Healing of bone defects by induced pluripotent stem cell-derived bone marrow mesenchymal stem cells seeded on hydroxyapatite-zirconia.

BACKGROUND: Induced pluripotent stem cells (iPSCs) can generate bone marrow mesenchymal stem cells (BMSCs) as seed cells for tissue-engineered bone to repair bone defects. In this study, we investigated the effects of hydroxyapatite-zirconia (HA/ZrO2) composites combined with iPSC-derived BMSCs as a bone substitute on repairing skull defects in rats.
METHODS: Human urinary cells isolated from a healthy donor were reprogramed into iPSCs and then induced into BMSCs. Immunocytochemistry (IHC) and reverse transcription-polymerase chain reaction (RT-PCR) were used to examine the characteristics of the induced MSCs. The iPSC-derived BMSCs were cultured on HA/ZrO2 composites, and cytocompatibility of the composite was analyzed by cell counting kit-8 (CCK-8) assays, RT-PCR, and scanning electron microscopy. Then, HA/ZrO2 combined with iPSC-derived expanded potential stem cells (EpSCs) were transplanted onto skull defects of rats. The effects of this composite on bone repair were evaluated by IHC.
RESULTS: The results showed that MSCs induced from iPSCs displayed the phenotypes and property of normal BMSCs. After seeding on the HA/ZrO2, iPSC-derived BMSCs had the ability to proliferate and differentiate into osteoblasts. After transplantation, iPSC-derived BMSCs on HA/ZrO2 promoted construction of bone on rat skulls.
CONCLUSIONS: These results indicated that transplantation of a HA/ZrO2 combined with iPS-derived BMSCs is feasible to reconstruct bones and may be a substantial reference for iPSC-based therapy for bone defects. 2021 Annals of Translational Medicine. All rights reserved.

Introduction

Bone defect is the destruction of the integrity of bone, which can usually be repaired through physiological evolution in vivo. However, large bone defects caused by severe bone trauma, osteomyelitis, bone tumors, or congenital osteopathy cannot be repaired through the physiological function of the body. Autogenous bone transplantation is often used to treat bone defects expected to not heal spontaneously. However, the source of bone used for transplantation is limited, and autologous transplantation inevitably causes secondary trauma in the donor site, while increasing pain and the risk of infection.

The use of allogeneic bone can partly alleviate the problem of insufficient bone sources for transplantation; however, it carries the risk of disease transmission and immune rejection. Metal and ceramic bone substitutes have the advantages of high strength and wide resource, but they lack biological activity and are easily prone to aging and loosening (1). Bone tissue engineering provides a new option for bone defect treatment by implanting cultured cells into biocompatible scaffolds. Seed cells adhere to and proliferate on scaffolds, differentiate into osteoblasts, mineralize to form bone, and then fill in the bone defect.

Cells are essential for bone tissue engineering (2). At present, seed cells mainly include embryonic stem cells (ESCs), induced pluripotent stem cells (iPSCs), adult stem cells/mesenchymal stem cells (MSCs) and osteoblasts (3). Osteoblasts, as a direct source of bone regeneration, have excellent osteogenic properties; however, as terminal cells, they have limited proliferation ability and insufficient source, which restricts their application as seed cells. The ESCs are omnipotent stem cells with super self-renewal and differentiation ability, but ethical problems limit their clinical application. To date, MSCs are the most widely studied cells and have been used in clinic. They can be obtained from bone marrow, umbilical cord blood, fat, placenta, endothelium, and other tissues. They have strong proliferation and differentiation ability and low immunogenicity.

However, the acquisition of MSCs, such as BMSCs, requires bone marrow extraction, which often causes great pain to patients. The number of BMSCs is very small, with only one BMSC per 100,000 nucleated cells in bone marrow (4,5). Contrastingly, iPSCs are derived from reprogramming of somatic cells and have strong self-renewal, proliferation, and differentiation capabilities similar to ESCs. There are no ethical issues, but undifferentiated iPSCs are tumorigenic, which limits their clinical application (6). Differentiation of iPSCs into mesenchymal stem cell-like cells (iPS-MSCs) results in similar biological properties and functions as MSCs, but there is no influence of MSCs acquisition and individual differences, nor ethical issues of ESCs. As a new type of seed cell, iPS-MSCs have abundant sources, strong differentiation ability, and good consistency. By detecting and comparing the telomerase activity of iPS-MSCs and MSCs, it was found that the telomerase activity of iPS-MSCs was 10 times higher than that of MSCs, which indicated that iPS-MSCs had stronger proliferation ability. More importantly, oncogenic genes OCT4, TRA-1-81, and TRA-1-60 were not expressed in iPS-MSCs, and no tumors were found in tumorigenicity testing of iPS-MSCs, which further demonstrated the safety of iPS-MSCs.

In recent years, iPS-MSCs have provided breakthrough progress in the treatment of osteonecrosis and bone defects (7,8). However, there are few reports on the transplantation of IPS MSCs into HA/ZrO2 as tissue-engineered bone materials. In our previous studies, gradient composites of zirconia and hydroxyapatite (HA/ZrO2) have been shown to have a three-dimensional (3D) porous structure with good biocompatibility. Moreover, when combined with BMSCs, HA/ZrO2 showed a good therapeutic effect on Beagle canine bone defects.

