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The repair of craniofacial bone defects is surgically challenging due to the complex anatomical structure of the craniofacial skeleton. Current strategies for bone tissue engineering using a preformed scaffold have not resulted in the expected clinical regeneration due to difficulty in seeding cells into the deep internal space of scaffold, and the inability to inject them in minimally invasive surgeries. In this study, we used the osteoconductive and mechanical properties of nano-scale calcium sulfate (nCS) and the biocompatibility of alginate to develop the injectable nCS/alginate (nCS/A) paste, and characterized the effect of this nCS/A paste loaded with bone morphogenetic protein 2 (BMP2) gene-modified rat mesenchymal stem cells (MSCs) on bone and blood vessel growth. Our results showed that the nCS/A paste was injectable under small injection forces. The mechanical properties of the nCS/A paste were increased with an increased proportion of alginate. MSCs maintained their viability after the injection, and MSCs and BMP2 gene-modified MSCs in the injectable pastes remained viable, osteodifferentiated, and yielded high alkaline phosphatase activity. By testing the ability of this injectable paste and BMP2-gene-modified MSCs for the repair of critical-sized calvarial bone defects in a rat model, we found that BMP2-gene-modified MSCs in nCS/A (nCS/A+M/B2) showed robust osteogenic activity, which resulted in consistent bone bridging of the bone defects. The vessel density in nCS/A+M/B2 was significantly higher than that in the groups of blank control, nCS/A alone, and nCS/A mixed with MSCs (nCS/A+M). These results indicate that BMP2 promotes MSCs-mediated bone formation and vascularization in nCS/A paste. Overall, the results demonstrated that the combination of injectable nCS/A paste and BMP2-gene-modified MSCs is a new and effective strategy for the repair of bone defects.
Craniofacial destruction is devastating to patients with facial trauma, congenital deformities of the facial skeleton, and oral malignancies, because it leads to devastating effects on patients' quality of life. Current clinical therapies mainly rely on using grafting materials, including autografts, allografts, xenografts, or alloplasts. Although these therapies can restore certain craniofacial bone defects to a limited degree, they are far from ideal. For example, major concerns over the use of autografts include the need for a second site of surgery, insufficient supply, inadequate size and shape, and the morbidity associated with the donor site. Other grafts such as alloplasts, allografts, and xenografts have disadvantages such as carrying the risk of long-term foreign body reaction, pathogen transmission and immune rejection, multiple surgeries, facial scar formation, and limited new bone formation.1–3 Hence, improved strategies are urgently needed to better treat critical-sized craniofacial bone defects with fewer surgeries, less scar formation and pain, and better aesthetic results.
One focus of craniofacial reconstructive research has been the use of tissue-engineered bone as a promising alternative to implant materials.4 In bone tissue engineering, the scaffold plays a crucial role in defining the 3D anatomical shape and microenvironment for regenerative cells, favoring the regeneration of new bone, maintaining space, and preventing soft tissue prolapsed in the bony lesion. Traditional cell-based therapies have employed preformed scaffolds. These scaffolds have many drawbacks, including the requirement of an open surgery procedure5 and machining the graft or carving the surgical site, which leads to increased bone loss, trauma, and surgical time;6 the difficulty in seeding cells into the deep internal space of the scaffold; and the inability to inject in minimally invasive surgeries.7 Facing the problems of irregular bone defects, injectable scaffolds are advantageous, because they can provide better performance in re-contoured craniofacial defects, incorporate various growth factors and cells, and do not require an open surgical procedure for placement.7,8 Thus, they can shorten the surgical time, minimize the damage, and achieve rapid recovery. Several injectable hydrogel and polymer carriers have been shown to be meritorious for cell delivery.7,9 However, these injectable carriers are not suitable for load-bearing repairs. Mechanical properties are important for the regeneration of load-bearing tissues such as the bone, to withstand stress to avoid scaffold fracture and maintain the structure to define the shape of the regenerated tissue.
