiple nasal subunit defects caused by trauma and the source of seed cells was auricular cartilage. The tissue engineered cartilage framework was constructed in the shape of normal human nasal alar cartilage and L-shaped silicone prosthesis with seed cells from cartilage and PGA-PLA compound biodegradable scaffold. The boy underwent nasal deformity correction and silicone prosthesis implantation in the first stage, and the prosthesis was removed and implanted with tissue engineered cartilage in the second stage; the remaining 4 adult patients all used expanded forehead flaps for nasal reconstruction. All 5 patients underwent 1-4 nasal revisions. The implanted tissue engineered cartilage was observed during the operation and taken from 2 patients for histological examination.ResultsAll the incisions healed by first intention after the tissue engineered cartilage implantation, and the expanded forehead flaps survived. Postoperative low fever occurred in 3 patients. No complications such as infection, obvious immune rejection response, and tissue engineered cartilage protrusion were found in all patients. All patients were followed up 9-74 months (mean, 54.8 months). During follow-up, the patients had no obvious discomfort in the nose and the ventilation function were good. All patients were satisfied with the nasal contour. Early-stage histological examination showed the typical cartilage characteristics in 1 patient after the implantation of tissue engineered cartilage. Late-stage histological examination in 1 patient of tissue engineered cartilage showed the characteristics of fibrous connective tissue; and the other showed there was remaining cartilage.ConclusionThe safety of tissue engineered cartilage constructed in vitro for reconstruction is preliminarily confirmed, but the effectiveness still needs further verification.
Objective To explore the effect of tissue engineered cartilage reconstructed by using sodium alginate hydrogel and SIS complex as scaffold material and chondrocyte as seed cell on the repair of full-thickness articular cartilage defects. Methods SIS was prepared by custom-made machine and detergent-enzyme treatment. Full-thickness articularcartilage of loading surface of the humeral head and the femoral condyle obtained from 8 New Zealand white rabbits (2-3weeks old) was used to culture chondrocytes in vitro. Rabbit chondrocytes at passage 4 cultured by conventional multipl ication method were diluted by sodium alginate to (5-7) × 107 cells/mL, and then were coated on SIS to prepare chondrocyte-sodium alginate hydrogel-SIS complex. Forty 6-month-old clean grade New Zealand white rabbits weighing 3.0-3.5 kg were randomized into two groups according to different operative methods (n=20 rabbits per group), and full-thickness cartilage defect model of the unilateral knee joint (right or left) was establ ished in every rabbit. In experimental group, the complex was implanted into the defect layer by layer to construct tissue engineered cartilage, and SIS membrane was coated on the surface to fill the defect completely. While in control group, the cartilage defect was filled by sodium alginate hydrogel and was sutured after being coated with SIS membrane without seeding of chondrocyte. General condition of the rabbits after operation was observed. The rabbits in two groups were killed 1, 3, 5, 7, and 9 months after operation, and underwent gross and histology observation. Results Eight rabbits were excluded due to anesthesia death, wound infection and diarrhea death. Sixteen rabbits per group were included in the experiment, and 3, 3, 3, 3, and 4 rabbits from each group were randomly selected and killed 1, 3, 5, 7, and 9 months after operation, respectively. Gross observation and histology Masson trichrome staining: in the experimental group, SIS on the surface of the implant was fused with the host tissue, and the inferface between them disappeared 1 month after operation; part of the implant was chondrified and the interface between the implant and the host tissue was fused 3 months after operation; the implant turned into fibrocartilage 5 months after operation; fiber arrangement of the cartilage in theimplant was close to that of the host tissue 7 months after operation; cartilage fiber in the implant arranged disorderly andactive cell metabol ism and prol iferation were evident 9 months after operation. While in the control group, no repair of thedefect was observed 9 months after operation. No obvious repair was evident in the defects of the control group within 9months after operation. Histomorphometric evaluation demonstrated that the staining intensity per unit area of the reparative tissue in the defect of the experimental group was significant higher than that of the control group at each time point (P lt; 0.05), the chondrification in the experimental group was increased gradually within 3, 5, and 7 months after operation (P lt; 0.05), and it was decreased 9 months after operation comparing with the value at 7 months after operation (P lt; 0.05). Conclusion Constructed by chondrocyte-sodium alginate hydrogel-SIS in complex with surficial suturing of SIS membrane, the tissue engineered cartilage can in-situ repair cartilage defect, promote the regeneration of cartilage tissue, and is in l ine with physiological repair process of articular cartilage.
