ObjectiveTo solve the fixation problem between ligament grafts and host bones in ligament reconstruction surgery by using ligament-bone composite scaffolds to repair the ligaments, to explore the fabrication method for ligament-bone composite scaffolds based on three-dimensional (3-D) printing technique, and to investigate their mechanical and biological properties in animal experiments. MethodsThe model of bone scaffolds was designed using CAD software, and the corresponding negative mould was created by boolean operation. 3-D printing techinique was employed to fabricate resin mold. Ceramic bone scaffolds were obtained by casting the ceramic slurry in the resin mould and sintering the dried ceramics-resin composites. Ligament scaffolds were obtained by weaving degummed silk fibers, and then assembled with bone scaffolds and bone anchors. The resultant ligament-bone composite scaffolds were implanted into 10 porcine left anterior cruciate ligament rupture models at the age of 4 months. Mechanical testing and histological examination were performed at 3 months postoperatively, and natural anterior cruciate ligaments of the right sides served as control. ResultsBiomechanical testing showed that the natural anterior cruciate ligament of control group can withstand maximum tensile force of (1 384±181) N and dynamic creep of (0.74±0.21) mm, while the regenerated ligament-bone scaffolds of experimental group can withstand maximum tensile force of (370±103) N and dynamic creep of (1.48±0.49) mm, showing significant differences (t=11.617,P=0.000; t=-2.991,P=0.020). In experimental group, histological examination showed that new bone formed in bone scaffolds. A hierarchical transition structure regenerated between ligament-bone scaffolds and the host bones, which was similar to the structural organizations of natural ligament-bone interface. ConclusionLigament-bone composite scaffolds based on 3-D printing technique facilitates the regeneration of biomimetic ligament-bone interface. It is expected to achieve physical fixation between ligament grafts and host bone.
ObjectiveTo study the hydrophilicity and the cell biocompatibility of the poly(3-hydroxybutyrate-co-3-hydroxyvalerate) (PHBV) and poly(3-hydroxybutyrate-co-3-hydroxyhexanoate) (PHBHHx) coated with a fusion protein polyhydroxyalkanoates granule binding protein (PhaP) fused with Arg-Gly-Asp (RGD) peptide (PhaP-RGD). MethodsPHBV and PHBHHx films were fabricated by solvent evaporation.Scanning electronic microscope (SEM) was used to study the morphology of the films.PhaP-RGD fusion proteins were expressed and purified by the technology of protein engineering; PHBV and PHBHHx films were immersed in the PhaP-RGD with an amount of 3.5 mg/mL protein/per sample respectively.The hydrophilicity of the surface were detected by the contact angle measurements.Septal cartilage cells obtained from human septal cartilage were cultured in vitro.The 2nd passage chondrocytes were incubated on PHBV unmodified with PhaP-RGD in group A1,PHBV modified with PhaP-RGD in group A2,PHBHHx unmodified with PhaP-RGD in group B1,PHBHHx modified with PhaP-RGD in group B2,and on the cell culture plates in group C.After cultured for 3 days,the proliferation of cells was detected by the DAPI staining; the proliferation viability of cells was detected by the MTT assay after cultured for 3 and 7 days; after cultured for 7 days,the adhesion and morphology of the cells on the surface of the biomaterial films were observed by SEM and the matrix of the cells was detected through the toluidine blue staining. ResultsSEM observation showed that PHBV and PHBHHx films had porous structures.The contact angle of the surface of the PHBV and PHBHHx films modified with PhaP-RGD fusion proteins were significantly reduced when compared with the films unmodified with PhaP-RGD fusion proteins (P<0.05).Chondrocytes of human nasal septal cartilage incubated on the films could grow in all groups.After 3 days of cultivation in vitro,the cell proliferation and viability of group B2 were the strongest among all groups (P<0.05); the cell proliferation after cultured for 7 days was significantly stronger than that after cultured for 3 days in groups A1,A2,B1,and B2 (P<0.05); and the cell proliferation was significantly stronger in groups B1 and B2 than groups A1,A2 and C,in group B2 than group B1,and in group A1 than group A2 (P<0.05).The results of toluidine blue staining showed that blue metachromasia matrixes were observed in groups A1,A2,B1,and B2; group A1 and group A2 had similar staining degree,and the staining of group B2 was deeper than that of group B1.The adhesion of cells in all groups was good through SEM observation; and the connection of cells formed and stretched into the pores of the materials. ConclusionThe biomaterial films of PHBHHx modified with PhaP-RGD fusion protein can promote its biocompatibility with chondrocytes.