Calcium sulfate (CS) is a crystalline structure. It is a biocompatible, bioactive, and biodegradable material.10 CS has a compressive strength which is greater than that of cancellous bone. The application of CS includes the filling of cysts, bone cavities,11,12 and segmental bone defects.13 In previous reports, CS occupies a unique position in the injectable paste materials.14–16 CS pastes can be easily injected percutaneously using a syringe and have been used in the treatment of periodontal disease, alveolar bone loss, and maxillary sinus augmentation,17,18 and as an adjunct with other graft materials in guided tissue regeneration.19 In recent years, significant progress has been made in various materials structured at the nano-scale.20,21 Since nanoparticles have significant surface effects, size, and quantum effects, nanocomposites usually exhibit much better performance properties than do traditional materials. The improved relevant properties include enhanced strength, stiffness, improved transparency, increased scratch, abrasion, solvent and heat resistance, increased surface area, and decreased gas permeability.22 Nano-calcium sulfate (nCS) particles in the range of 30–100nm can enhance physical properties, such as high-surface area for growth factor adsorption, with the potential for controlling the rate of release of the adsorbed material, as well as superior mechanical strength for optimal osteoconductivity and resistance to fractures.23 However, scaffolds made solely of these nano-scale particles have only nano-scale pores. These cannot provide space for cell migration and vascularization. Space for cells and blood vessels is one of the most important elements of scaffolds.24,25 The addition of macro pores should not only enhance cell migration, but also help vascularization for oxygen and nutrient delivery, waste removal, and protein transport.26,27
Alginate is a natural anionic polysaccharide that is commonly obtained from brown seaweed. Due to its biocompatibility, low immunogenicity, mildness of gelation conditions, high hydrophilicity, biodegradability under normal physiological conditions, and low cost, purified alginate has been widely used in food and pharmaceutical industries and many biomedical therapeutic applications,28–30 and for bone tissue engineering.31–35 Alginate consists of poly-d-mannuronic acid (M) blocks, poly-l-guluronic acid (G) blocks, and alternating G/M blocks and forms stable hydrogels in the presence of certain divalent cations (i.e., Ca2+) through the ionic interaction between the carboxylic acid group located on the polymer backbone and the chelating cation.36,37 Alginate hydrogels cross-linked with calcium have the advantage of being injectable.38 In addition, when a scaffold containing alginate is placed in the medium, there is uncontrolled degradation of ionically cross-linked alginate due to the loss of divalent cations.39,40 This leads to the formation of pores inside the scaffold, which enhances cell migration.41
Although scaffolds provide templates for bone regeneration, biologic factors such as cells, growth factors, or genes are typically required to effectively repair challenging bone defects.42 Mesenchymal stem cells (MSCs) are a population of multipotent, nonhematopoietic marrow-derived cells that are easily expanded in culture and differentiate into cells with an osteogenic (OS) phenotype.43,44 Implantation of the MSCs has the potential to enhance healing of the bone.45 Osteoinductive growth factors such as recombinant human bone morphogenetic protein-2 (rhBMP2) have demonstrated some clinical success for bone healing, but large sustainable doses46,47 and the extremely high costs of manufacturing this glycoprotein48 restrict its clinical applications. It has been proved that MSCs that are genetically engineered to express specific growth factors such as recombinant rhBMP2 have unique advantages for promoting bone regeneration because the gene expression in cells is stable, and this treatment modality is much less expensive than that using the recombinant protein.49 Therefore, this study aims at developing an injectable, biodegradable, porous, and load-bearing nCS/alginate (nCS/A) delivery system for the implantation of BMP2-gene-modified MSCs to improve the treatment of critical-sized craniofacial bone defects. We developed and characterized the nCS/A paste delivery system, and analyzed the in vitro growth characteristic of BMP2-gene-modified MSCs in the nCS/A paste as well as the in vivo bone formation by the implantation of nCS/A paste with BMP2-gene-modified MSCs in a rat critical-sized calvarial defect.