Objective
To explore heterotopic chondrogenesis of canine myoblasts induced by cartilage-derived morphogenetic protein 2 (CDMP-2) and transforming growth factor β1 (TGF-β1) which were seeded on poly (lactide-co-glycolide) (PLGA) scaffolds after implantation in a subcutaneous pocket of nude mice.
Methods
Myoblasts from rectus femoris of 1-year-old Beagle were seeded on PLGA scaffolds and cultured in medium containing CDMP-2 and TGF-β1 for 2 weeks in vitro. Then induced myoblasts-PLGA scaffold, uninduced myoblasts-PLGA scaffold, CDMP-2 and TGF-β1-PLGA scaffold, and simple PLGA scaffold were implanted into 4 zygomorphic back subcutaneous pockets of 24 nude mice in groups A, B, C, and D, respectively. At 8 and 12 weeks, the samples were harvested for general observation, HE staining and toluidine blue staining, immunohistochemical staining for collagen type I and collagen type II; the mRNA expressions of collagen type I, collagen type II, Aggrecan, and Sox9 were determined by RT-PCR, the glycosaminoglycans (GAG) content by Alician blue staining, and the compressive elastic modulus by biomechanics.
Results
In group A, cartilaginoid tissue was milky white with smooth surface and slight elasticity at 8 weeks, and had similar appearance and elasticity to normal cartilage tissue at 12 weeks. In group B, few residual tissue remained at 8 weeks, and was completely degraded at 12 weeks. In groups C and D, the implants disappeared at 8 weeks. HE staining showed that mature cartilage lacuna formed of group A at 8 and 12 weeks; no cartilage lacuna formed in group B at 8 weeks. Toluidine blue staining confirmed that new cartilage cells were oval and arranged in line, with lacuna and blue-staining positive cytoplasm and extracellular matrix in group A at 8 and 12 weeks; no blue metachromatic extracellular matrix was seen in group B at 8 weeks. Collagen type I and collagen type II expressed positively in group A, did not expressed in group B by immunohistochemical staining. At 8 weeks, the mRNA expressions of collagen type I, collagen type II, Aggrecan, and Sox9 were detected by RT-PCR in group A at 8 and 12 weeks, but negative results were shown in group B. The compressive elastic modulus and GAG content of group A were (90.79 ± 1.78) MPa and (10.20 ± 1.07) μg/mL respectively at 12 weeks, showing significant differences when compared with normal meniscus (P lt; 0.05).
Conclusion
Induced myoblasts-PLGA scaffolds can stably express chondrogenic phenotype in a heterotopic model of cartilage transplantation and represent a suitable tool for tissue engineering of menisci.
Objective To introduce the application of polymer material, chitosan, in the cartilage tissue engineering. Methods The recent original articleson the application of chitosan in cartilage tissue engineering were extensivelyreviewed. The biocompatibility and biodegradation characters of chitosan and its application were analysed.Results Chitosan has a high degree of biocompatibility and a favorable chondrogenic characteristic. It can support the maintenance of the phenotypic morphology of chondrocytes besides being used as a scaffold for cell growth. Conclusion The perspect of the application of chitosan in cartilage tissue engineering is hopeful.
ObjectiveTo investigate the effect of three-dimensional cultivation with dynamic compressive stimulation on promotion of cartilage growth in vitro, by constructing tissue engineered cartilage with three-dimensional porous articular cartilage extracellular matrix (ECM) scaffolds laden with rabbit chondrocytes and performing mechanical stimulation by compressive stress in bioreactor.
MethodsChondrocytes of healthy adult New Zealand rabbits were isolated, and passage 2 chondrocytes were seeded onto three-dimensional porous articular cartilage ECM scaffolds for 5 days pre-cultivation, and then were divided into 2 groups:Group A continued static culture as control; group B (dynamic culture condition) underwent dynamic compressive strain stimulation (compressive strain of 15%, frequence of 1 Hz) in a bioreactor. Cell viability and distribution in scaffolds were observed; the glycosaminoglycan (GAG) content, collagen content, and total DNA content were measured after 3 weeks of culturing; and elastic modulus was evaluated by mechanical test.