Here, we differentiated urine cell-derived iPSCs into BMSCs, and cultured these cells on a HA/ZrO2 scaffold to form tissue-engineered bone that was then transplanted into the skull defect of rats. The effects of iPSC-derived MSCs on bone regeneration were then analyzed, and the feasibility of using iPSC-derived MSCs as seed cells to construct bone substitutes to repair bone defects were also assessed.

We present the following article in accordance with the ARRIVE reporting checklist (available at https://dx.doi.org/10.21037/atm-21-5402).

Methods

Generation and analysis of iPS-MSCs

Urine cells (UCs) were collected from a 24-year-old healthy male volunteer (after he had provided informed consent), and reprogrammed into iPSCs by introducing 4 exogenous transcription factors (OCT4, SOX2, C-MYC, KLF4) into human UCs using a retrovirus-mediated infection system. Briefly, we used calcium phosphate transfection to introduce 4 plasmids (OCT4, SOX2, C-MYC, and KLF4) into 393T cells, then respectively collected viral fluids for 48 h and 72 h. The UCs were infected twice with the addition of polybrene containing a final concentration of 8 μg/mL and changed to UC culture medium 12 h later. After 4–5 days of infection, the nucleocytoplasmic ratio became larger, and the cells were spread onto embryonic fibroblast (MEF) feeder cells and (2×105/10 cm dish) were replaced with human (h)ESCs medium (20% dermal fibroblast cells + knockout serum replacement (DFBs + KSR) medium). All of cultures were supplemented with 50 μg/mL each of vitamin C and 1 mM final concentration of valproic acid (VPA) until the clonogenic cells appeared. The clonal iPSCs were collected onto 6-well plates plated with an MEF-like layer or Matrigel, cultured with mTesR1 medium. The Culture medium was changed daily.

When iPSCs reached about 30% confluence, they were switched to MSCs induction medium including minimum essential medium a (aMEM; Sigma-Aldrich, St. Louis. MO, USA, M4526), 10% fetal bovine serum (FBS; Gibco, Amarillo, TX, USA), 2 mm glutamine (Sigma, G7513), 100 μm ascorbic acid (Wako, Richmond, VA, USA, 013-12061)1 mM sodium pyruvate (Sigma, s8636), nonessential amino acids (Gibco) and 4-(2-hydroxyethyl)-1-piperazineethanesulfonic acid (HEPES; Sigma), maintained in culture for 2 weeks with fluid changed every 3–4 days. After 2 weeks, cells were passaged by digestion with pancreatin replacement medium and passaged onto gelatin 0.1% (after which no plating was required), denoted as P1, and passaged continuously until more homogeneous mesenchymal-like cells emerged. Afterwards, culture was switched to mesenchymal stem cell medium (5% UltraGRO TM advanced + aMEM).

The BMSCs samples serving as controls were collected from patients with normal hip fracture at the Xiaoshan Hospital of Traditional Chinese Medicine. All procedures performed in this study involving human participants were in accordance with the Declaration of Helsinki (as revised in 2013). The study was approved by the Ethics Committee of Xiaoshan Hospital of Traditional Chinese Medicine (No. 2014396) and informed consent was taken from all the patients. Briefly, 5 mL of bone marrow was diluted 1:1 with phosphate-buffered saline (PBS). The bone marrow was dropped into a 50 mL centrifuge tube containing 10 mL Ficoll using a Pap pipette, 1,800 rpm, 25 °C, for 18 min centrifugation. We then aspirated the middle flocculent layer into a new centrifuge tube with PBS dilution, washed it twice, and performed 10 min centrifugation at 1,000 rpm and 4 °C. After the MSC medium was resuspended, it was seeded into 10 cm dishes and replenished to 10 mL. After 48 h, half of the medium was changed every 2 days, using pancreatin replacement digested for 1:3 passages after confluency.

The expression of OCT4, NANOG, and vimentin proteins after the iPSCs had differentiated into iPS-MSCs was evaluated by immunofluorescence, and BMSCs were used as control. The glass pieces were built into 24 well plates first, and then the cells were seeded on the climbing pieces. When the density of cells had grown appropriately, they were washed once with PBS. Cells were first fixed in 4% paraformaldehyde (PFA) for 30 min at room temperature, then permeabilized in 0.2% Triton for 30 min at room temperature, after which they were fixed in 3% bovine serum albumin (BSA) for 2 h at room temperature. The liquid was aspirated and discarded, and the cells were then incubated with antibodies in 1% BSA configuration overnight in the dark at 4 °C, and finally secondary antibodies were added and incubated for 1–2 h in the dark at room temperature. At the end of each step above, the cells were washed 3 times with PBS for 5 min and shaken at 30 rpm. Subsequently, they were added to a final concentration of 1 μg/mL 4’,6-diamidino-2-phenylindole (DAPI; Sigma-Aldrich), 0.5 mL per well, and kept in the dark at room temperature for 5 min. The sections were sealed and observed under a fluorescence microscope (LSM710, ZEISS, Oberkocken, Germany).