ObjectiveTo evaluate the effect of tissue engineered periosteum on the repair of large diaphysis defect in rabbit radius, and the effect of deproteinized bone (DPB) as supporting scaffolds of tissue engineering periosteum. MethodsBone marrow mesenchymal stem cells (BMSCs) were cultured from 1-month-old New Zealand Rabbit and osteogenetically induced into osteoblasts. Porcine small intestinal submucosa (SIS) scaffold was produced by decellular and a series mechanical and physiochemical procedures. Then tissue engineered periosteum was constructed by combining osteogenic BMSCs and SIS, and then the adhesion of cells to scaffolds was observed by scanning electron microscope (SEM). Fresh allogeneic bone was drilled and deproteinized as DPB scaffold. Tissue engineered periosteum/DPB complex was constructed by tissue engineered periosteum and DPB. Tissue engineered periosteum was "coat-like" package the DPB, and bundled with absorbable sutures. Forty-eight New Zealand white rabbits (4-month-old) were randomly divided into 4 groups (groups A, B, C, and D, n=12). The bone defect model of 3.5 cm in length in the left radius was created. Defect was repaired with tissue engineered periosteum in group A, with DPB in group B, with tissue engineered periosteum/DPB in group C; defect was untreated in group D. At 4, 8, and 12 weeks after operation, 4 rabbits in each group were observed by X-ray. At 8 weeks after operation, 4 rabbits of each group were randomly sacrificed for histological examination. ResultsSEM observation showed that abundant seeding cells adhered to tissue engineered periosteum. At 4, 8, and 12 weeks after operation, X-ray films showed the newly formed bone was much more in groups A and C than groups B and D. The X-ray film score were significantly higher in groups A and C than in groups B and D, in group A than in group C, and in group B than in group D (P<0.05). Histological staining indicated that there was a lot of newly formed bone in the defect space in group A, with abundant newly formed vessels and medullary cavity. While in group B, the defect space filled with the DPB, the degradation of DPB was not obvious. In group C, there was a lot of newly formed bone in the defect space, island-like DPB and obvious DPB degradation were seen in newly formed bone. In group D, the defect space only replaced by some connective tissue. ConclusionTissue engineered periosteum constructed by SIS and BMSCs has the feasibility to repair the large diaphysis defect in rabbit. DPB isn't an ideal support scaffold of tissue engineering periosteum, the supporting scaffolds of tissue engineered periosteum need further exploration.
In cases where a tracheal injury exceeds half the length of the adult trachea or one-third of the length of the child trachea, it becomes difficult to perform end-to-end anastomosis after tracheal resection due to excessive tension at the anastomosis site. In such cases, tracheal replacement therapy is required. Advances in tissue engineering technology have led to the development of tissue engineering tracheal substitutes, which have promising applications. Hydrogels, which are highly hydrated and possess a good three-dimensional network structure, biocompatibility, low immunogenicity, biodegradability, and modifiability, have had wide applications in the field of tissue engineering. This article provides a review of the characteristics, advantages, disadvantages, and effects of various hydrogels commonly used in tissue engineering trachea in recent years. Additionally, the article discusses and offers prospects for the future application of hydrogels in the field of tissue engineering trachea.