nCS was produced according to the method of Park et al.23,50 Briefly, a cryo-vacuum process was used to convert hydrate CS into dihydrate nCS, which was then subjected to oven drying to produce hemihydrate nCS as previously described.51 Sterilization was performed by glow discharge treatment. The injectable nCS/A pastes were formulated by varying the ratio of nCS and alginate. Briefly, alginate was dissolved in phosphate-buffered saline to prepare 15%, 10%, and 5% solution, and then, pH was adjusted to 7.2–7.4. About 127.5, 135, or 142.5mg nCS powder was, respectively and correspondingly, mixed with 150μL alginate in the ratios 85:15, 90:10, or 95:5. The total mass of nCS and alginate was 150mg. After 2min, a 25μL cell suspension with 1×106 MSCs infected with Ad-LacZ or Ad-BMP2 was added to the nCS/A paste to generate an injectable scaffold. Based on the ratio of alginate, they were named nCS/15%A, nCS/10%A, and nCS/5%A. All operations were performed at 4°C.
MSCs mixed in nCS/A paste (nCS/15%A, nCS/10%A, and nCS/5%A) were cultured in a 48-well plate for 24h and then fixed for scanning electron microscopic (SEM) analysis (See the Supplementary Materials and Methods).
Injectability was determined as the mass of the paste extruded from the syringe divided by the total mass before injecting.52,53 Each test was performed five times, and the average value was calculated. Please see the Supplementary Materials and Methods for details.
The nCS/15%A, nCS/10%A, and nCS/5%A pastes were, respectively, placed in 3×4×25mm molds; clamped between two glass slides54; then set in a humidor at 37°C for 4h; and demolded and immersed in culture media (Modified Eagle's Medium alpha with 10% fetal bovine serum, 1×penicillin/streptomycin) at 37°C for 20h before testing. A standard three-point flexural test (ASTM F 417-78) was used to fracture the specimens at a crosshead speed of 1mm/min on a computer-controlled Universal Testing Machine (model 5500R). The flexural strength was calculated by S=3La/(2bh2), where L is the maximum load on the load-displacement curve, a is the span, b is the specimen width, and h is the specimen thickness.55,56
The cell viability was assayed using MTS cell viability assay kit (Promega). Briefly, the cultured MSCs were randomly divided into three groups: nCS seeding group: MSCs were seeded on an nCS/10%A scaffold; nCS mixture group: MSCs were mixed with nCS/10%A paste; and plate group: MSCs were directly plated in a 96-well plate. There were five wells for each time point and each group. The cells in each group were then induced with OS medium (culture media supplemented with 50μg/mL ascorbic acid, 10−8 M dexamethasone, and 10mM sodium β-gylcerol-phosphate) for 24, 48, and 72h, respectively, and then, the cell viability at different time points was analyzed by using the MTS cell viability assay kit. Briefly, 20μL MTS assay solution was added to the cultured cells with 100μL culture media, and incubated at 37°C for 3h. Then, the supernatants were transferred in a 96-well microtiter plate for measuring the OD value at 490nm using a microplate reader.
MSCs were infected with Ad-lacZ or Ad-BMP2 for 24h. Then, the cells were seeded on or mixed with nCS/10%A paste and induced with OS media for 7 days. Alkaline phosphatase (ALP) activity was determined by using an ALP assay kit in keeping with the manufacturer's instructions (Sigma). ALP activity was normalized with the value of DNA content and expressed as nmol of p-nitrophenol produced per minute per milligram of total DNA.58 DNA concentration was measured according to the method of Schneider et al.59
See the Supplementary Materials and Methods.
