Objective To investigate the promotion effect of neurotropic reinnervation with chemically extracted acellular nerve allograft. Methods The sciatic nerves of 5 healthy adult SD rats, regardless of gender and weighing 270-300 g, were collected to prepare chemically extracted acellular nerve allograft. Eighteen healthy adult Wistar rats, regardless of genderand weighing 300-320 g, were made the model of left sciatic nerve defect (10 mm) and randomly divided into 2 groups: autograft (control group, n=9) and allograft group (experimental group, n=9). The defects were bridged by acellular nerve allograft in experimental group and by autograft by turning over the proximal and distal ends of the nerve in control group. At 3 months after transplantation, dorsal root ganglion (DRG) resection operation was performed in 6 rats of 2 groups. At 3 weeks after operation, the sural nerves were harvested to calculate the misdirection rate of nerve fibers with pathological staining and compute-assisted image analysis. Cholinesterase staining and carbonic anhydrase staining were performed in the sural nerve of 3 rats that did not undergo DRG resection at 3 months. Results The results of chol inesterase staining and carbonic anhydrase staining showed that experimental group had less brown granules and more black granules than control group. After DRG resection, count of myelinated nerve fiber were 4 257 ± 285 in the experimental group and 4 494 ± 310 in the control group significant (P lt; 0.05). The misdirection rate was 2.27% ± 0.28% and 7.65% ± 0.68% in the experimental group and in the control group respectively, showing significant difference (P lt; 0.05). Conclusion Chemically extracted acellular nerve allograft can not only act as a scaffold in the period of nerve defects repair, but markedly enhance the effects of neurotropic reinnervation.
ObjectiveTo observe the volume and distribution of necrotic tissue of femoral head in steroid-induced osteonecrosis of femoral head (SONFH) patients by three-dimensional reconstruction of CT.MethodsA clinical data of 25 patients with SONFH between September 2016 and December 2018 was analyzed. There were 22 males and 3 females, with an average age of 38.8 years (range, 20-63 years). The necrosis of the femoral head was in stage Ⅱ of Association Research Circulation Osseous (ARCO). The disease duration ranged from 3 to 18 months, with an average of 9.2 months. A three-dimensional reconstruction with CT data of SONFH patients were performed by Mimics Research 21.0 software and the femoral head was segmented into eight regions by 3-matic Research 13.0 software. The volume of necrotic tissue of the femoral head and the volume rate of necrotic tissue to femoral head were calculated and the distribution was also analyzed.ResultsThe three-dimensional digital model of the femoral head showed that the necrotic tissue of the femoral head was located above the anterior superior medial, and the area of the necrotic tissue was in a dome-like shape. The results showed that the necrotic tissue in the femoral head was mainly concentrated on the anterior superior internal area, the anterior superior outer area, and the posterior superior internal area. The volume of femoral head was (48 399.52±9 408.90) mm3, and the volume of necrotic tissue was (20 917.08±6 566.94) mm3, and the volume ratio of necrotic tissue to femoral head was 44.75%±15.72%. The proportion of necrotic volume in different regions was different, and the necrotic tissues were mainly distributed in the anterior superior internal area, the anterior superior outer area, and the posterior superior internal area.ConclusionThe volume and distribution of necrotic tissue in femoral head can be evaluated quickly and intuitively by three-dimensional reconstruction of CT in Mimics software.