Expression of pluripotency genes OCT4, NANOG and mesoderm marker gene vimentin on iPS-MSCs was examined by RT-PCR, with iPSCs and BMSCs as controls. Total RNA was extracted from cells at different differentiation stages according to the RNA kit instructions. The RNA was reverse transcribed into complementary DNA (cDNA) according to the reverse transcription kit instructions, and then the relative quantification of messenger RNA (mRNA) expression of each gene was performed on a quantitative real-time polymerase chain reaction (qPCR) instrument according to the manufacturer's instructions. The reverse transcription (RT)-PCR results were confirmed by at least 3 independent analyses. Relative gene expression was calculated using the 2-∆∆CT method relative to the glyceraldehyde 3-phosphate dehydrogenase (GAPDH) control. The primer sequences are given in .

Table 1

Primer sequences for RT-PCR

Gene name	Forward	Reverse
OCT4	CCTCACTTCACTGCACTGTA	CAGGTTTTCTTTCCCTAGCT
NANOG	TGAACCTCAGCTACAAACAG	TGGTGGTAGGAAGAGTAAAG
GAPDH	ATTGCCCTCAACGACCACT	ATGAGGTCCACCACCCTGT
VIMENTIN	CGGGAGAAATTGCAGGAGGA	AAGGTCAAGACGTGCCAGAG
Runx2	CTGTGGTTACTGTCATGGCG	AGGTAGCTACTTGGGGAGGA
Col1a1	AGGGCCAAGACGAAGACATC	AGATCACGTCATCGCACAAC
ALP	ATCAGGGACATTGACGTGATC	TTCCAGGTGTCAACGAGGTC
OCN	CTCACACTCCTCGCCCTATT	AACTCGTCACAGTCCGGATT

RT-PCR, reverse transcription-polymerase chain reaction.

Flow cytometry analysis was conducted as follows: Pancreatin substitute was used to digest and collect cells, which was washed twice with prechilled PBS, and then incubated with fitc-14, fitc-45, fitc-90, fitc-14, fitc-hla-dr, pe-34, pe-44, pe-73, PE-1, apc-19, and apc-105 antibodies (all mouse anti-human antibody, Becton, Dickinson, and Co. (BD), Franklin Lakes, NJ, USA) in the dark for 30 min. The tubes without antibodies were set up as blank controls. After washing with PBS, cells were resuspended in buffer (no less than 1×104 cells per tube) and then processed for analysis on a Fortessa Flow Cytometer (BD, USA).

Multipotent differentiation capacity was analyzed as follows: Cells were seeded into 6 well plates until they reached about 70% confluence. Then, the medium was replaced respectively with osteogenic and adipogenic induction medium which was changed every 3 days. The differentiation lasted for 21 days. The cells were then stained by Alizarin red and oil red O, respectively. For chondrogenic differentiation, 5×105 cells were collected by centrifugating into 15 mL centrifuge tubes (pellet) and adding to chondrogenic induction medium. The cell pellets were gently blown up while changing the medium every 3 days. The samples were embedded in paraffin and sectioned for identification by Alcian blue staining after 21 days.

Teratoma formation test was conducted as follows: The iPS-MSCs (P6) and iPSCs were trypsinized into single-cell suspensions and re-suspended in PBS at the density of 1×107 cells/mL. A total of 100 μL iPS-MSCs, iPSCs suspensions, and the pure PBS were injected subcutaneously into the hind limbs of 8-week-old male nonobese diabetic/severe combined immunodeficiency (NOD-SCID) mice (Shanghai Slac Laboratory Animal Co. Ltd, Shanghai, China), respectively. Teratoma formation was examined after transplantation for 8 weeks.

Culture and osteogenic differentiation of iPS-MSCs on HA/ZrO2 scaffolds

The HA/ZrO2 porous gradient composite foams ceramic materials were obtained by mechanical foam impregnation combined with gradient composite high-temperature sintering and the materials were provided by Shanghai University School of Material Science and Engineering. The sponges were pretreated with 15 wt% sodium hydroxide solution, then air dried sponges were immersed into the slurry with repeated soaking 3 times. The main components of the slurry, which was thoroughly stirred and mixed with distilled water, included ZrO2 powder (65%, 60%, 55% wt%, respectively), polyvinyl alcohol (PVA, 0.5 wt%), carboxymethylcellulose (CMC, 0.5 wt%), silica sol (10 wt%), ammonium polyacrylate (PAA-NH4, 0.6 wt%), and octanol (0.5 wt%). After soaking, the excess slurry was blown by nitrogen (N2) and dried in an oven at 110 °C for 24 h. After drying, the foam materials with slurry immersed were sintered at 1,550 °C to obtain porous ZrO2 scaffolds. Then, ZrO2 scaffolds were soaked gradually into a mixture of 30% HA/70% ZrO2, 50% HA/50% ZrO2, 100% HA, which had to be air dried before each soak. Finally, a porous HA/ZrO2 gradient composite foam ceramic material was successfully fabricated by sintering and cooling at 1,250 °C in a furnace.