Twenty-four male Sprague Dawley (SD) rats at 8 weeks old were used in this study. The in vivo experimental protocol was reviewed and approved by the University at Buffalo Animal Care and Use Committee. Please see the Supplementary Materials and Methods for general anesthesia, surgery, and postoperational care procedures. The animals were divided into four groups: group 1, blank control; group 2, nCS/A; group 3, nCS/A+MSC (nCA/A+M); and group 4 nCS/A+BMP2-gene-modified MSC (nCS/A+M/B2). At the end of the 7-week period, the animals were euthanized using CO2, and all implants were harvested for a further analysis.
Bone density measurements (BMD, g/cm2) of all implants from the rats (six rats per group) were performed using a LUNAR PIXImus bone densitometer. LUNAR PIXImus software was used to analyze the scanned data. On the computerized scan plots, five regions of interest per implant were selected to measure the BMD of the defect area, and the average values were taken as the final result per implant. This allowed BMD measurement in close relation to the bone regeneration area by excluding pixels by the software. For histological analysis, half specimens (half implant) per group were decalcified and cut into 5μm sections. The sections were then stained with hematoxylin and eosin. The ratio of the bone area in the implants against the total implant tissue of section was quantified using NIH Image J software and defined as the percentage of bone volume in the implant/total volume of the implant. The other half specimens were used for ALP activity analysis as previously described.
Paraffin-embedded decalcified bone sections were processed for immunohistochemistry staining for Von Willebrand factor (vWF).60 Primary antibody (goat vWF antibody) was diluted 1:300 (Abcam), and secondary rabbit anti-goat antibody conjugated to horseradish peroxidase was diluted 1:500 in 1% bovine serum albumin. Blood vessels, indicated by vWF staining, were counted manually at 10×magnification in the total implant area and normalized to the implant area with the use of Image J software.
Statistical analysis was performed using SPSS-17.0 software. Where indicated, experimental data were reported as mean±standard deviation of triplicate independent samples. Data were analyzed using Student's t-test and one-way analysis of variance, and Tukey's HSD test was applied as a post hoc test if statistical significance was determined. A value of p≤0.05 was considered statistically significant.
A number of surface proteins have been used to enrich rat MSCs, including CD29, CD44, CD90, CD73, CD105, CD271, and Stro-I.61,62 In our study, we used CD44 and CD90 as positive markers to enrich MSCs. The hematopoietic stem cells (HSC) marker CD34 and endothelial progenitor cell (EPC) marker CD31 was used to confirm that the MSCs were depleted of HSCs and EPCs.63 As shown in Figure 1A, more than 96% of the cells expressed CD90 (96.2%) and CD44 (97%). In contrast, there were scarcely CD31-positive endothelial cells (4.5%) or CD34-positive immature hematopoietic cells (7.7%). Immunostaining results showed that MSCs were positive for CD44 and CD90 (Fig. 1B). In addition, MSCs could be successfully differentiated into three cell lineages—osteoblasts, chondrocytes, and adipocytes (Fig. 1C).
Dissolution tests showed that the integrity of nCS/A scaffolds with 50% and 30% alginate was completely lost after 48h, nCS/15%A partially maintained their shape, but nCS/10%A and nCS/5%A completely maintained their shape (Supplementary Fig. S1A). Therefore, we chose nCS/5%A, nCS/10%A, and nCS/15%A for further studies. Injectability analysis showed that all three kinds of pastes were readily extruded at relatively small injection forces. Compared with nCS alone, the injection forces for nCS with alginate were higher in an alginate dose-dependent pattern (p<0.05) (Fig. 2A). Mechanical property tests showed an increase in strength for all loadings of nCS with different ratios of alginate relative to nCS alone (p<0.05) (Fig. 2B). We found that the MSCs cell viability in nCS/10%A was better than nCS/5%A and nCS/15%A (see Supplementary Fig. S1B). Moreover, SEM analysis showed that the average pore diameter in the nCS/10%A scaffold was 70–80μm (Fig. 2C, D), and the cells attached on the nCS/10%A scaffold (Fig. 2E). Combining these observations, we selected nCS/10%A as an optimal concentration for further experiments.
