Fabrication of gelatin methacrylate/nanohydroxyapatite microgel arrays for periodontal tissue regeneration
Authors Chen X, Bai S, Li B, Liu H, Wu G, Liu S, Zhao Y
Received 29 April 2016
Accepted for publication 10 June 2016
Published 14 September 2016 Volume 2016:11 Pages 4707—4718
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Dr Lei Yang
Xi Chen,1 Shizhu Bai,1 Bei Li,2 Huan Liu,1 Guofeng Wu,1 Sha Liu,3 Yimin Zhao1
1State Key Laboratory of Military Stomatology and National Clinical Research Center for Oral Diseases, Shaanxi Key Laboratory of Oral Diseases, Department of Prosthodontics, 2State Key Laboratory of Military Stomatology and National Clinical Research Center for Oral Diseases, Shaanxi Key Laboratory of Oral Diseases, Center for Tissue Engineering, School of Stomatology, 3Department of Plastic and Reconstructive Surgery, Xijing Hospital, The Fourth Military Medical University, Shaanxi, People’s Republic of China
Introduction: Periodontitis is a chronic infectious disease and is the major cause of tooth loss and other oral health issues around the world. Periodontal tissue regeneration has therefore always been the ultimate goal of dentists and researchers. Existing fabrication methods mainly focused on a top–down tissue engineering strategy in which several drawbacks remain, including low throughput and limited diffusion properties resulting from a large sample size. Gelatin methacrylate (GelMA) is a kind of photocrosslinkable and biocompatible hydrogel, with the capacities of enabling cell encapsulation and regeneration of functional tissues. Here, we developed a novel method to fabricate GelMA/nanohydroxylapatite (nHA) microgel arrays using a photocrosslinkable strategy. The viability, proliferation, and osteogenic differentiation and in vivo osteogenesis of human periodontal ligament stem cells (hPDLSCs) encapsulated in microgels were evaluated. The results suggested that such microgels provide great potential for periodontal tissue repair and regeneration.
Methods: Microgel arrays were fabricated by blending different weight ratios of GelMA and nHA. hPDLSCs were encapsulated in GelMA/nHA microgels of various ratios for a systematic evaluation of cell viability, proliferation, and osteogenic differentiation. In vivo osteogenesis in nude mice was also studied.
Results: The GelMA/nHA microgels exhibited appropriate microarchitecture, mechanical strength, and surface roughness, thus enabling cell adhesion and proliferation. Additionally, the GelMA/nHA microgels (10%/2% w/v) enhanced the osteogenic differentiation of hPDLSCs by elevating the expression levels of osteogenic biomarker genes, such as ALP, BSP, OCN, and RUNX2. In vivo ectopic transplantation results showed that GelMA/nHA microgels (10%/2% w/v) increased mineralized tissue formation with abundant vascularization, compared with the 1%, 3%, and the pure GelMA group.
Conclusion: The GelMA/nHA microgels (10%/2% w/v) facilitated hPDLSCs viability, proliferation, and osteogenic differentiation in vitro and further promoted new bone formation in vivo, suggesting that the GelMA/nHA microgels (10%/2% w/v) provide great potential for periodontal tissue regeneration.
Keywords: periodontal ligament stem cells, gelatin methacrylate, nanohydroxyapatite, microgel array, differentiation, periodontal tissue regeneration
Periodontitis is an infectious disease involving multiple degenerative and inflammatory states of periodontal supporting structures (ie, alveolar bone, periodontal ligaments [PDLs], and cementum) and is the major cause of tooth loss and oral health issues in the world.1 According to the World Health Report in 2013, the total proportion of periodontal patients in USA and People’s Republic of China reached 60% and 90%, respectively.2 For seriously damaged or missing periodontal supporting structures, traditional treatment procedures (eg, scaling and root planning, open flap debridement, and injectable drug delivery) can hardly be used for reconstruction owing to the large size of the damaged area and the limited regeneration capacity of such tissues.3 The periodontal tissue engineering strategy has emerged as a series of temporal and spatial sequential procedures that enhance periodontal regeneration and is, therefore, important to meet the transplantation and implantation demand in certain clinical therapies.4–7
For existing tissue engineering strategies, cells are seeded onto a biocompatible scaffold and expected to populate in the scaffold and remodel the local microenvironment by secreting their own extracellular matrix (ECM).7,8 Several kinds of scaffolds have been successfully developed for periodontal tissue regeneration. For example, collagen scaffolds with varying porosities (40%~90%) have been used for PDL repair and regeneration.9 The results suggested that scaffolds with porosity higher than 80% successfully formed PDL-like tissues after 2 weeks of culture. Chitosan scaffolds combined with PDL stem cells (PDLSCs) have also been applied for improvement of osteogenic differentiation and generation of alveolar bone-like structures in vitro.10 Despite several thin or avascular tissues, such as skin, bladder, and cartilage, having been successfully engineered through the top–down approach, the fabrication of complex functional tissues with high cell densities and high metabolic requirements still has challenges. This is because the sample is commonly engineered at centimeter levels, which may affect cell functions as a result of limited diffusion properties of nutrients and oxygen, and therefore it can hardly sustain a long-term culture in vitro. In addition, the existing fabrication method is low throughput and the utilized natural scaffolds can hardly meet the sufficient mechanical strength of in vivo periodontal tissues, especially for alveolar bone and PDL regeneration. Thus, it is important to develop novel fabrication strategies and microscale biomaterials with tunable mechanical properties for periodontal tissue engineering in vitro.