Objective Bone marrow mesenchymal stem cells (BMSCs), as replacement cells of Schwann cells, can increase the effect of peripheral nerve repair. However, it has not yet reached any agreement to add the appropriate number of seeded cells in nerve scaffold. To investigate the effect of different number of BMSCs on the growth of rat dorsal root gangl ia(DRG). Methods Three 4-week-old Sprague Dawley (SD) rats (weighing 80-100 g) were selected to isolate BMSCs, whichwere cultured in vitro. Three 1- to 2-day-old SD rats (weighing 4-6 g) were selected to prepare DRG. BMSCs at passage 3 were used to prepare BMSCs-fibrin glue complex. According to different number of BMSCs at passage 3 in fibrin glue, experiment was divided into group A (1 × 103), group B (1 × 104), group C (1 × 105), and group D (0, blank control), and BMSCs were cocultured with rat DRG. The axon length of DRG, Schwann cell migration distance, and axon area index were quantitatively evaluated by morphology, neurofilament 200, and Schwann cells S-100 immunofluorescence staining after cultured for 48 hours. Results Some long cell processes formed in BMSCs at 48 hours; migration of Schwann cells and axons growth from the DRG were observed, growing in every direction. BMSCs in fibrin glue had the biological activity and could effect DRG growth. The axon length of DRG and Schwann cell migration distance in groups A, B, and C were significantly greater than those in group D (P lt; 0.05). The axon length of DRG and Schwann cell migration distance in group C were significantly less than those in group B (P lt; 0.05), but there was no significant difference between group A and group C, and between group A and group B (P gt; 0.05). The axon area index in groups A and B was significantly greater than that in group D (P lt; 0.05), but there was no significant difference between group C and group D (P gt; 0.05); there was no significant difference in groups A, B, and C (P gt; 0.05). Conclusion In vitro study on DRG culture experiments is an ideal objective neural model of nerve regeneration. The effect of different number of BMSCs in fibrin glue on the growth of DRG has dose-effect relationship. It can provide a theoretical basis for the appropriate choice of the BMSCs number for tissue engineered nerve.
Objective Poly (propylene carbonate) (PPC), a newly reported polymer, has good biodegradabil ity and biocompatibil ity. To explore the feasibil ity of using electrospinning PPC materials in nerve tissue engineering, and to observe the effect of al igned and random PPC materials on axonal growth of rat dorsal root gangl ions (DRGs) in vitro. Methods Either al igned or randomly oriented sub-micron scale polymeric fiber was prepared with an electrospinning process. DRGs were harvested from 3 newborn Sprague-Dawley rats (female or male, weighing 4-6 g), and were incubated into 12-pore plate containing either al igned (the experimental group, n=6) or randomly oriented sub-micron scale polymeric fiber (the control group, n=6). The DRGs growth was observed with an inverted microscope; at 7 days immunofluorescent staining and scanning electronic microscope (SEM) observation were performed to quantify the extent of neurite growth andSchwann cells (SCs) migration. Results Either al igned or random fibers were fabricated by an electrospinning process. The diameter of the individual fiber ranged between 800 nm and 1 200 nm. In al igned PPC material, 90% fibers arranged in long axis direction, but the fibers in random PPC material arranged in all directions. The DRGs grew well in 2 PPC materials. Onthe al igned fiber film, the majority of neurite growth and SCs migration from the DRGs extended unidirectionally, parallel to the al igned fibers; however, neurite growth and SCs migration on the random fiber films oriented randomly. The extents of neurite growth were (2 684.7 ± 994.8) μm on the al igned fiber film and (504.7 ± 52.8) μm on the random fiber films, showing significant difference (t= —5.360, P=0.000). The distances of SCs migration were (2 770.6 ± 978.4) μm on the al igned fiber film and (610.2 ± 56.3) μm on the random fiber films, showing significant difference (t= —5.400, P=0.000). The extent of neurite growth was fewer than the distances of SCs migration in 2 groups. Conclusion The orientation structure of sub-micron scalefibers determines the orientation and extent of DRGs neurite growth and SCs migration. Al igned electrospinning PPC fiber is proved to be a promising biomaterial for nerve regeneration.
