Decellularized tissue engineering scaffolds appear to have the properties of similar structure and mechanical characteristics to native tissues，good biocompatibility，suitability for cell adhesion，growth and angiogenesis induction，and non-immunogenicity. Genipin has anti-inflammatory，antithrombotic and antioxidative features which can considerably suppress vascular and endothelial inflammatory activation，increase mechanical strength of biological scaffolds，inhibit inflammatory response and decrease degradation rate of biological scaffolds. By cross-linking with decellularized matrices，Genipin can further improve corresponding performance of tissue engineering matrices，which is very helpful to promote the application of tissue engineering into clinical practice of cardiothoracic surgery. This review focuses on recent research process and possible prospects of Genipin cross-linking in tissue engineering in the field of cardiothoracic surgery.
Objective To investigate the biomechanical properties of porous bioactive bone cement (PBC) in vivo and to observe the degradation of PBC and new bone formation histologically. Methods According to the weight percentage (W/ W, %) of polymethylmethacrylate (PMMA) to bioglass to chitosan, 3 kinds of PBS powders were obtained: PBC I (50 ︰ 40 ︰ 10), PBC II (40 ︰ 50 ︰ 10), and PBC III (30 ︰ 60 ︰ 10). The bilateral femoral condylar defect model (4 mm in diameter and 10 mm in depth) was established in 32 10-month-old New Zealand white rabbits (male or female, weighing 4.0-4.5 kg), which were randomly divided into 4 groups (n=8); pure PMMA (group A), PBC I (group B), PBC II (group C), and PBC III (group D) were implanted in the bilateral femoral condylar defects, respectively. Gross observation were done after operation. X-ray films were taken after 1 week. At 3 and 6 months after operation, the bone cement specimens were harvested for mechanical test and histological examination. Four kinds of unplanted cement were also used for biomechanical test as control. Results All rabbits survived to the end of experiment. The X-ray films revealed the location of bone cement was at the right position after 1 week. Before implantation, at 3 months and 6 months after operation, the compressive strength and elastic modulus of groups C and D decreased significantly when compared with those of group A (P lt; 0.05), but no significant difference was found between groups C and D (P gt; 0.05); the compressive strength at each time point and elastic modulus at 3 and 6 months of group B decreased significantly when compared with those of group A (P lt; 0.05). Before implantation and at 3 months after operation, the compressive strength and elastic modulus of groups C and D decreased significantly when compared with those of group B (P lt; 0.05); at 6 months after operation, the compressive strength of group C and the elastic modulus of group D were significantly lower than those of group B (P lt; 0.05). The compressive strength and elastic modulus at 3 and 6 months after operation significantly decreased when compared with those before implantation in groups B, C, and D (P lt; 0.05), but no significant difference was found in group A (P lt; 0.05). At 3 months after operation, histological observation showed that a fibrous tissue layer formed between the PMMA cement and bone in group A, while chitosan particles degraded with different levels in groups B, C, and D, especially in group D. At 6 months after operation, chitosan particles partly degraded in groups B, C, and D with an amount of new bone ingrowth, and groups C and D was better than group B in bone growth; group A had no obvious change. Quantitative analysis results showed that the bone tissue percentage was gradually increased in the group A to group D, and the bone tissue percentage at 6 months after operation was significantly higher than that at 3 months within the group. Conclusion According to the weight percentage (W/W, %) of PMMA to bioglass to chitosan, PBCs made by the composition of 40 ︰ 50 ︰ 10 and 30 ︰ 60 ︰ 10 have better biocompatibility and biomechanical properties than PMMA cement, it may reduce the fracture risk of the adjacent vertebrae after vertebroplasty.