Hydrogels have emerged as a kind of soft material with three-dimensional (3D) polymer network, water-absorbability, and tunable properties (eg, physical, chemical, and biocompatible) and have been found to have widespread use in biomedical applications such as tissue regeneration and drug delivery systems. Recently, both natural and synthetic hydrogels composed of micro-/nanostructures (eg, pores and fibrous structure) have been developed to mimic the chemical and physical properties of natural ECM, and these have further been used for periodontal tissue repair and regeneration. For instance, chitosan hydrogels combined with β-glycerophosphate have been utilized for the improvement of osteogenic differentiation and generation of alveolar bone-like tissue constructs after 2 weeks of culture.11 Polyethylene glycol hydrogels that contain cell adhesive RGD sequences have also been used for treating dentoalveolar defects.12 Although such hydrogels were regarded as biocompatible and biodegradable biomaterials for reconstructing periodontium-like tissues, several issues still remain. For example, the currently used large scale (eg, centimeter level) sample size of these hydrogels will limit the diffusion of nutrients and oxygen. Another issue is that the existing method lacks satisfactory revascularization abilities, which is a key requirement for the engineering of functional 3D tissue constructs such as bone, muscle, heart, and liver.13,14
Gelatin methacrylate (GelMA) is gelatin modified by methacryloyl (methacrylamide and methacrylate) side groups that has been recently developed for mimicking 3D cell microenvironment and generating 3D functional tissue constructs due to their biocompatibility, photocrosslinkable ability, and mechanical tunability to a reasonable extent.15,16 It is worth mentioning that the GelMA hydrogel is easy to be microfabricated through photopatterning, micromolding, self-assembly, and bioprinting strategies.15 GelMA hydrogel has also been successfully utilized in several studies for the development of vascular networks in 3D microenvironments. For instance, GelMA hydrogels provided a favorable microenvironment for human umbilical vein endothelial cells to form a confluent monolayer and for MC3T3 cells to differentiate into osteogenic cells.17 A hybrid biomaterial based on GelMA and gold nanoparticles has also been used to regenerate bone tissues in vitro.18 GelMA hydrogel is therefore appropriate for constructing functional tissues in vitro. Herein, we describe a simple, facile, and high-throughput method to fabricate GelMA/nanohydroxylapatite (nHA) microgel arrays. The microstructure and mechanical properties of GelMA/nHA microgels have been characterized. In vitro and in vivo experiments were conducted to test the viability, proliferation, and osteogenic differentiation of human PDLSCs (hPDLSCs) encapsulated in GelMA/nHA microgels and further evaluate their potential applications to repair damaged alveolar bone. A key enabling feature of this method is the high throughput and simplicity of the fabrication process of such functional microgels, which hold great potential for periodontal tissue regeneration applications.