Objective To construct a recombinant adenovirus vector pAdxsi-GFP-NELL1 that co-expressing green fluorescent protein (GFP) and homo sapiens NEL-l ike 1 (NELL1) protein (a protein bly expressed in neural tissue encoding epidermal growth factor l ike domain), to observe its expression by transfecting the recombinant adenovirus into rat bone marrow mesenchymal stem cells (BMSCs) so as to lay a foundation for further study on osteogenesis of NELL1 protein. Methods From pcDNA3.1-NELL1, NELL1 gene sequence was obtained, then NELL1 gene was subcloned into pShuttle-GFP-CMV (-)TEMP vector which was subsequently digested with enzyme and insterted into pAdxsi vector to package the recombinant adenovirus vector (pAdxsi-GFP-NELL1). After verified by enzyme cutting and gel electrophoresis, pAdxsi-GFPNELL1 was ampl ified in HEK293 cells and purified by CsCl2 gradient purification, titrated using 50% tissue culture infective dose (TCID50) assay. The rat BMSCs were cultured and identified by flow cytometry and directional induction, then were infected with adenoviruses (pAdxsi-GFP-NELL1 and pAdxsi-GFP). NELL1 expression was verified by RT-PCR and immunofluorescence; GFP gene expression was verified by the intensity of green fluorescence under fluorescence microscope. Cell counting kit-8 (CCK-8) was used for investigate the influence of vectors on the prol iferation of rat BMSCs. Results Recombinant adenoviral vector pAdxsi-GFP-NELL1, which encodes a fusion protein of human NELL1, was successfully constructed and ampl ified with titer of 1 × 1011 pfu/mL. The primary BMSCs were cultured and identified by flow cytometric analysis, osteogenic and adipogenic induction, then were used for adenoviral transfection efficiency and cell toxicity tests. An multipl icity of infection of 200 pfu/cell produced optimal effects in transfer efficiency without excessive cell death in vitro. Three days after transfection with 200 pfu/cell pAdxsi-GFP-NELL1 or pAdxsi-GFP, over 60% BMSCs showed green fluorescent by fluorescence microscopy. Imunofluorescence with NELL1 antibody also revealed high level expression of human NELL1 protein in red fluorescent in these GFP expressing cells. RT-PCR analysis confirmed that the exogenous expression of NELL1 upon transfection with pAdxsi-GFPNELL1 at 200 pfu/cell, whereas NELL1 remained undetectable in Ad-GFP-transfected rat BMSCs. The prol iferative property of primary rat BMSCs after adenoviral NELL1 transfection was assayed by CCK-8 in growth medium. Growth curve demonstratedno significant difference among BMSCs transfected with pAdxsi-GFP-NELL1, pAdxsi-GFP, and no treatment control at 7 days (P gt; 0.05). Conclusion Recombinant adenovirus vector pAdxsi-GFP-NELL1 can steady expressing both GFP and NELL1 protein after being transfected into rat BMSCs. It provides a useful tool to trace the expression of NELL1 and investigate its function in vitro and in vivo.
Objective Native extracellular matrix (ECM) is comprised of a complex network of structural and regulatory proteins that are arrayed into a tissue-specific, biomechanically optimal, fibrous matrix. The multifunctional nature of the native ECM will need to be considered in the design and fabrication of tissue engineering scaffolds. To investigate the extraction techniques of naturally derived nerve ECM and the feasibil ity of nerve tissue engineering scaffold. Methods Ten fresh canine sciatic nerves were harvested; nerve ECM material was prepared by hypotonic freeze-thawing, mechanicalgrinding, and differential centrifugation. The ECM was observed by scanning electron microscope. Immunofluorescencestaining was performed to detect specific ECM proteins including collagen type I, laminin, and fibronectin. Total collagen and glycosaminoglycan (GAG) contents were assessed using biochemical assays. The degree of decellularization was evaluated with staining for nuclei using Hoechst33258. The dorsal root gangl ion and Schwann cells of rats were respectively seeded onto nerve tissue-specific ECM films. The biocompatibil ity was observed by specific antibodies for cell markers. Results Scanning electron microscope analysis revealed that nerve-derived ECM consisted of a nanofibrous structure, which diameter was 30-130 nm. Immunofluorescence staining confirmed that the nerve-derived ECM was made up of collagen type I, laminin, and fibronectin. The histological staining showed that the staining results of sirius red, Safranin O, and toluidine blue were positive. Hoechst33258 staining showed no DNA within the decellularized ECM. Those ECM films had good biocompatibil ity for dorsal root gangl ion and Schwann cells. The cotents of total collagen and GAG in the nerve-derived ECM were (114.88 ± 13.33) μg/ mg and (17.52 ± 2.34) μg/mg, showing significant difference in the content of total collagen (P lt; 0.01) and no significant difference in the content of GAG (P gt; 0.05) when compared with the contents of normal nerve tissue [(54.07 ± 5.06) μg/mg and (25.25 ± 1.56) μg/mg)]. The results of immunofluorescence staining were positive for neurofilament 200 after 7 days and for S100 after 2 days. Conclusion Nerve-derived ECM is rich in collagen type I, laminin, and fibronectin and has good biocompatibil ity, so it can be used as a nerve tissue engineering scaffold.