To determine whether mixing MSCs with injectable nCS/A paste affects MSCs viability and proliferation, an MTS cell viability assay was performed in three groups—seeding, mixing, and plating. The results showed no significant differences in cell viability among three groups, indicating that mixing MSCs with injectable nCS/A paste does not affect MSCs viability and proliferation, and, hence, nCS/10%A paste is likely not toxic (Fig. 3A). To investigate the safety of Ad-BMP2 to the MSCs, cell viability and mineralization were analyzed by using different titers of Ad-BMP2 to infect cells. The results showed that the cells infected with the multiplicity of infection (MOI) 100 and 50 showed normal cell growth and stronger cell mineralization compared with other groups, indicating that Ad-BMP2 at MOI 100 and 50 had no toxicity to the cells (see Supplementary Fig. S2A, B). To trace the expression level of BMP2 in BMP2 gene-modified MSCs, the BMP2 levels in the culture media were measured by ELISA Kit. The results showed that the BMP2 level reached a peak at day 4, then slowly decreased over 14 days, and finally rapidly dropped down to the control level (Fig. 3B) at day 21. At day 7 after OS media induction, ALP activity in the BMP2-gene-modified MSCs group (nCS/A+M/B2) was about 2.4-fold higher than that in MSCs group (nCS/A+M) (Fig. 3C). Moreover, quantitative reverse transcriptase–polymerase chain reaction showed that osteocalcin (OCN), type I collagen (Col I), BMP2, and vascular endothelial growth factor (VEGF) gene expression dramatically increased in the nCS/A+M/B2 group compared with that in the nCS/A+M group (Fig. 3D). These data indicate that BMP2 is a strong enhancer for bone regeneration mediated by the injectable nCS/A with MSCs construct.
To evaluate the potential of the construct of injectable nCS delivery system and BMP2 gene-modified MSCs for bone regeneration in vivo, an 8-mm defect was created in the calvarial bones of SD rats. At 7 weeks after implantation, Faxitron x-ray (Fig. 4A) results showed that the BMP2-gene-modified MSCs group (nCS/A+M/B2) exhibited nearly complete closure of bony defects with much more newly formed bone with normal BMD compared with other groups. AdLacZ-transduced MSCs group (nCS/A+M) also showed more area with higher BMD than the blank control and nCS/A groups. nCS/A group showed a small amount of new bone, but had no normal BMD area (p<0.05). A quantitative analysis of BMD (Fig. 4F) showed that the BMD in the nCS/A+M/B2 group was significantly higher than that in the other groups. Without BMP2 gene transduction, the BMD in nCS/M was also significantly higher than that in nCS/A and the control (blank) groups; however, it was much lower than that in the nCS/A + M/B2 group. Notably, the nCS/A group also showed significantly higher BMD compared with the blank group. Consistent with the x-ray BMD result, histological analysis (Fig. 4B–E, B′-E′) showed that there was a larger amount of new bone formed in nCS/A+M/B2 and nCS/A+M groups (Fig. 4D, D′ E, E′). Compared with the nCS/A+M group, which induced partial bone defect healing, the nCS/A+M/B2 group exhibited robust OS activity, with complete coverage of defects with newly formed bone in most samples. In addition, there were also small regions of osteoid matrix within the interior of the implants in the nCS/A group (Fig. 4C, C′) relative to the blank control (Fig. 4B, B′). These results indicate that nCS/A paste can stimulate new bone formation. Furthermore, a histomorphometric analysis of histological slides also showed a significantly larger bone area within the nCS/A+M/B2 implant when compared with the other three groups (Fig. 4G).