Objective To investigate a method for preparing decellularized rat heart scaffold, and to detect and evaluate the decellularized scaffold. Methods The decellularized rat heart scaffold was prepared by retrograde perfusion with a combination of enzymatic and Triton X-100 detergent methods to remove the populations of resident cells, and then the decellularized scaffold was observed by gross, toluidine blue staining, HE staining, scanning electron microcope (SEM), Alcian blue staining, and immunohistochemisty staining to evaluate the structure and essential component of extracellular maxtix (ECM) in the scaffold. Results Tissue engineered scaffold based on decellularized whole heart ECM was successfully prepared, which maintained not only the gross morphology of the heart, but also the intact vascular structure and ultrastructural conformation that certified by toluidine blue staining, HE staining, and SEM analyses. Alcian blue staining and immunohistochemisty staining showed that the essential components of ECM, such as collagen type I, glycosaminoglycan, fibronectin, and Laminin were remained in decellularized whole heart matrix. Conclusion The decellularized whole heart ECM prepared by method mentioned can maintain the intact structure of rat heart and basic compositions of extracellular matrices, so it could be suitable for further studies of tissue engineered scaffolds for whole heart reconstruction.
Objective To develop a diclofenac sodium-loaded gelatin scaffold with anti-inflammatory activity and provide a new avenue for alleviating the inflammatory response and enhancing cartilage regeneration in vivo. Methods Diclofenac sodium was homogeneously mixed with gelatin to prepare a diclofenac sodium-loaded porous gelatin scaffold by freeze-drying method as the experimental group, and a pristine porous gelatin scaffold was served as a control group. The general morphology of the scaffold was observed, the pore size of the scaffold was measured by scanning electron microscopy, the porosity of the scaffold was calculated by drainage method, the loading of diclofenac sodium into the gelatin scaffold was detected by fourier transform infrared spectrometer and X-ray diffraction examinations, and the release kinetics of diclofenac sodium from gelatin scaffold was tested using an in vitro release assay. The two scaffolds were co-cultured with lipopolysaccharide-predisposed RAW264.7 in vitro, and the expressions of interleukin 1β (IL-1β) and tumor necrosis factor α (TNF-α) were detected by reverse transcription polymerase chain reaction (RT-PCR), enzyme-linked immuno sorbent assay, and Western blot, to detect the in vitro anti-inflammatory effect of the drug-loaded scaffold. Thereafter, the second generation chondrocytes of New Zealand white rabbits were inoculated on the two groups of scaffolds for in vitro culture, and the cytocompatibility of the scaffold was tested by live/dead staining and cell counting kit 8 assay, the feasibility of in vitro cartilage regeneration of the scaffold was evaluated via gross observation, HE staining, Safranin-O staining, and immunohistochemical collagen type Ⅱ staining, as well as biochemical quantitative analyses. Finally, the two groups of chondrocyte-scaffolds were implanted subcutaneously into New Zealand white rabbits, and after 4 weeks, the general observation, HE staining, safranin O staining, immunohistochemical collagen type Ⅱ staining, and biochemical quantitative analyses were performed to verify the cartilage regeneration in vivo, and the expression of inflammation-related genes CD3 and CD68 was detected by RT-PCR to comprehensively evaluate the anti-inflammatory performance of the scaffolds in vivo. Results The two scaffolds exhibited similar gross, microporous structure, pore size, and porosity, showing no significant difference (P>0.05). Diclofenac sodium was successfully loaded into gelatin scaffold. Data from in vitro anti-inflammatory assay suggested that diclofenac sodium-loaded gelatin scaffold showed alleviated gene and protein expressions of IL-1β and TNF-α when compared with gelatin scaffold (P<0.05). The evaluation of cartilage regeneration in vitro showed that the number of living cells increased significantly with the extension of culture time, and there was no significant difference between the two groups at each time point (P>0.05). White cartilage-like tissue was regenerated from the scaffolds in both groups, histological observation showed typical cartilage lacuna structure and specific cartilage extracellular matrix secretion. There was no significant difference in the content of cartilage-specific glycosaminoglycan (GAG) and collagen type Ⅱ between the two groups (P>0.05). In vivo experiments showed that the samples in the experimental group had porcelain white cartilage like morphology, histologic staining showed obvious cartilage lacuna structure and cartilage specific extracellular matrix, the contents of GAG and collagen type Ⅱ were significantly higher than those in the control group, and the protein and mRNA expressions of CD3 and CD68 were significantly lower than those in the control group, with significant differences (P<0.05). ConclusionThe diclofenac sodium-loaded gelatin scaffold presents suitable pore size, porosity, and cytocompatibility, as well as exhibited satisfactory anti-inflammatory ability, providing a reliable scheme for alleviating the inflammatory reaction of regenerated cartilage tissue after in vivo implantation and promoting cartilage regeneration in vivo.