Material and methods
Type A porcine skin gelatin powder and methacrylic anhydride were obtained from Sigma-Aldrich Co. (St Louis, MO, USA). Acicular nHA with purity >99.0% was obtained from Emperor Nano Material Co. (Nanjing, People’s Republic of China). A dialysis tubing with a cutoff point of 12–14 kDa was obtained from Spectrum Labs (Rancho Dominguez, CA, USA). Irgacure 2959 photocrosslinker was obtained from CIBA Chemicals (Basel, Switzerland). 3-(Trimethoxysilyl) propyl methacrylate (TMSPMA) was purchased from Sigma-Aldrich Co. Printed photomasks were purchased from Qingyi Co. (Shenzhen, People’s Republic of China). Polymethyl methacrylate was purchased from Guangyu Co. (Hangzhou, People’s Republic of China). Live/Dead viability/cytotoxicity kit was purchased from Thermo Scientific Co. (Rockford, IL, USA). 3-(4,5-Dimethylthiazol-2-yl)-2,5-diphenyl tetrazolium bromide (MTT) assay and 5-bromo-2-deoxyUridine (Brdu) was obtained from Sigma-Aldrich Co. Anti-BrdU antibody and AlexaFluor488-conjugated AffiniPure Goat Anti-Human IgG was obtained from Abcam (Cambridge, UK). Alizarin Red S, β-glyceraldehyde-3-phosphate, L-ascorbic acid, dexamethasone, and paraformaldehyde were purchased from Sigma-Aldrich Co.
Synthesis of GelMA
GelMA, a biocompatible and biodegradable hydrogel that is effective for 3D cell encapsulation, was synthesized as described previously.19 Briefly, gelatin powder was added to phosphate-buffered saline (PBS) solution at a temperature of 65°C and stirred until fully dissolved at 10% w/v. Gelatin powder was added to PBS solution at a temperature of 65°C and stirred until fully dissolved at 10% w/v. Methacrylic anhydride was added to this solution at a rate of 0.8 mL/minute while stirring at 45°C until the target volume was reached. The mixture was then dialyzed against distilled water at 40°C for 2 weeks using the cutoff dialysis tubing. The water was changed every day to remove salts and methacrylic acid (Figure 1B). Then, the GelMA solution was lyophilized and stored at −80°C for future use.
Fabrication of GelMA/nHA microgel arrays
GelMA solution (5% and 10% w/v) was mixed with nHA of varying concentration (1%, 2%, and 3% w/v) and Irgacure2959 (0.5% w/v), and the composite solution was added in a polymethyl methacrylate mold. Designed photomasks composed of circle arrays with a diameter of 1 mm were used here. A TMSPMA-treated glass slide with a pre-patterned photomask labeled on it was also covered on the mold and exposed to 2.9 mW/cm2 ultraviolet (UV) light (365 nm) for 30 seconds (Figure 1A).
Degradability of GelMA hydrogels
To evaluate the degradability of cell-laden GelMA hydrogels, we prepared the GelMA sample encapsulated with cells at density of 1×106 cells/mL. The degradability profile of GelMA was obtained by calculating the volume of the hydrogel sample with increasing culturing time.
Scanning electron microscopy
GelMA/nHA hydrogel arrays were left to swell in deionized water overnight, followed by freezing in liquid nitrogen. Then, the frozen hydrogel was lyophilized overnight using a Thermo Scientific freeze dryer. Lyophilized samples were sputter-coated with iridium and imaged with a scanning electron microscope (SEM) (S-4800; Hitachi, Tokyo, Japan).
Mechanical testing of GelMA/nHA microgels
GelMA/nHA microgels were detached from the slide and tested at a rate of 15% strain/minute on a Bose 3200 mechanical tester. The Young’s modulus was determined as the slope of the linear region corresponding with 10% strain.
hPDLSCs were primarily isolated from one human normal third molar extracted for orthodontic reasons, and single cell-derived colonies were obtained by the limiting dilution technique (P0) based on previous reports.20,21 Written informed consent was obtained from the patient for use of the tissue. hPDLSCs at passage P2–P6 were used in all the following experiments. Briefly, hPDLSCs were trypsinized and resuspended in GelMA hydrogel precursor composed of 0.5% w/v photoinitiator at a concentration of 1×106 cells/mL.16 Microgel units were fabricated by exposing to 2.9 mW/cm2 UV light (365 nm) for 30 seconds on TMSPMA-treated glass slides. The glass slides containing microgels were washed with PBS and incubated in culture medium under standard culture conditions. The culture medium was changed every 2 days.