vWF is a glycoprotein that is synthesized in endothelial cells and megakaryocytes and presents in large quantities in subendothelial matrices such as vessel basement membranes.64 Due to this, vWF has been considered a useful marker for detecting blood vessels by immunohistochemistry.65 To determine the effects of injectable nCS/A delivery system with BMP2-gene-modified MSCs on blood vessel ingrowth in a bone defect model, the densities of blood vessels present in the nCS/A+M/B2 and nCS/A+M groups were measured by histological sections staining for vWF. The results showed that nCS/A+M/B2 implant areas displayed a higher density of blood vessels interspersed throughout the implant region compared with that in the nCS/A+M implant region (Fig. 5A). Quantification of blood vessel area throughout the total implant area confirmed that nCS/A+M/B2 implants had a significantly higher blood vessel density than nCS/A+M (Fig. 5B). The results just cited indicate that BMP2-gene-modified MSCs in nCS/A paste can induce angiogenesis and lead to more bone regeneration within the defect area.
To improve healing of critical-sized defects, to date, a major barrier is the lack of sufficient integration of biomaterial design and engineered cells such as stem cells to promote bone regeneration. Although many studies use MSCs and scaffolds of calcium-based minerals,66–68 this was the first that evaluated the combination of BMP2-gene-modified MSCs with an injectable and porous nCS/A paste. The results of this study demonstrated the importance and efficiency of this injectable system in bone regeneration, and highlighted the potential utility of this construct for bone repair and regeneration.
In previous studies, beta-tricalcium phosphate and hydroxyapatite composites were used as bone repair materials for delivering MSCs or growth factors, and have been proved to have good OS characteristics.69,70 However, these delivery constructs lack good plasticity, and the cellular implantation procedure is complicated due to problems such as brittleness, poor mold ability, and inappropriate rate of biodegradability for the respective cells to multiply.25,71 Recently, Yamada et al.72 used a combination of platelet-rich plasma as an injectable scaffold with MSCs to increase osteogenesis and found a progressive, complete resorption of the scaffold and enhanced new bone formation. However, similar to injectable hydrogel and polymer carriers, one downside to this scaffold is that the inadequate mechanical strength easily causes the deformation under load, which restricts its application for the critical-sized bone defect, especially for the craniofacial bone defect.72 Compared with those materials and/or scaffolds, the hemihydrate of CS is a highly biocompatible, osteoconductive, and biodegradable material that is one of the simplest synthetic bone-like fillers17,73 and injectable paste material.14–16 In this study, by extending the work presented in Park et al.,23 we combined nCS and alginate and developed a novel injectable and porous nCS/A system. We used nCS as a base carrier to increase surface area for stem cells and soft tissue attachment, and used alginate to produce pores and adjust the strength of the paste. Our results showed that the presence of alginate increased the strength of the nCS material, but did not significantly affect the cell viability. Consistent with this finding, Bron et al.74 also found that the concentration of alginate in the range used here provides higher stiffness in the scaffolds, but does not affect cell viability. Although the most commonly-used concentration of alginate for drug and cell delivery is between 1% and 3% (m/v%),75,76 in tissue-engineering application, more and more studies have used higher concentrations to increase mechanical strength and generate pores by using different strategies, and found that higher concentrations of alginate do not affect cell viability.74,77,78 Both the in vivo and in vitro results presented here demonstrate that the nCS/10%A composition not only is biocompatible and has proper biodegradability, but also promotes OS differentiation of stem cells without decreasing cell viability.
Previous studies have shown that bone ingrowth into porous systems with different pore sizes and the diameter of interconnecting pores determine the quality of tissue growing into the porosity space.79–82 The most optimal pore size for mineralized bone ingrowth still seems to be a controversial topic. For example, Hulbert et al.83 concluded that the interconnections of the porosity should be larger than 100μm for regenerating mineralized bone. In contrast, Bobyn et al.84 found that effective bone ingrowth into porous space can happen in the scaffold with pore sizes down to 50μm, whereas the Itala group79 showed that there is no threshold value for new bone ingrowth in pore sizes ranging from 50 to 125μm under nonload-bearing conditions. Our results showed that the average pore diameter of micro-pores generated in the nCS/10%A injectable was 70–80μm. Our in vitro and in vivo studies further showed that 70–80μm of nCS/10%A could lead to effective cell proliferation and bone ingrowth, suggesting that an nCS/10%A scaffold with 70–80μm pore size is suitable for bone ingrowth.