【Abstract】 Objective To investigate the secretion of target gene and differentiation of BMSCs transfected by TGF-β1 and IGF-1 gene alone and together into chondrocytes and to provide a new method for culturing seed cells in cartilage tissue engineering. Methods The plasmids pcDNA3.1-IGF-1 and pcDNA3.1-TGF-β1 were ampl ified and extracted, then cut by enzymes, electrophoresed and analyzed its sequence. BMSCs of Wistar rats were separated and purificated by the density gradient centrifugation and adherent separation. The morphologic changes of primary and passaged cells were observed by inverted phase contrast microscope and cell surface markers were detected by immunofluorescence method. According to the transfect situation, the BMSCs were divided into 5 groups, the non-transfected group (Group A), the group transfected by empty vector (Group B), the group transfected by TGF-β1 (Group C), the group transfected by IGF-1 (Group D) and the group transfected both by TGF-β1 and IGF-1 (Group E). After being transfected, the cells were selected, then the prol iferation activity was tested by MTT and expression levels were tested by RT-PCR and Western blot. Results The result of electrophoresis showedthat sequence of two bands of the target genes, IGF-1 and TGF-β1, was identical with the sequence of GeneBank cDNA. A few adherent cells appeared after 24 hours culture, typical cluster formed on the forth or fifth days, and 80%-90% of the cells fused with each other on the ninth or tenth days. The morphology of the cells became similar after passaging. The immunofluorescence method showed that BMSCs were positive for CD29 and CD44, but negative for CD34 and CD45. A few cells died after 24 hoursof transfection, cell clone formed at 3 weeks after selection, and the cells could be passaged at the forth week, most cells became polygonal. The boundary of some cells was obscure. The cells were round and their nucleus were asymmetry with the particles which were around the nucleus obviously. The absorbency values of the cells tested by MTT at the wavelength of 490 nm were0.432 ± 0.038 in group A, 0.428 ± 0.041 in group B, 0.664 ± 0.086 in group C, 0.655 ± 0.045 in group D and 0.833 ± 0.103 in group E. The differences between groups A, B and groups C, D, E were significant (P lt; 0.01). The differences between groups A and B or between C, D and E were not significant (P gt; 0.05)。RT-PCR and Western blot was served to detect the expression of the target gene and protein. TGF-β1 was the highest in group C, 0.925 0 ± 0.022 0, 124.341 7 ± 2.982 0, followed by group E, 0.771 7 ± 0.012 0, 101.766 7 ± 1.241 0（P lt; 0.01）; The expression of IGF-1 was the highest in group E, 1.020 0 ± 0.026 0, 128.171 7 ± 9.152 0, followed by group D, 0.465 0 ± 0.042 0, 111.045 0 ± 6.248 0 （P lt; 0.01）. And the expression of collagen II was the hignest in group E, 0.980 0 ± 0.034 0, 120.355 0 ± 12.550 0, followed by group C, 0.720 0 ± 0.026 0, 72.246 7 ± 7.364 0（P lt; 0.01）. Conclusion The repairment of cartilage defects by BMSCs transfected with TGF-β1 and IGF-1 gene together hasa good prospect and important significance of cl inic appl ication in cartilage tissue engineering.
Objective To review the recent advances in the application of graphene oxide (GO) for bone tissue engineering. Methods The latest literature at home and abroad on the GO used in the bone regeneration and repair was reviewed, including general properties of GO, degradation performance, biocompatibility, and application in bone tissue engineering. Results GO has an abundance of oxygen-containing functionalities, high surface area, and good biocompatibility. In addition, it can promote stem cell adhesion, proliferation, and differentiation. Moreover, GO has many advantages in the construction of new composite scaffolds and improvement of the performance of traditional scaffolds. Conclusion GO has been a hot topic in the field of bone tissue engineering due to its excellent physical and chemical properties. And many problems still need to be solved.