Viability and proliferation of hPDLSCs in GelMA/nHA microgels
The viability of hPDLCs encapsulated in GelMA/nHA microgels was evaluated by Live/Dead staining and MTT assay. For Live/Dead staining, 2 mM ethidium homodimer-1 and 0.5 mM calcein AM were added to the cell-laden microgels in Hank’s balanced salt solution for 15–20 minutes. The samples were then imaged using an Olympus IX81 microscope (Tokyo, Japan). MTT assay was also used for quantifying cell viability in GelMA/nHA microgels. The proliferation of hPDLSCs was tested through BrdU incorporation. Briefly, 10 μg/mL BrdU was added to the culture medium and incubated for 12 hours. After washing with Dulbecco’s phosphate-buffered saline (DPBS) three times, cells were fixed in 4% polyformaldehyde for 10 minutes. Then, cells were sequentially incubated in anti-BrdU antibody (1:1,000) and AlexaFluor488-conjugated Anti-human IgG (1:500). Positive proliferated cells were quantified using fluorescence microscopy.
In vitro osteogenic differentiation of hPDLSCs and Alizarin Red staining
hPDLSCs-laden GelMA/nHA microgel arrays at a concentration of 1×106 cells/mL were incubated in osteogenic media (alpha-minimum essential medium supplemented with 10% fetal bovine serum, 10 mM b-glyceraldehyde-3-phosphate, 60 mg/mL L-ascorbic acid, and 10 nM dexamethasone) as previously described.22,23 The media were changed twice a week, and 4 weeks later, the GelMA/nHA microgel arrays were washed twice with DPBS followed by fixation using 4% paraformaldehyde for 30 minutes. Then, the cell-laden microgels were incubated in 0.2% Alizarin Red S stain for 15 minutes. Images were acquired by SEM using an Olympus IX81 microscope.
Real-time polymerase chain reaction
Total RNA extraction was performed on hPDLSCs using TRIzol reagent (Invitrogen Life Technology, Carlsbad, CA, USA), and first-strand cDNA syntheses were performed according to the manufacturer’s protocol. Reverse transcription was performed using the PrimeScript real-time polymerase chain reaction (RT-PCR) kit (Thermo Scientific) followed by semiquantitative RT-PCR using specific primers. The primer sequences of alkaline phosphatase (ALP), bone sialoprotein (BSP), osteocalcin (OCN), and runt-related transcription factor 2 (RUNX2) are shown in Table 1. The expression of the target genes was normalized against the β-actin. RT-PCR was performed using the 7500 Fast Real-Time PCR System (Life Technologies, Inc., Waltham, MA, USA).
Table 1 Specific primer sequences used for RT-PCR analysis
In vivo implantation
Thirty-two 4–6 week male BALB/c-nu/nu mice were purchased from the Fourth Military Medical University Animal Center and housed in a pathogen-free environment (24°C and a 12 h/12 h light-dark cycle). The animals were provided with purified water and food ad libitum, and were allowed to acclimatize to local vivarium conditions for at least one week. All animal procedures were performed in accordance to the criteria outlined in the Guide for the Care and Use of Laboratory Animals prepared by the National Academy of Sciences.24 The study was approved by the Institutional Review Board of the Fourth Military Medical University School of Stomatology. The nude mice were anesthetized with 2% inhaled isoflurane and ventilated using a rodent mechanical ventilator, and microgels containing 10% w/v GelMA and different concentrations of nHA nanoparticles (0%–3% w/v) laden with osteoinductive pretreated hPDLSCs at P3 (for 1 week) were transplanted subcutaneously into the dorsal regions of the nude mice. Each group (10% w/v GelMA with 0%, 1%, 2%, and 3% w/v nHA) consisted of eight-cell material implants. Incisions were closed using 5-0 silk threads (Jinhua Medical Supplies Co., Shanghai, People’s Republic of China). Animals were sacrificed 8 weeks later, and the implants were rinsed with DPBS several times followed by fixation for subsequent analysis.
Histological evaluation and SEM of the implants
To evaluate new bone formation 8 weeks after in vivo transplantation, histological examinations (including hematoxylin and eosin [HE] and Masson’s trichrome staining) and SEM analysis of the implants were carried out. Briefly, for histological examinations, implants were harvested, fixed with 4% paraformaldehyde, and decalcified in 10% ethylenediaminetetraacetic acid solution at room temperature for 2–3 weeks. Then, the samples were sliced into 5 mm-thick paraffin-embedded sections and stained with HE or Masson’s trichrome stains.25 Histological analyses were performed using an Olympus IX81 microscope. For SEM analysis of the implants, similar procedures were performed as described earlier.
All statistical analyses were performed with one-way analysis of variance with Tukey’s post hoc test or paired t-test accordingly using the GraphPad Prism software (San Diego, CA, USA). Each datum was expressed as mean ± standard error of mean of at least three independent experiments (n≥3). A P-value <0.05 was accepted as statistically significant.