BMPs are potent morphogens with a strong OS potential.85 rhBMP2 has obtained U.S. Food and Drug Administration approval for human applications to stimulate spinal fusion and repair nonunion long bone defects.86–88 However, these trials demonstrated some disadvantages such as difficulty in retaining BMPs in a biomaterial matrix, high BMP loading requirements, and high cost.89 MSCs that are genetically engineered to express specific growth factors have unique advantages for promoting bone regeneration due to their relatively stable expression of growth factors and them being less expensive than using the recombinant proteins.90,91 In this study, by injecting nCS/10%A paste mixed with BMP2-gene-modified MSCs (nCS/A+M/B2) into well-established critical-sized rat calvarial bone defects,92 we found that the BMD was much higher than that in other groups and exhibited nearly complete closure of bony defects in a short time (7 weeks). Histological analysis complemented the BMD result. All defects in this group were almost covered with mineralized bone tissue. These results demonstrated that injectable nCS/A paste is a biodegradable and biocompatible scaffold, and genetically engineered expression of BMP2 in MSCs in nCS/10%A paste can provide an even more effective approach for repair of a critical-sized bone defect.93 Notably, the critical-sized defects were repaired much better in the MSCs-containing groups compared with the group without MSCs (see Fig. 5), and exhibited no sign of rejection in all groups, indicating that at least most of the implanted allogeneic MSCs maintained their viability and had no apparent immunorejection of the host. This conclusion was supported by some previous findings. For example, Li et al.94 found that there is no immunological rejection and graft versus host disease by intravenously injecting green fluorescent protein-labeled allogeneic MSCs into rabbits. Saito et al.95 found that the rats have immunological tolerance to mouse MSCs. Devine et al.96 reported that human MSCs persist after infusion in utero to fetal sheep. Inoue et al.97 found that MSCs express very low levels of immunogenic class Ia and II molecules from the major histocompatibility complex and that MSCs lack immunogenic antigens. In addition, the results of this study support the concept that BMP2 can enhance angiogenesis and bone regeneration.98,99 Localized and sustained BMP2 delivery from MSCs significantly increased the expression of osteoblast marker genes and VEGF and promoted blood-vessel density and bone formation in the bone defect area. Hence, the effects of BMP2 delivery in MSCs observed in this study corroborate the previous work that highlights the importance of BMP2 and MSCs in angiogenesis and bone healing.
In conclusion, this study provides the first evidence of support that this novel injectable nCS/A paste can stimulate bone formation and is an efficient vehicle for stem cells to promote new bone formation. The combination of the nCS/A paste with BMP2-gene-modified MSCs can dramatically enhance new bone formation and angiogenesis, and lead to a nearly complete repair of critical-sized calvarial bone defects. On the basis of the data presented here, it appears that this system can be useful not only in critical-sized bone defect, but also in the filling of defects with limited accessibility or narrow cavities such as in periodontal bone repair. Its use in minimally invasive techniques, such as in situ fracture fixation and percutaneous vertebroplasty to fill the lesions and strengthen osteoporotic bone, is another area to further pursuit.
The authors thank David Hadbawnik for a critical reading of the article, and Dr. Wade J. Sigurdson, the director of the Flow Cytometry Facility at the School of Medicine and Biomedical Sciences, University at Buffalo, for assistance with the flow cytometry assay. They thank Dr. Neoyuli Hanaki for technical assistance with making a critical-sized calvarial bone defect model. This work was supported by a National Institute of Health grants AR055678 (S. Yang) and AR061052 (S. Yang).
No competing financial interests exist.