ObjectiveTo investigate the formation of nanostructure on cuttlefish bone transformed hydroxyapatite (CB-HA) porous ceramics and the effects of different nanostructures on the osteoblasts adhesion, proliferation, and alkaline phosphatase (ALP) expression.MethodsThe cuttlefish bone was shaped as plate with diameter of 10 mm and thickness of 2 mm, filled with water, and divided into 4 groups. The CB-HA in groups 1-4 were mixed with different phosphorous solutions and then placed in an oven at 120℃ for 24 hours. In addition, the samples in group 4 were further sintered at 1 200℃ for 3 hours to remove nanostructure as controls. The chemical composition of CB-HA were analyzed by X-ray diffraction spectroscopy, Fourier transform infrared spectrum, and inductively coupled plasma (ICP). The physical structure was analyzed using scanning electron microscopy, specific surface tester, and porosity tester. The MC3T3-E1 cells of 4th generation were co-cultured with 4 groups of CB-HA. After 1 day, the morphology of the cells was observed under scanning electron microscopy. After 1, 3, and 7 days, the cell proliferation was analyzed by MTT assay. After 7 and 14 days, the ALP expression was measured by pNPP method.ResultsX-ray diffraction spectrum showed that the four nanostructures of CB-HA were made of hydroxyapatite. The infrared absorption spectrum showed that the infrared absorption peak of CB-HA was consistent with hydroxyapatite. ICP showed that the ratio of calcium to phosphorus of all CB-HA was 1.68-1.76, which was consistent with hydroxyapatite. Scanning electron microscopy observation showed that the nanostructure on the surface of CB-HA in groups 1-3 were large, medium, and small cluster-like structures, respectively, and CB-HA in group 4 had no obvious nanostructure. There were significant differences in the specific surface areas between groups (P<0.05). There was no significant difference in the porosity between groups (P>0.05). Compared with group 4, groups 1-3 have more pores with pore size less than 50 nm. After co-cultured with osteoblasts, scanning electron microscopy observation and MTT assay showed that the cells in groups 2 and 3 adhered and proliferated better and had more ALP expression than that in groups 1 and 4 (P<0.05).ConclusionThe size of cluster-like nanostructure on the surface of CB-HA can be controlled by adjusting the concentration of ammonium ions in the phosphorous solution, and the introduction of small-sized cluster-like nanostructure on the surface of CB-HA can significantly improve the cell adhesion, proliferation, and ALP expression of the material which might be resulted from the enlarged surface area.
ObjectiveTo study the feasibility of acellular matrix materials prepared from deer antler cartilage and its biological compatibility so as to search for a new member of the extracellular matrix family for cartilage regeneration. MethodsThe deer antler mesenchymal (M) layer tissue was harvested and treated through decellular process to prepare M layer acellular matrix; histologic observation and detection of M layer acellular matrix DNA content were carried out. The antler stem cells [antlerogenic periosteum (AP) cells] at 2nd passage were labelled by fluorescent stains and by PKH26. Subsequently, the M layer acellular matrix and the AP cells at 2nd passage were co-cultured for 7 days; then the samples were transplanted into nude mice to study the tissue compatibility of M layer acellular matrix in the living animals. ResultsHE and DAPI staining confirmed that the M layer acellular matrix did not contain nucleus; the DNA content of the M layer acellular matrix was (19.367±5.254) ng/mg, which was significantly lower than that of the normal M layer tissue [(3 805.500±519.119) ng/mg](t=12.630, P=0.000). In vitro co-culture experiments showed that AP cells could adhere to or even embedded in the M layer acellular matrix. Nude mice transplantation experiments showed that the introduced AP cells could proliferate and induce angiogenesis in the M layer acellular matrix. ConclusionThe deer antler cartilage acellular matrix is successfully prepared. The M layer acellular matrix is suitable for adhesion and proliferation of AP cells in vitro and in vivo, and it has the function of stimulating angiogenesis. This model for deer antler cartilage acellular matrix can be applied in cartilage tissue engineering in the future.