Characterization of GelMA/nHA microgels
GelMA/nHA microgel arrays were fabricated through a photolithography strategy. GelMA hydrogel precursor mixed with nHA nanoparticles were polymerized by exposing to UV light (Figure 1A). Here, addition of methacrylate groups to the amine-containing side groups of gelatin can be utilized to make it photocrosslinkable to a hydrogel (Figure 1B). The shape of the hydrogel can be regulated through a designed photomask (diameter 1,000 μm). Moreover, GelMA is the hydrolysis product of collagen and contains lots of adhesive ligands (eg, arginine–glycine–aspartic acid sequences) that promote cell adhesion. The morphology of GelMA/nHA microgel arrays was well identified by encapsulating fluorescein isothiocyanate-fluorescent beads in microgels (Figure 1C). The microarchitecture of GelMA/nHA microgels was then characterized. SEM images indicated that the pore size of hydrogel decreased with increasing nHA fraction (Figure 2A and B). For the 5% w/v GelMA group, microgels exhibited a 3D interconnected pore structure, with pores of size 170±10 μm. The wall surface of micropores became rougher with increasing nHA fraction. The pore size decreased to 15±3.5 μm when GelMA microgels were modified by 3% w/v nHA. SEM images of the 10% w/v GelMA group suggested that the pore size of the microgel also decreased with increasing nHA fraction. The pore sizes were 108±11 μm and 20±2.3 μm for the 10% w/v GelMA group (control) and the 10%/2% w/v GelMA/nHA group, respectively. nHA nanoparticles significantly aggregated in the 10%/3% w/v GelMA/nHA microgels. We also assessed the biodegradable property of GelMA hydrogel encapsulated with hPDLSCs, which is important for cell growth, penetration, and remodeling of the local microenvironment (Figure S1).
The mechanical properties and swelling ratio of GelMA/nHA microgels were also tested. The results indicated that the stiffness of microgels was enhanced by increasing both monomer and nHA concentration (Figure 2C). For the control group, Young’s modulus was 20±1.5 kPa (5% w/v GelMA) and 35±2.3 kPa (10% w/v GelMA), respectively. The modulus can be significantly increased when mixed with nHA at a concentration of 3% w/v (46±3 kPa for 5% w/v GelMA and 98±5 kPa for 10% w/v GelMA). Interestingly, the swelling ratio of GelMA/nHA microgels was only related to GelMA monomer fraction (Figure 2D). There was no significant difference between groups with varying nHA concentrations. Here, 10% w/v GelMA microgel was selected for further studies because of its better mechanical properties, which can meet the mechanical properties of neonatal alveolar bone tissues.
Viability, proliferation, and osteodifferentiation of hPDLSCs in microgels
hPDLSCs were encapsulated in GelMA/nHA microgels and the viability of cells tested using both Live/Dead staining and MTT assay (Figure 3A and B). Fluorescent images indicated that the viability of cells in the 10% w/v GelMA groups after 24 hours encapsulation was not affected when nHA concentration was 1% w/v and 2% w/v. For the 3% w/v nHA group, the number of dead cells increased. Similarly, MTT assay results suggested that cell viability significantly decreased in the 3% w/v nHA group. However, cell viability increased with increasing culture time. Cell proliferation in GelMA/nHA microgels was also assessed through BrdU incorporation after 3 days of culture (Figure 3C). The results showed that cells significantly proliferated in the 2% nHA group compared to other groups, with a positive BrdU cell percent of 34%±4%. The positive cell percent in the 3% w/v nHA group was only 11%±2.5%. We then investigated the osteogenic differentiation potential of hPDLSCs encapsulated in GelMA/nHA microgels using Alizarin Red S staining (Figure 3D). The images suggested that hPDLSCs encapsulated in 2% nHA exhibited significant mineralization after 10 days of culture compared to microgels with other ratios. Additionally, we evaluated mineralization by analyzing the expression of osteogenic biomarkers including ALP, BSP, OCN, and RUNX2 through RT-PCR (Figure 3E). The results suggested that 2% w/v nHA encapsulation in 10% w/v GelMA microgels significantly enhanced the osteogenic differentiation of hPDLSCs after 14 days of culture.