Objective To explore the effect of controlled release of nerve growth factor (NGF) on peripheral nerve defect repaire by acellular nerve graft. Methods The microspheres of NGF were prepared with drug microsphere technologyand fixed with the fibrin glue to make the compl icated controlled release NGF. Twenty healthy male SD rats weighing 280-300 g were adopted to prepare acellular xenogenous nerve, 52 male Wistar rats weighing 250-300 g were adopted to prepare the 10 mm defect model of left sciatic nerve. and thereafter were randomly divided into 4 groups: autograft group(group A), acellular nerve allograft combined with the double controlled release NGF (group B), acellular nerve allograft (group C) and acellular nerve allograft combined with fibrin glue (group D). Without any operation, the right sciatic nerve was regarded as control group. General observation was conducted after operation. The nerve axon regeneration length was measured 2 weeks after operation. The effects of peripheral nerve regeneration were evaluated by neural electrophysiology, the recovery rate of triceps surae muscular tension and weight and histological assessment 16 weeks after operation. Results All the animals survived till the end of experiment. The length of nerve regeneration was measured at 2 weeks after transplantation. The regeneration nerve of group A was longer than that of other groups (P lt; 0.05), group B longer than groups C and D (P lt; 0.05), and there were no difference between group C and group D (P gt; 0.05). At 16 weeks after operation, the recovery rates of nerve conduction velocity of groups A and B (73.37% ± 7.82% and 70.39% ± 8.45%) were larger than that of groups C and D (53.51% ± 6.31% and 55.28% ± 5.37%) (P lt; 0.05). The recovery rates of the triceps surae muscular tension in group A (85.33% ± 5.59%) were larger than that in groups B, C and D (69.79% ± 5.31%, 64.46% ± 8.49％ and 63.35% ± 6.40%) (P lt; 0.05). There were no significant differences among groups B, C and D (P gt; 0.05). The recovery rates of the triceps surae weight in group A (62.54% ± 8.25%) werelarger than that in groups B, C and D (53.73% ± 4.56%, 46.37% ± 5.68% and 45.78% ± 7.14%, P lt; 0.05). There was significant difference between group B and groups C, D (P lt; 0.05) and no significant differences between group C and group D (P gt; 0.05). The histological observation indicated that axon number and myel in thickness in group B were larger than those in group C and group D (P lt; 0.05). The axonal diameter in group B was significantly less than that in group A (P lt; 0.05). Conclusion Acellular nerve graft combined with the controlled release NGF is a satisfactory alternative to repair the peripheral nerve defect.