Cell adhesion: The materials were firstly sterilized using a autoclave (121.3 °C, 20 min) and then immersed in a-MEM which was put in a cell culture incubator for 1 h. The iPS-MSCs and BMSCs were seeded onto HA/ZrO2 respectively and cultured with osteogenic differentiation medium and normal medium without inducer. After 7 days, the samples were gradually fixed with 2% glutaraldehyde solution for 4 h, 1% osmic acid solution for 1 h, dehydrated through graded ethanol gradients (30%, 50%, 70%, 80%, 90%, 95%, 100%), until they reached the critical point and then sputtered gold. Finally, we photographed the samples under scanning electron microscope to observe the adhesion of iPS-MSCs and BMSCs on HA/ZrO2.

For proliferation analysis, cells were seeded into a 96 well plate (2×103 cells/well), with 3 replicate wells per group. The CCK-8 was added to wells at 1, 4, and 7 days postinfection (10 L/well) and examined 1 h later. The OD values were measured at 450 nm to estimate viable cells. The cell viabilities were expressed as relative growth rate (RGR) determined by RGR (%) = [(OD)sample/OD (negative control)] ×100%. Toxicity grade: An RGR ≥100% was classified as grade 0, 75%≤ RGR <100% as grade I, 50%≤ RGR <75% as grade II, 25%≤ RGR <50% as grade III, 1%≤ RGR <15% as grade IV, and RGR =0 as grade v.

For osteogenic differentiation, iPS-MSCs and BMSCs were respectively seeded at 1×104/cm2 on 15 mm diameter HA/ZrO2 materials in 12 well culture plates and Alizarin red staining was performed at 7, 14, and 21 days. Cells were fixed with 90% ethanol for 10min and then stained using 0.2% Alizarin red solution with a pH of 6.4 for 30min at room temperature. After washing with double-distilled water to remove unbound dye, cells were imaged by light microscopy. The expressions of Runx2, COL1A1, ALP, and OCN, which were specifically related to osteogenic differentiation of iPS-MSCs and BMSCs, were determined by fluorescence qPCR in different time periods (7, 14, and 21 days). Methods of fluorescence qPCR were as previously described. Primer design sequences are shown in .

Repair of HA/ZrO2 combined with iPS-MSCs on rat skull defects

Animal experiments were performed under a project license (No. 10296) granted by the Ethics Committee of Xiaoshan Hospital of Traditional Chinese Medicine, in compliance with the hospital guidelines for the care and use of animals. A protocol was prepared before the study without registration. The animals were housed and surgically manipulated following the guidelines established by the animal ethics committee in the hospital, which gives laboratory animal care and reduces suffering. Male SD rats aged 8–10 weeks were used in the experiments, which were purchased from the animal experimental center of Zhejiang University. Anesthesia was achieved by intraperitoneal injection of ketamine (70 mg/kg bodyweight) and xylazine (10 mg/kg), followed by local anesthesia with 2 mL lidocaine injected on rats’ calvaria. A linear sagittal incision was made along the middle calvaria, followed by a full thickness incision to expose periosteum. A bone window of approximately 0.6 cm in diameter was drilled on both left and right side of the rat skull using an electric dental bur. A total of 18 numbered rats were randomly grouped by random number table. The experiments were divided into 3 groups: HA/ZrO2 material alone (n=6), HA/ZrO2 combined with iPS-MSCs osteogenic differentiated in vitro for 7 days group (IPS-MSc + HA/ZrO2, n=6), and HA/ZrO2 combined with BMSC osteogenic differentiated in vitro for 7 days group (BMSC + HA/ZrO2, n=6). All groups had material grafted on the bone window of the left side and no material grafted on the right side as blank control. Rats were housed in a constant greenhouse at 20 °C with a 12 h light/dark cycle. Food and water were provided ad libitum. All the rats received an injection of immunosuppressant cyclosporine A (30 mg/kg bodyweight) every day.

At 12 weeks after surgery, all rats had survived well and were included in the outcome study, which involved euthanasia by ether overdose anesthesia. The skull tissues were scanned using animal micro-computed tomography (CT) (SkyScan Bruker Belgium) and MicroView ABA software (GE Healthcare, Chicago, IL, USA) for bone mass analysis.

Statistical analysis

Statistical analyses were performed using SPSS 22.0 (IBM Corp., Armonk, NY, USA). All data were expressed as the mean value ± standard deviation (SD). Statistical significance was analyzed using one way analyses of variance (ANOVA), followed by post hoc least significant difference (LSD) tests. A confidence level of 95% (95% CI) was considered significant.

Results

Generation and characterization of iPS-MSCs

Differentiation was induced by serial passaging (). After several passages, the cells changed from the original clonal mass shaped iPSCs () into fibroblast-like iPS-MSCs (), which was morphologically similar to BMSCs (). The results of immunofluorescence analysis showed that the positive expressions of pluripotency genes OCT4 and NANOG in iPSCs () were barely detected in iPS-MSCs () and BMSCs (), which were contrary to mesoderm gene vimentin (). The RT-PCR analysis showed high expression of genes specific for iPSCs (OCT4, NANOG), and downregulation of pluripotency genes in iPS-MSCs and BMSCs. Meanwhile, vimentin, originally lowly expressed on iPSCs, was highly expressed on both iPS-MSCs and BMSCs (). The results were consistent with the immunofluorescence detection.