In vivo osteogenesis
To evaluate the in vivo osteogenic potential, the preosteoinduced hPDLSC microgel composite materials were subcutaneously implanted into the backs of nude mice. During the 8 weeks of breeding, all the animals healed uneventfully, and there was no sign of complications or material exposure at the surgical sites. From the gross view of the implants, we found that all the implants integrated well with the subcutaneous tissue of the nude mice and that vascularization was detected in the control, 1%, and 2% w/v nHA groups (Figure 4A), and this was further verified by SEM images where red blood cells were found inside the microgels of the 2% w/v nHA (Figure 4B), suggesting that vascularization can be induced within GelMA/nHA microgels. The internal ultrastructure of the implants was demonstrated using SEM. In the control, 1%, and 2% nHA groups, hPDLSCs penetrated through connective fibers with or without nHA attached and encapsulated, thereby showing good spreading and attachment. However, cells were rarely seen in the 3% nHA group (Figure 4B). New periodontal tissue formation was investigated by HE and Masson’s trichrome staining (Figure 5A and B). Both HE and Masson’s histological staining results indicated that a certain amount of PDL-like tissue and blood vessels formed in the control, 1%, and 2% nHA groups. Mineralization can be obtained by increasing nHA fraction in microgels. For the 1% and 3% w/v nHA group, newly formed tissue constructs showed a lack of cell populations and ECM components such as collagen. This may be caused by the insufficient nHA fraction and stack porosity, as a result of limited space that inhibits cell growth and penetration. Uniform mineralization was seen in the 2% nHA group, and bone crypts with multinucleated cells (osteoclast-like cells) were initially generated.
Great efforts have been made to develop methods for tissue regeneration using 3D scaffolds.26 For periodontal tissue regeneration, existing studies have demonstrated that biocompatible scaffolds can promote hPDLSCs adhesion and proliferation.1,2,8 However, the fabrication process is low throughput, and the utilized natural scaffolds can hardly meet the sufficient mechanical strength of in vivo periodontal tissues.27,28 Additionally, the sample created using the existing method exhibited large sample size with limited diffusion properties, which may affect cell function and make it hard to achieve long-term culture.29,30 GelMA/nHA microgel arrays provide great potential for periodontal tissue regeneration with sufficient mechanical strength and can also allow for the generation of high-throughput microscale samples rapidly. The structural characterization results suggested that the pore size decreased with increasing GelMA and nHA fraction. nHA incorporation enhanced the topographical properties of the wall surface of interconnected pores, which may promote cell adhesion.31,32 Aggregation of nHA nanoparticles occurred when nHA fraction was larger than 2% w/v, which may significantly decrease the diffusion of nutrients in microgels and further inhibit cell viability. The mechanical properties of microgels can be enhanced by increasing nHA fraction, which may have resulted from the uniform distribution of nanoparticles in microgels, and the stability of 3D polymer network subsequently increased. The biocompatibility of GelMA/nHA microgels was also investigated. Cell viability, proliferation, and osteogenic differentiation were significantly decreased in the 3% w/v nHA group due to the compact pore structure of the microgels. The nHA fraction was optimized in both in vitro and in vivo experiments. In vivo studies indicated that both mineralization and vascularization occurred in the 10% w/v/2% w/v GelMA/nHA microgels. All these results suggested that the 10% w/v/2% w/v GelMA/nHA microgels meet the requirement for tensile strength in bone regeneration and enhanced in vivo new bone formation, compared with the pure 10% w/v GelMA microgels.
In this study, high-throughput and biocompatible GelMA/nHA microgel arrays were fabricated using a photolithography strategy. Taken together, the experimental results indicated that the microstructure and mechanical properties can be regulated by changing GelMA and nHA fraction. hPDLSCs encapsulated in GelMA/nHA microgels exhibited high viability, proliferation potential, and strong osteogenic differentiation ability in vitro. Additionally, GelMA/nHA microgels significantly enhanced new bone regeneration in nude mice, suggesting that such microgels hold great potential for periodontal tissue regeneration.
This work was financially supported by the National Natural Science Foundation of China grants (no 81271188 and no 81200823). The authors appreciate Prof Feng Xu and Doctor Yuhui Li from Bioinspired Engineering and Biomechanics Center (BEBC) of Xi’an Jiaotong University for their kind help.
YZ, SB, and XC designed the experiments. XC, BL, and HL performed the in vitro experiments. XC and SL performed the in vivo experiments. YZ and GW interpreted the results and revised the paper. XC wrote the main text of the manuscript. All authors contributed toward data analysis, drafting and revising the paper, and agreed to be accountable for all aspects of the work.
The authors report no conflicts of interest in this work.
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Figure S1 Evaluation of degradation profile of cell-laden GelMA hydrogels.
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