Objective To obtain highly purified and large amount of Schwann cells (SCs) by improved primary culture method, to investigate the biocompatibility of small intestinal submucosa (SIS) and SCs, and to make SIS load nerve growth factor (NGF) through co-culture with SCs. Methods Sciatic nerves were isolated from 2-3 days old Sprague Dawley rats and digested with collagenase II and trypsin. SCs were purified by differential adhesion method for 20 minutes and treated with G418 for 48 hours. Then the fibroblasts were further removed by reducing fetal bovine serum to 2.5% in H-DMEM. MTT assay was used to test the proliferation of SCs and the growth curve of SCs was drawn. The purity of SCs was calculated by immunofluorescence staining for S-100. SIS and SCs at passage 3 were co-cultured in vitro. And then the adhesion, proliferation, and differentiation of SCs were investigated by optical microscope and scanning electron microscope (SEM). The NGF content by SCs was also evaluated at 1, 2, 3, 4, 5, and 7 days by ELISA. SCs were removed from SIS by repeated freeze thawing after 3, 5, 7, 10, 13, and 15 days of co-culture. The NGF content in modified SIS was tested by ELISA. Results The purity of SCs was more than 98%. MTT assay showed that the SCs entered the logarithmic growth phase on the 3rd day, and reached the plateau phase on the 7th day. SCs well adhered to the surface of SIS by HE staining and SEM; SCs were fusiform in shape with obvious prominence and the protein granules secreted on cellular surface were also observed. Furthermore, ELISA measurement revealed that, co-culture with SIS, SCs secreted NGF prosperously without significant difference when compared with the control group (P gt; 0.05). The NGF content increased with increasing time. The concentration of NGF released from SIS which were cultured with SCs for 10 days was (414.29 ± 20.87) pg/cm2, while in simple SIS was (4.92 ± 2.06) pg/cm2, showing significant difference (P lt; 0.05). Conclusion A large number of highly purified SCs can be obtained by digestion with collagenase II and trypsin in combination with 20-minute differential adhesion and selection by G418. SIS possesses good biocompatibility with SCs, providing the basis for further study in vivo to fabricate the artificial nerve conduit.
Objective To research in vitro biocompatibility of silicon containing micro-arc oxidation (MAO) coated magnesium alloy ZK60 with osteoblasts. Methods The surface microstructure of silicon containing MAO coated magnesium alloy ZK60 was observed by a scanning electron microscopy (SEM), and chemical composition of the coating surface was determined by energy dispersive spectrum analysis. The experiments were divided into 4 groups: silicon containing MAO coated magnesium alloy ZK60 group (group A), uncoated magnesium alloy ZK60 group (group B), titanium alloy group (group C), and negative control group (group D). Extracts were prepared respectively with the surface area to extraction medium ratio (1.25 cm2/ mL) according to ISO 10993-12 standard in groups A, B, and C, and were used to culture osteoblasts MC3T3-E1. The α-MEM medium supplemented with 10% fetal bovine serum was used as negative control in group D. The cell morphology was observed by inverted phase contrast microscopy. MTT assay was used to determine the cell viability. The activity of alkaline phosphatase (ALP) was detected. Cell attachment morphology on the surface of different samples was observed by SEM. The capability of protein adsorption of the coating surface was assayed, then DAPI and calcein-AM/ethidium homodimer 1 (calcein-AM/EthD-1) staining were carried out to observe cell adhesion and growth status. Results The surface characterization showed a rough and porous layer with major composition of Mg, O, and Si on the surface of silicon containing MAO coated magnesium alloy ZK60 by SEM. After cultured with the extract, cells grew well and presented good shape in all groups by inverted phase contrast microscopy, group A was even better than the other groups. At 5 days, MTT assay showed that group A presented a higher cell proliferation than the other groups (P lt; 0.05). Osteoblasts in groups A and C presented a better cell extension than group B under SEM, and group A exhibited better cell adhesion and affinity. Protein adsorption in group A [ (152.7 ± 6.3) µg/mL] was significantly higher than that of group B [(96.3 ± 3.9) µg/mL] and group C [ (96.1 ± 8.7) µg/mL] (P lt; 0.05). At each time point, the adherent cells on the sample surface of group A were significantly more than those of groups B and C (P lt; 0.05). The calcein-AM/EthD-1 staining showed that groups A and C presented better cell adhesion and growth status than group B. The ALP activities in groups A and B were 15.55 ± 0.29 and 13.75 ± 0.44 respectively, which were significantly higher than those in group C (10.43 ± 0.79) and group D (10.73 ± 0.47) (P lt; 0.05), and group A was significantly higher than group B (P lt; 0.05). Conclusion The silicon containing MAO coated magnesium alloy ZK60 has obvious promoting effects on the proliferation, adhesion, and differentiation of osteoblasts, showing a good biocompatibility, so it might be an ideal surface modification method on magnesium alloys.