Figure 1

The cellular morphology and expression of pluripotency genes in iPS-MSCs, compared with iPSCs and BMSCs. (A) Clonal iPSCs, (B-D) Immunofluorescence staining for expression of OCT4, NANOG, vimentin in iPSCs; (E) P6 iPS-MSCs; (F-H) Immunofluorescence staining for expression of OCT4, NANOG, vimentin in iPS-MSCs; (I) P4 BMSCs; (J-L) Immunofluorescence staining for expression of OCT4, NANOG, vimentin in BMSCs. Red: marker protein; blue: cell nucleus. Scale bar, 200 µm. (M-O) Expression of OCT4, NANOG, and vimentin before and after differentiation of iPSCs into iPS-MSCs, BMSCs as control. **P<0.01; NS represents no difference. iPSCs, induced pluripotent stem cells; iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; BMSCs, bone marrow mesenchymal stem cells.

The surface molecular hallmarks were detected of passage 6 iPS-MSCs by flow cytometric analysis. BMSCs served as a positive control, while iPSCs were also tested. The results showed that iPS-MSCs highly expressed CD73, CD90, CD105, and CD44 (larger than 95%) with low expression of hematopoietic stem cell surface molecular markers (CD34 and CD45), macrophage molecular marker CD14, lymphocyte molecular marker CD19, and HLA-DR (), which were in compliance with the International Stem Cell Society for the surface molecular characterization of MSCs. Besides, the results showed that iPS-MSCs were similar to BMSCs, in addition to having low or no expression of the rest of the surface molecular markers except CD90.

Figure 2

The surface molecular markers of iPSCs, iPS-MSCs and BMSCs. iPSCs, induced pluripotent stem cells; iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells. BMSCs, bone marrow mesenchymal stem cells.

We compared the capacity for tri-lineage differentiation after 21 days of iPS-MSCs and BMSCs (). After osteogenic induction, a wide red area of calcium nodules could be seen under a microscope by Alizarin red staining, which indicated that the cells had good osteogenic differentiation function. Adipogenically differentiated cells were stained with oil red O and obvious lipid droplet formation was visible. After chondrogenic differentiation, the cells showed positive staining of Alcian blue, which indicated that they could differentiate into cartilage. In summary, iPS-MSCs had the same ability about multilineage differentiation as BMSCs.

Figure 3

Multipotent differentiation capacity. Scale bar, 200 µm. ARS, Alizarin red staining; iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; BMSCs, bone marrow mesenchymal stem cells.

To verify tumorigenicity, we injected iPS-MSCs subcutaneously into the hind limbs of NOD-SCID mice, which were also injected with iPSCs on the other side. After 8 weeks, clear tumor growth could be observed in mice transplanted with iPSCs, while the side of transplanted iPS-MSCs did not generate tumors even after dissection (). It was obvious that iPS-MSCs were safer than iPSCs.

Figure 4

Teratoma formation test. (A) iPS-MSCs and iPSCs were transplanted on the left and right sides for 8 weeks, respectively; (B) iPSCs-generated tumors in mice. iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; iPSCs, induced pluripotent stem cells. iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells.

Biocompatibility and osteogenic differentiation of iPSC-MSC seeded on HA/ZrO2

As reported in our previous study (9), the HA in powdered composites was transformed into CaH2P2O7, Ca2P2O7, CaP, CaH2 phases. After being in contact with water, these nonhydrated phosphate phases could provide the necessary concentration of calcium and phosphate ions for bone mineralization. Meanwhile, high concentrations of calcium phosphate could form HA again in body temperature to stimulate bone formation. The addition of the inert ZrO2 greatly improved the biomechanical strength of the composite materials. The average flexural strength of materials was 898.67 MPa, which was much higher than the usage requirements of human weight-bearing sites. The HA/ZrO2 porosity was 25 ppi and uniform with pore size of 150–300 μm. These were prepared as round pieces of different sizes according to experimental requirements. After iPS-MSCs and BMSCs were cultured on HA/ZrO2 with normal medium for 7 days, under scanning electron microscopy (SEM), cells tightly adhered to the surface of the materials, spread out, and grew in a fibrous configuration, and spanned the pores on the surface of the materials with good condition (). The CCK-8 studies showed that (), cells proliferated continuously in both culture solutions with increasing time, and the evaluation of cytotoxicity grade was grade 0 in both cultures. Therefore, iPS-MSCs and BMSCs can adhere, grow, proliferate, and differentiate well with HA/ZrO2 in vitro. All experiments showed that HA/ZrO2 had good biocompatibility.

Figure 5

The cell-growth on the materials was examined by SEM. SEM, scanning electron microscopy. The internal structure of HA/ZrO2 materials were dense and porous, which presented a tridimensional distribution. The blue arrow indicated that both iPS-MSCs and BMSCs tightly adhered to the surface of the materials, spread out and grew in a fibrous configuration. The red arrow indicated that all the cells spanned the pores on the surface of the materials with good condition. (A-D) Under different magnifications, iPS-MSCs growing on the surface of the materials were observed; (E-H) BMSCs growing on the surface of the materials were observed under different magnifications. iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; BMSCs, bone marrow mesenchymal stem cells.

