Objective To develop an experimental model of abdominal aorta transplantation with nano-biomimetictissue engineered blood vessel (NBTEBV) and to investige the change of histomorphology in evolutionary process of degradation and remodel ing. Methods Twenty 6-month-old New Zealand rabbits were included, weighing 2-3 kg, male or female. The autologous seed cells of rabbits were harvested to build NBTEBV in vitro. After the branch of abdominal aorta under kidney was l igated, about 10 mm abdominal aorta was cut and replaced by NBTEBV; the anastomotic stoma was marked by Ti cl ips. NBTEBV’s evolutionary processes of degradation and rebuilding were observed. Twelve weeks after operation, DSA and color Doppler examinations were made. At 1, 4 and 12 weeks after operation, the gross and histological observations were made and 14C binding in PLGA was detected with X-ray photon spectroscopy. Results Of 20 rabbits, 17 showed that the NBTEBV was patency; 3 died from NBTEBV occlusion 36 or 72 hours after operation. The results of DAS and color Doppler showed the blood flow was patency, the blood flow rate was normal and there was no angiectasis. The lumen of transplanted blood vessel was covered with monolayer endothel ial cells. At 1 week, smooth muscle cells (SMCs) arranged regularly and much PLGA distributed in the EMCs. At 4 weeks, SMCs arranged in a layer, ECM was forming, mimic ECM degraded partly; PLGA decreased obviously. At 12 weeks, the SMCs arranged regularly, ECM formed, mimic ECM degraded, no PLGA was seen in the wall, the shape of graft was similar to the natural vessel. The decreasing crest value of 14C in specimen showed the degradation of PLGA. Conclusion NBTEBV has a good surgical maneuverabil ity and histocompatibil ity, its remodel ing evolutionary process fits in with tissue engineering specification. Building NBTEBV with ELSP is feasible.
OBJECTIVE: To study the histocompatibility and degradation in vivo of a new artificial material, calcium polyphosphate fiber (CPPF), and to provide some experimental basis for further study in tendon tissue engineering. METHODS: CPPF and carbon fiber (CF) as control material were implanted in symmetry part in subcutaneous layer, muscle and Achilles tendon of 20 SD rats. The day of operation, the 4th, 8th, 12th, 16th, and 20th weeks after operation, X-ray examination was performed to detect the density change of materials. Local tissue and materials were observed grossly, and pathological examination was made with HE staining 4, 8, 12, 16 weeks after operation. RESULTS: CPPF degraded completely within 16 weeks in muscle, and in 20 weeks after implantation in Achilles tendon and subcutaneous layer according to X-ray and pathological examination. No calcium phosphate crystal deposit was observed in local tissue. No obviously degradation of CF was found within 20 weeks. Local infiltration of lymphocytes and macrophagocytes around CPPF were much fewer than that of CF. CPPF combined compactly with surrounding hyperplastic tissue. CONCLUSION: CPPF degrade thoroughly from 16 to 20 weeks without sediment of crystal of calcium phosphate in vivo. CPPF has good histocompatibility and can be used as a scaffold material of tissue engineering.
ObjectiveTo explore the degradation of AZ31 magnesium alloy and poly (lactic-co-glycolic acid) (PLGA) in the femoral condyle, and then evaluate the laws of degradation of AZ31 magnesium alloy by Micro-CT images and data. MethodsForty 3-month-old male New Zealand white rabbits (weighing, 2.5 kg) were randomly divided into 4 groups, 10 rabbits each group. Forty micro-arc-oxidized AZ31 magnesium alloy pins and 40 PLGA pins were implanted into the right and left femoral condyle, respectively. Micro-CT images and data analysis were used to evaluate the degradation at 4, 8, 12, and 16 weeks after operation (n=10). Degradation was evaluated by weight difference between pre-and post-implantation. The inflammatory response was observed around the implants by HE staining. The weight loss of magnesium alloy and Micro-CT results were compared. ResultsThe Micro-CT images showed that PLGA pins had gray low signal, which was similar to the soft tissue around. At 4 weeks after operation, no signs of degradation were observed, and there were little corrosion pitting on the magnesium alloy. At 8 weeks, corrosion pitting gradually expanded, the boundary between the longitudinal axis and the cross section became blurred; at 16 weeks, corrosion pitting became bigger, and the boundary was discontinuous. Micro-CT quantitative analysis showed that the volume fraction of magnesium pins decreased slowly at 4 and 8 weeks; it was significantly lower at 12 and 16 weeks than 4 and 8 weeks (P < 0.05). The magnesium cylinder mineral density continuously decreased during the study period, it had a rapidly speed from 12 to 16 weeks (P < 0.05). However, the magnesium CT image density showed a slight change (P>0.05). The surface-to-volume ratio of the pins constantly increased, and the ratio was significantly larger at 12 and 16 weeks than 4 and 8 weeks, and at 16 weeks than 12 weeks (P < 0.05). There was more and more corrosion pitting on the surface with time, which resulted in a decrease in the radius that mean trabecular thickness gradually decreased, showing significant difference between different time points after 8 weeks (P < 0.05). The weight loss detection showed that the degradation of magnesium pin and PLGA gradually increased with time (P < 0.05), and the degradation rate of magnesium pin was significantly lower than that of PLGA at 8-12 weeks (P < 0.05), but the degradation rate of magnesium pin was higher than that of PLGA at 16 weeks. At each time point, the weight loss of magnesium alloy was similar to that by Micro-CT, but mass fraction was lower than volume fraction and had significant differences at 8, 12, and 16 weeks (P < 0.05). HE staining revealed that slight inflammatory response was observed around the magnesium pins at 4 weeks, and inflammatory reaction gradually reduced with time and disappeared at 16 weeks, but no inflammatory reaction was seen around PLGA. ConclusionMicro-CT has the advantages of non-trauma, in vivo detection, quantitative analysis, and precise data in evaluating the degradation of AZ31 magnesium alloy. Regarding the degradation of the magnesium alloy and PLGA in vivo, the degradation rate is slow in the early stage, and then increases with time. The degradation of PLGA is faster and earlier but it is then overtaken by AZ31 magnesium alloy at 16 weeks. During the degradation, the density of the magnesium has almost no change. The biomaterials can not firmly attach to the surrounding tissues due to inadequate holding forces.