Objective To observe the histological structure and cytocompatibility of novel acellular bone matrix (ACBM) and to investigate the feasibility as a scaffold for bone tissue engineering. Methods Cancellous bone columns were harvested from the density region of 18-24 months old male canine femoral head, then were dealt with high-pressure water washing, degreasing, and decellularization with Trixon X-100 and sodium deoxycholate to prepare the ACBM scaffold. The scaffolds were observed by scanning electron microscope (SEM); HE staining, Hoechst 33258 staining, and sirius red staining were used for histological analysis. Bone marrow mesenchymal stem cells (BMSCs) from canine were isolated and cultured with density gradient centrifugation; the 3rd passage BMSCs were seeded onto the scaffold. MTT test was done to assess the cytotoxicity of the scaffolds. The proliferation and differentiation of the cells on the scaffold were observed by inverted microscope, SEM, and live/dead cell staining method. Results HE staining and Hoechst 33258 staining showed that there was no cell fragments in the scaffolds; sirius red staining showed that the ACBM scaffold was stained crimson or red and yellow alternating. SEM observation revealed a three dimensional interconnected porous structure, which was the microstructure of normal cancellous bone. Cytotoxicity testing with MTT revealed no significant difference in absorbance (A) values between different extracts (25%, 50%, and 100%) and H-DMEM culture media (P gt; 0.05), indicating no cytotoxic effect of the scaffold on BMSCs. Inverted microscope, SEM, and histological analysis showed that three dimensional interconnected porous structure of the scaffold supported the proliferation and attachment of BMSCs, which secreted abundant extracellular matrices. Live/dead cell staining results of cell-scaffold composites revealed that the cells displaying green fluorescence were observed. Conclusion Novel ACBM scaffold can be used as an alternative cell-carrier for bone tissue engineering because of thoroughly decellularization, good mircostructure, non-toxicity, and good cytocompatibility.
Objective To investigate the effect of bone marrow mesenchymal stem cells (BMSCs) embedded in fibrin glue around chemical extracted acellular nerve allograft (CEANA) on the peripheral nerve regeneration. Methods Twenty-oneadult male C57 mice (weighing 25-30 g) and 15 adult male Balb/c mice (weighing 25-30 g) were selected. The sciatic nerves were harvested from the Balb/c mice to prepare CEANA. The BMSCs were isolated from 3 C57 mice and were cultured; BMSCs embedded in fibrin glue were cultured for 3, 7, 14, and 21 days. Then the supernatant was obtained and co-cultured with PC12 cells for 2 days to observe the PC12 cell growth in vitro. The other 18 C57 mice were used to establ ish the left sciatic nerve defect models of 10 mm and divided into 3 groups: autogenous nerve graft with fibrin glue (group A, n=6), CEANA graft with BMSCs (5 × 106) embedded in fibrin glue (group B, n=6), and CEANA graft with fibrin glue (group C, n=6). The right sciatic nerves were exposed as the controls. At 2, 4, 6, and 8 weeks, the mouse static sciatic index (SSI) was measured. The histomorphometric assessment of triceps surae muscles and nerve grafts were evaluated by Masson staining, toluidine blue staining, and transmission electron microscope (TEM) observationat 8 weeks after operation. Results BMSCs were uniform distribution in fibrin glue, which were spherical in shape, and the cells began to grow apophysis at 3 days. PC12 cells differentiated into neuron-l ike cells after addition supernatant co-cultured after 2 days. Incisions healed well in each group. At 2, 4, 6, and 8 weeks, the SSI increased gradually in 3 groups. SSI in group A was higher than that in groups B and C at 4, 6, and 8 weeks after operation (P lt; 0.05). SSI in group B was sl ightly higher than that in group C, but had no significant difference (P gt; 0.05). At 8 weeks, the wet weight recovery rate of triceps surae muscles and fibers number of myel inated nerve were better in group B than in group C, but worse in group B than in group A, showing significant differences (P lt; 0.05). The triceps surae muscle fibers area and myel in sheath thickness had significant differences between group B and group C (P lt; 0.01), but there was no significant difference between group A and group B (P gt; 0.05). Conclusion BMSCs embedded in fibrin glue around CEANA can improve functional recovery of peripheral nerve injury.
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.