Table 2

CCK-8 assays for proliferation analysis

Group	1 day				2 days				3 days
	OD (mean ± SD)	RGR (%)	Tox		OD (mean ± SD)	RGR (%)	Tox		OD (mean ± SD)	RGR (%)	Tox
IPS-MSCs neg group	0.255±0.002				0.570±0.036				1.078±0.102
IPS-MSCs + HA/ZrO2 extract group	0.320±0.026	125.49	0		0.765±0.014	134.21	0		1.130±0.234	104.82	0
BMSC neg group	0.259±0.011				0.733±0.064				1.083±0.124
BMSC + HA/ZrO2 extract group	0.275±0.022	106.18	0		0.743±0.044	1.014	0		1.208±0.235	111.54	0

CCK-8, cell counting kit-8; OD, optical density; RGR, relative growth rate; iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; iPSCs, induced pluripotent stem cells; BMSCs, bone marrow mesenchymal stem cells.

We compared the osteogenic differentiation of iPS-MSCs and BMSCs on HA/ZrO2 materials at different times (7, 14, and 21 days) in vitro by detecting the expression of osteogenesis related genes (Runx2, COL1A1, ALP, and OCN). The gene Runx2 can promote early osteogenic differentiation as a key factor necessary for osteogenic differentiation of mesenchymal stem cells; Col1a1 is a kind of collagen associated with the formation of the extracellular matrix (ECM) of the pre-osteoblast, which progressively expresses ALP during the maturation stage and then OCN during the mineralization phase. First of all, the results of fluorescence qPCR showed that the expression of osteogenesis related genes in both iPS-MSCs and BMSCs increased significantly with time and there was no significant difference between the two groups (). Besides, it was shown that both iPS-MSCs and BMSCs had a good mineralization ability on the HA/ZrO2 materials after Alizarin red staining. With increasing time, the color was darker and the area of red larger, which indicated the increasing calcium nodule (). Furthermore, the results of calcium nodule quantification testing showed no significant difference in calcium content between the two types of cells during the same period ().

Figure 6

The tests about osteogenic differentiation of iPS-MSCs and BMSCs. (A-D) The expression of osteogenesis related genes (Runx2, COL1A1, ALP, and OCN) in iPS-MSCs and BMSCs on days 7, 14, and 21. (E) Alizarin red staining used in osteogenic differentiation of iPSMSCs and BMSCs on HA/ZrO2 at 7, 14, and 21 days. (F) Calcium nodule quantification test about osteogenic differentiation of iPS-MSCs and BMSCs on HA/ZrO2 at 7, 14, and 21 days. iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; BMSCs, bone marrow mesenchymal stem cells.

Repairing effects of HA/ZrO2 combined with IPS-MSCs on rat skull defects

To validate the osteogenic capacity of iPS-MSCs in vivo, we used BMSCs as controls and individually combined with HA/ZrO2 as composite materials after 7 days of osteogenic induction in vitro and then transplanted them into rats with skull bone defects. After 12 weeks, the results examined by micro-CT revealed that almost all defects transplanted by HA/ZrO2+ iPS-MSCs group and HA/ZrO2+ BMSCs group were repaired better than transplanting with HA/ZrO2 alone group (). For bone mass analysis, the values of volume bone mineral density (vBMD), new bone formation volume (BV), and percent new bone formation volume (BV/TV) in both HA/ZrO2 combined with iPS-MSCs or BMSCs groups were significantly higher than those in the HA/ZrO2 alone group ().

Figure 7

Micro-CT examination and bone mass analysis. (A) The left hole was transplanted by iPS-MSCs + HA/ZrO2, the right hole was a blank control. (B) The left hole was BMSCs + HA/ZrO2, the right hole was a blank control. (C) The left hole was HA/ZrO2, the right hole was a blank control. (D-F) The bone mass comparison in BV, BV/TV and vBMD. iPS-MSCs, induced pluripotent stem cells-mesenchymal stem cell-like cells; BMSCs, bone marrow mesenchymal stem cells; BV, new bone formation volume; BV/TV, percent new bone formation volume; vBMD, volume bone mineral density.

Discussion

The MSCs belong to adult stem cells and have a strong ability to self-renew and proliferate. They can be transformed into bone cells, adipocytes, nerve cells, muscle cells, and endothelial cells under different induction conditions. They have many advantages such as being easy to manipulate gene and weak immunogenicity, which gradually becomes an appropriate cell carrier for gene therapy. At present, although the treatment of BMSCs has been more widely applied in the clinic (10-12), several factors limit their further clinical applications. Firstly, the acquisition of BMSCs is an invasive operation, and the number of BMSCs provided by patients themselves is limited. Besides, there are individualized differences in the activities of MSCs, such as disease, age, and other factors. Moreover, poor pericellular environment such as inflammatory reaction, immune rejection, hypoxia, and oxidative stress also decreases the ability of BMSCs (13).