Objective To review the research progress of articular cartilage scaffold materials and look into the future development prospects. Methods Recent literature about articular cartilage scaffold for tissue engineering was reviewed, and the results from experiments and clinical application about natural and synthetic scaffold materials were analyzed. Results The design of articular cartilage scaffold for tissue engineering is vital to articular cartilage defects repair. The ideal scaffold can promote the progress of the cartilage repair, but the scaffold materials still have their limitations. Conclusion It is necessary to pay more attention to the research of the articular cartilage scaffold, which is significant to the repair of cartilage defects in the future.
Objective To prepare collagen-chitosan /nano-hydroxyapatite-collagen-polylactic acid (Col-CS/ nHAC-PLA) biomimetic scaffold and to examine its biocompatibility so as to lay the foundation for its application on the treatment of osteochondral defect. Methods PLA was dissolved in dioxane for getting final concentration of 8%, and the nHAC power was added at a weight ratio of nHAC to PLA, 1 ∶ 1. The solution was poured into a mold and frozen. CS and Col were dissolved in 2% acetum for getting the final concentrations of 2% and 1% respectively, then compounded at a weight ratio of CS to Col, 20 ∶ 1. The solution was poured into the frozen mold containing nHAC-PLA, and then biomimetic osteochondral scaffold of Col-CS/nHAC-PLA was prepared by freeze-drying. Acute systemic toxicity test, intracutaneous stimulation test, pyrogen test, hemolysis test, cytotoxicity test, and bone implant test were performed to evaluate its biocompatibility. Results Col-CS/nHAC-PLA had no acute systemic toxicity. Primary irritation index was 0, indicating that Col-CS/nHAC-PLA had very slight skin irritation. In pyrogen test, the increasing temperature of each rabbit was less than 0.6℃, and the increasing temperature sum of 3 rabbits was less than 1.3℃, which was consistent with the evaluation criteria. Hemolytic rate of Col-CS/nHAC-PLA was 1.38% (far less than 5%). The toxicity grade of Col-CS/nHAC-PLA was classified as grade I. Bone implant test showed that Col-CS/nHAC-PLA had good biocompatibility with the surrounding tissue. Conclusion Col-CS/ nHAC-PLA scaffold has good biocompatibility, which can be used as an alternative osteochondral scaffold.
ObjectiveTo explore the influence of three central venous catheter biomedical materials (polyurethane, silicone, and polyvinyl chloride) on the proliferation, apoptosis, and cell cycle of Xuanwei Lung Cancer-05 (XWLC-05) cells so as to provide the basis for clinical choice of central venous catheter. MethodsXWLC-05 cells were cultured and subcultured, and the cells at passage 3 were cultured with polyurethane, silicone, and polyvinyl chloride (1.0 cm × 1.0 cm in size), and only cells served as a control. At 24, 48, and 72 hours after cultured, MTT assay was used to detect the cellular proliferation and flow cytometry to detect the cell cycle and apoptosis. At 72 hours after cultured, inverted microscope was used to observe the cell growth. ResultsInverted microscope showed the cells grew well in control group, polyurethane group, and silicone group. In polyvinyl chloride group, the cells decreased, necrosed, and dissolved; residual adherent cells had morphologic deformity and decreased transmittance. At 24 and 48 hours, no significant difference in proliferation, apoptosis, and cell cycle was found among 4 groups (P gt; 0.05). At 72 hours, the proliferations of XWLC-05 cells in three material groups were significantly inhibited when compared with control group (P lt; 0.05), and the cells in polyvinyl chloride group had more significant proliferation inhibition than polyurethane group and silicone group (P lt; 0.05), but there was no signifcant difference in proliferation inhibition between polyurethane group and silicone group (P gt; 0.05). Compared with the control group, three material groups had significant impact on the rate of apoptosis and cell cycle: polyvinyl chloride group was the most remarkable, followed by silicone group, polyurethane group was minimum (P lt; 0.05). ConclusionPolyvinyl chloride can significantly impact the proliferation, apoptosis, and cell cycle of XWLC-05 cells; polyurethane has better biocompatibility than polyvinyl chloride and silicone