ResultsLaser scanning confocal microscopy indicated that cells grew well and evenly distributed in the scaffold of group B, while poor cells growth and loss of staining in the central region of the scaffolds were observed in group A. Scanning electron microscopy showed that chondrocytes possessed good adhesion, proliferation, and growth on the scaffolds of group B; while the number of chondrocytes was significantly reduced, and cells scattered in group A. Biochemical composition analysis showed that collagen, GAG, and DNA contents of cell-scaffold constructs were (675.85±27.93) μg/mg, (621.72±26.75) μg/mg, and (16.98±3.23) μg/sample in group B, and were (438.72±6.35) μg/mg, (301.63±30.51) μg/mg, and (10.18±4.39) μg/sample in group A respectively, which were significantly higher in group B than in group A (t=18.512, P=0.000;t=17.640, P=0.000;t=2.790, P=0.024). Mechanical testing indicated that the elastic modulus of group B[(0.67±0.09) MPa] was significantly higher than that of group A[(0.49±0.16) MPa] and cell-free scaffolds[(0.43±0.12) MPa] (P < 0.05).
ConclusionMimetic compressive stress with three-dimensional dynamic conditions created in the bioreactor is superior to the ordinary static three-dimensional cultivation, it can provide the optimal environment for chondrocytes on the ECM scaffolds, which may be a good way to construct tissue engineered cartilage in vitro.
【Abstract】 Objective To develop a novel cartilage acellular matrix (CACM) scaffold and to investigate its performance for cartilage tissue engineering. Methods Human cartilage microfilaments about 100 nm-5 μm were prepared after pulverization and gradient centrifugation and made into 3% suspension after acellularization treatment. After placing the suspension into moulds, 3-D porous CACM scaffolds were fabricated using a simple freeze-drying method. The scaffolds were cross-l inked by exposure to ultraviolet radiation and immersion in a carbodiimide solution 1-ethyl-3-(3-dimethylaminopropyl) carbodiimide hydrochloride and N-hydroxysucinimide. The scaffolds were investigated by histological staining, SEM observation and porosity measurement, water absorption rate analysis. MTT test was also done to assess cytotoxicity of the scaffolds. After induced by conditioned medium including TGF-β1, canine BMSCs were seeded into the scaffold. Cell prol iferation and differentiation were analyzed using inverted microscope and SEM. Results The histological staining showed that there are no chondrocytefragments in the scaffolds and that toluidine blue, safranin O and anti-collagen II immunohistochemistry staining werepositive. The novel 3-D porous CACM scaffold had good pore interconnectivity with pore diameter (155 ± 34) μm, 91.3% ± 2.0% porosity and 2 451% ± 155% water absorption rate. The intrinsic cytotoxicity assessment of novel scaffolds using MTT test showed that the scaffolds had no cytotoxic effect on BMSCs. Inverted microscope showed that most of the cells attached to the scaffold. SEM micrographs indicated that cells covered the scaffolds uniformly and majority of the cells showed the round or ell iptic morphology with much matrix secretion. Conclusion The 3-D porous CACM scaffold reserved most of extracellular matrix after thoroughly decellularization, has good pore diameter and porosity, non-toxicity and good biocompatibil ity, which make it a suitable candidate as an alternative cell-carrier for cartilage tissue engineering.
Objective To study the influence of different mechanical environments on repair cartilage defect with marrow mesenchymal stem cells as seed cells. Methods The rabbit marrow mesenchymal stem cells were isolated and cultured. The cartilage defects were repaired by autologous tissue engineered cartilage with the marrow mesenchymal stem cells as seed cells. Fifteen rabbits with cartilage defect were divided into 3 groups: dislocation group with cell-free scaffold(controlgroup), dislocation group with cartilaginous construct and normal mechanical environment group with cartilaginous construct. The repaired tissue was harvested and examined 6 weeks postoperatively. Results The repair tissue in normal mechanical environment group with cartilaginous construct showed cartilage-like tissue in superficial layer and subchondral bone tissue in deep layer 6 weeks postoperatively. The defect was filled with bone tissue in dislocation group with cartilaginous construct 6 weeks postoperatively. The surrounding normal cartilage tissue showed vascular invasion from subchondral area and the concomitant thinningof the normal cartilage layer. The cartilaginous construct left in the femoral trochlea groove formed hyaline cartilage-like tissue. The defect was repaired byfibrous tissue in control group. Conclusion The repaired tissue by tissue engineered cartilage with marrow mesenchymal stem cells as seed cells showed the best result in normal mechanical environment group, which indicates that it will be essential for the formation and maintenance of tissue engineered cartilage to keep the normal mechanical stress stimulus.