There are similarities between iPSCs and ESCs in morphology, epigenetic modifications, gene and protein expression, and iPSCs have great potential regarding self-renewal, high proliferation, and multilineage differentiation. They can be reprogrammed from differentiated mature cells, which solve the ethical concerns of ESCs. Besides, iPSCs are induced from patients’ autologous cells so that they avoid immune rejection. With the development of reprogramming technology, iPSCs derived by induction with adenovirus, transient expression of plasmid vectors, or recombinant proteins have a lower tumorigenic risk. Some results have shown that hiPSCs-derived MSCs have higher telomerase activity, and better immunomodulation and tissue repair abilities than MSCs. No tumor was observed in animals after implanting iPS-MSCs, which indicates their security. The investigators also contrasted the finding that iPS-MSCs have a greater capacity for vascular repair than BMSCs. All studies have indicated that iPS-MSCs are more promising for cell therapy and regenerative medicine (14-17).

At present, there have been several reports on the methods of iPSCs or ESCs differentiated into MSCs, including spontaneous differentiation in embryoid bodies (EBs) or inducing and differentiating directly in conditioned media (18-22). Inducting EBS differentiation is a classical method, and iPSCs can differentiate into the inner cell mass of spherical blastocyst under a specific suspension culture. Mature EBs include many types of cells which represent derivatives of the 3 embryonic germ layers. However, the procedure of differentiation in EBS is tedious, is more time-consuming, and is considered inefficient. The methods of direct conditioned medium induction are mostly achieved by the way of adding cytokines and small molecule compounds, but also by using direct culture with BMSCs and iPSCs or ESs after serial passage to acquire MSCs. During the differentiation of iPSCs, the transforming growth factor-β (TGF-β) pathway maintains stemness of iPS cells. Acting as a TGF-β signal inhibitor, SB431542 can promote the differentiation of iPSCs (23-25).

In this study, we cultured BMSCs in the presence of SB431542, combined with the method of serial subculture to induce iPS cells. For 7 consecutive days in medium supplemented with 10 uM SB431542, the first passage was performed with milder accutase enzymatic digestion. The cells were full 3–4 days after passaging, and after another passage, spindle cells similar to those of BMSCs appeared. From the induction to obtaining BMSC-like cells, it takes only about 2 weeks, as a result of which the time of induction is greatly shortened. According to the 2006 International Society for stem cells (ISCT) identification criteria for human MSCs (26): (I) MSCs can grow adherently under standard culture conditions; (II) MSCs express CD105, CD73, and CD90 and do not express CD45, CD14, CD11b, HLA-DR, CD79α, or CD19, in which the positive rate of CD73, CD90, and CD105 should be ≥95% and the positive rate of other negative markers should be ≤2%; (III) MSCs have the ability of 3-way differentiation of osteogenic, adipogenic, and chondrogenic in vitro. Flow cytometric analysis used in surface markers of iPSC BMSCs, BMSCs, and hiPSCs revealed that iPSCs expressed the surface molecules CD44, CD73, CD105, CD90, CD14, CD19, CD34, CD45, and HLA-DR before differentiation from 0.4%, 0.3%, 0.1%, 100%, 0.2%, 0.2%, 0.3%, 0%, 0% into 99.8%, 99. 9%, 100%, 99. 9%, 0.8%, 0.3%, 0.4%, 0.6%, 0.8%, which were similar with the BMSCs as control expressing 100%, 100%, 99.2%, 98.1%, 0.3%, 0.4%, 0.5%, 0.2%, and 2.1%. Using immunofluorescence staining to contrast the expression of related proteins before and after iPSCs differentiated, it was shown that iPS-differentiated cells did not express the pluripotency marker protein OCT4 and the ectoderm marker protein Nestin, but did express the mesoderm marker protein vimentin (27). The iPS-BMSCs were induced for osteogenic, adipogenic, and chondrogenic differentiation, and after 21 days stained positive with Alizarin red, oil red O, and Alcian blue. The results were consistent with qRT-PCR related gene assays. The above results befit the definition of MSCs by ISCT, indicating the successful establishment of a highly efficient method for differentiating iPSCs into MSCs.