Objective Surface modification of nitinol (NiTi) shape memory alloy is an available method to prevent nickel ion release and coating with titanium-niobium (TiNb) alloy will not affect the superelasticity and shape memory of NiTi. To evaluate the bone histocompatibil ity of NiTi shape memory alloy implants coated by TiNb in vivo. Methods NiTi memory alloy columns which were 4 mm in diameter and 12 mm in length were coated with Ti (Ti-coating group) and TiNb alloy (TiNb-coating group) respectively by magnetron sputtering technique. And NiTi group were not coated on the surface. Fifteen mongrel dogs were divided into 3 groups randomly with 5 dogs in each group. NiTi, Ti-coating and TiNb-coating columns were implanted into the lateral femoral cortex of each group, respectively. There were 10 columns embedded in eachdog’s femur whose distance was 1.0 cm to 1.5 cm from each other. The materials were obtained 12 months after operation. After X-ray photography, only those columns which were perpendicular to the cortex of the femur shaft were selected for subsequent analysis. Push-out tests were performed to attain the maximum shear strength (the number of specimens of TiNi group, Ticoating group, and TiNb-coating group were 12, 10, and 14, respectively). Undecalcified sections were used for histological observation and the calculation of osseointegration rate (the number of specimens of TiNi group, Ti-coating group, and TiNb-coating group were 8, 5, and 10, respectively). Results The maximum shear strength of Ti-coating group (95.10 ± 10.03) MPa, and TiNb-coating group (91.20 ± 15.42) MPa were significantly higher than that of NiTi group (71.60 ± 14.24) MPa (P lt; 0.01). Gimesa staining showed that no obvious macrophage and inflammation cell was observed in 3 groups. The osseointegration rates of NiTi group, Ti-coating group, and TiNb-coating group were (21.30% ± 0.23%), (32.50% ± 0.31%), and (38.60% ± 0.58%), respectively; there were significant differences among 3 groups (P lt; 0.01). Conclusion The implants of 3 groups all have good bone histocompatabil ity. But the osseointegration rate and the shear strength in the Ti-coating group and the TiNb-coating group were better than those in the NiTi group, the TiNb-coating group is the best among them.
Objective To study the preparation method of acellular vascular matrix and to evaluate its biocompatibil ity and safety so as to afford an ideal scaffold for tissue engineered blood vessel. Methods Fresh caprine carotids (length, 50 mm) were harvested and treated with repeated frozen (—80 )/thawing (37℃), cold isostatic pressing (506 MPa, 4 ), and 0.125% sodium dodecyl sulfate separately for preparation of acellular vascular matrix. Fluorescence staining and DNA remain test were used to assess the cell extracting results. Biological characteristics were compared with the raw caprine carotids using HE staining, Masson staining, scanning electron microscope (SEM), and mechanical test. Biocompatibil ity wasdetected using cell adhesion test, MTT assay, and subcutaneously embedding test. Ten SD rats were divided into 2 groups (n=5). In experimental group, acellular vascular matrix preserved by the combination of repeated frozen/thawing, ultrahigh pressure treatment and chemical detergent was subcutaneously embedded; and in control group, acellular vascular matrix preserved only by repeated frozen/thawing and ultrahigh pressure treatment was subcutaneously embedded. Results HE staining and Masson staining revealed that no nucleus was detected in the acellular vascular matrix. SEM demonstrated that a lot of collagen fibers were preserved which were beneficial for cell adhesion. Fluorescence staining and DNA remain test showed that the cells were removed completely. There was no significant difference in stress and strain under the maximum load between before and after treatment. Mechanical test revealed that the acellular vascular matrix reserved mechanical properties of the raw caprine carotids. Cell adhesion test and MTT assay confirmed that cytotoxicity was grade 0-1, and the acellular vascular matrix had good compatibil ity to endothel ial cells. After subcutaneously embedding for 8 weeks, negl igible lymphocyte infiltration was observed in experimental group but obvious lymphocyte infiltration in control group. Conclusion The acellular vascular matrix, which is well-preserved by the combination of repeated frozen/thawing, ultrahigh pressure treatment, and chemical detergent, is an ideal scaffold for tissue engineered blood vessel.