The application of tissue-engineered bone to repair bone defects is a hot spot in current clinical medicine (28-30). As a scaffold for cells, the selection criteria of tissue-engineering bone scaffold materials include: (I) excellent biomimetic properties. Bone tissue is a structure with 3D porousness, which is conducive to the metabolic absorption of nutrients. Artificial scaffold materials also need a porous structure similar to bone tissue, which is conducive to the ingrowth of cells and better promotes the reconstruction of bone repair; (II) a certain mechanical strength; (III) good osteoconductive and osteoinductive effect; (IV) be degradable. The degradative components of scaffold material are similar to bone composition, which not only cause no toxicity but also promote the generation of bone. Currently, cell scaffolds used for bone repair mainly include fiber scaffolds, microspheres, porous scaffolds, hydrogels and composite scaffolds (31). Hydroxyapatite (HA), a bioactive material close to natural apatite mineral, is the major inorganic substance of human bone (32-34). After implantation, HA will be partially degraded to release the necessary calcium and phosphorus, after which the elements will be absorbed, utilized, and incorporated into new tissues, so that the HA implant and bone tissues can be well integrated. HA can facilitate the formation of extracellular matrix including collagen I, fibronectin, peptides, growth factors, glucosamine, and other active molecules, which activate the related signaling pathways for the adsorption of stem cells onto biomaterials (35). In a study by Shie et al. (36), inhibition of MAPK/ERK and MAPK/p38 signaling pathways significantly decreased the adhesion, proliferation, and differentiation of hMSCs and HDPCs in calcium silicate cement. Chen et al. (37) found that the adhesion and osteogenic differentiation of BMSCs cultured on a HA-coated surface could be better after using low-magnitude and high-frequency vibrations, while the Wnt10B, β-catenin, Runx2 and osterix were significantly increased, as a result of which vibration may directly induce osteogenesis by activating the Wnt/β-catenin signaling pathway. Although HA has good osteoconductivity, osteoinductivity, and biocompatibility (38), simple HA as a scaffold material has defects such as low strength, poor toughness, and degranulation. Being fabricated into porous materials further reduces the flexural strength and fracture toughness of HA, as a result of which the scaffold material with single HA cannot meet the requirements for bone replacement in load-bearing parts of the human body. Zirconium dioxide (ZrO2) is a mineral raw material of zirconia with a very high density, the hardness of which is second only to diamond. Besides, it has a good biocompatibility, without allergy, irritation, corrosion, or other adverse reactions (38-40). Combining HA and ZrO2 to prepare HA/ZrO2 composites both improved the physical strength of HA and retained the good biocompatibility of HA. In this study, the porous composites of HA/ZrO2 were prepared by gradient recombination by high-temperature sintering adding pore former. Adjusting the strength by changing the HA/ZrO2 voids can produce highly simulated artificial bone materials with mechanical properties that most closely resemble natural bone. Biomechanical examination revealed that HA/ZrO2 composites exhibited an average flexural strength of 898.6 MPa, which could reach up to 1,112.6 MPa, far exceeding the natural bone strength in humans (41,42).

Subsequently we used MSCs differentiated from hiPSCs to construct novel tissue-engineered bone by seeding in HA/ZrO2 porous foam ceramic materials, and then examining the biocompatibility. Seeding iPS-MSCs and BMSCs on HA/ZrO2 for SEM at days 2, 7, and 14 showed that both cells adhered to the surface of the materials, proliferated well, and gradually grew into the internal voids of the materials. The CCK-8 assay was used to detect cell proliferation, and the OD values of the cells cultured with the extract of the dip solution from HA/ZrO2 showed a gradual increase on days 1, 4, and 7, which were not significantly different in the control cells cultured in complete medium. The cytotoxic grade ratings of HA/ZrO2 were all grade 0, which indicated that HA/ZrO2 porous foam ceramic materials had good biosafety. We seeded iPS-MSCs and BMSCs on HA/ZrO2 porous materials, respectively, for osteogenic induction and differentiation in vitro, after which we performed calcium nodule assay by Alizarin red staining and related gene of osteogenesis expression assay at different time points (days 7, 14, and 21) to compare the osteogenic potential of the 2 cells on HA/ZrO2 materials. The results showed that both iPS-MSCs and BMSCs composite materials were deeply stained with Alizarin red dye solution over time. Besides, the quantitative analysis of calcium content showed that calcium content gradually increased in both groups, indicating that iPS-MSCs have a good osteogenic capacity like BMSCs. The results of qRT-PCR confirmed that Runx2, Col1a1, ALP, and OCN expressions all increased with time, in which OCN reached a high value at day 21. As a specific transcriptional regulator (43), Runx2 is necessary and sufficient for osteogenic differentiation of BMSCs. The expression of Runx2 can promote the transcriptional maturation of osteogenesis-related protein genes and the sustained expression of Runx2 is beneficial to the progress of osteogenic differentiation (44). The gene Col1a1 is an important marker of osteogenic differentiation, which accounts for more than 90% of the bone matrix and is an important component of osteogenesis (45,46). As an essential enzyme in osteogenesis, ALP can hydrolyze organic phosphate, release inorganic phosphorus, and then form hydroxyapatite, which is a marker about early maturation in osteogenic differentiation of MSCs (45,47). The ECM protein OCN is only found in the ECM secreted of osteoblasts currently. Its appearance marks the beginning of the mineralization phase in osteogenic differentiation, which is well recognized as a marker of mature osteoblast differentiation (48,49). The results illustrated that HA/ZrO2 could promote the osteogenic differentiation of iPS-MSCs from BMSCs. Finally, we transplanted iPS-MSCs on HA/ZrO2 to repair rat calvarial defects. At 28 days after transplantation, the calvarial defects repaired by iPS-MSCs + HA/ZrO2 composite healed at a rate close to that of bone defects repaired by BMSCs + HA/ZrO2 composite. All of them were faster than the control group, which indicated that HA/ZrO2 not only has good biocompatibility, but also can promote osteogenesis and accelerate the healing of bone defects later.

Conclusions

In conclusion, we obtained IPSC-MSCs by inducing UC-derived iPSCs, which were characterized by phenotype, gene, and multi-differentiating capacity resembling normal human BMSCs. The iPSC-MSCs were able to continue their proliferation and osteogenic differentiation like BMSCs after being seeded on HA/ZrO2. Likewise, the compound of iPS-MSCs and HA/ZrO2 can promote the healing of calvarial defects in rats after transplantation. This study provides a novel approach for bone tissue engineering, and a substantial reference about iPSC-based therapy for bone tissue repair and orthopedic diseases.

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