BioMed Research International
Volume 2019 (2019), Article ID 7343957, 10 pages
https://doi.org/10.1155/2019/7343957

Research Article

Acceleration of Bone Regeneration in Critical-Size Defect Using BMP-9-Loaded nHA/ColI/MWCNTs Scaffolds Seeded with Bone Marrow Mesenchymal Stem Cells

Ran Zhang,¹ Xuewen Li,² Yao Liu,³ Xiaobo Gao,⁴ Tong Zhu,¹ and Li Lu¹

¹Department of Oral and Maxillofacial Surgery, School of Stomatology, China Medical University, 117 Nanjing North Street, Shenyang 110002, China
²Department of Oral Anatomy and Physiology, School of Stomatology, China Medical University, 117 Nanjing North Street, Shenyang 110002, China
³Department of Pediatric Dentistry, School of Stomatology, China Medical University, 117 Nanjing North Street, Shenyang 110002, China
⁴Department of Oral and Maxillofacial Surgery, The Affiliated Hospital of Chifeng University, Chifeng 024005, China

Correspondence should be addressed to Li Lu; lulicmu3503@hotmail.com

Received 22 October 2018; Revised 4 March 2019; Accepted 21 March 2019; Published 11 April 2019

Academic Editor: Elena Landi

Copyright © 2019 Ran Zhang et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

Abstract.

Biocompatible scaffolding materials play an important role in bone tissue engineering. This study sought to develop and characterize a nano-hydroxyapatite (nHA)/collagen I (ColI)/multi-walled carbon nanotube (MWCNT) composite scaffold loaded with recombinant bone morphogenetic protein-9 (BMP-9) for bone tissue engineering by in vitro and in vivo experiments. The composite nHA/ColI/MWCNT scaffolds were fabricated at various concentrations of MWCNTs (0.5, 1, and 1.5% wt) by blending and freeze drying. The porosity, swelling rate, water absorption rate, mechanical properties, and biocompatibility of scaffolds were measured. After loading with BMP-9, bone marrow mesenchymal stem cells (BMMSCs) were seeded to evaluate their characteristics in vitro and in a critical sized defect in Sprague-Dawley rats in vivo. It was shown that the 1% MWCNT group was the most suitable for bone tissue engineering. Our results demonstrated that scaffolds loaded with BMP-9 promoted differentiation of BMMSCs into osteoblasts in vitro and induced more bone formation in vivo. To conclude, nHA/ColI/MWCNT scaffolds loaded with BMP-9 possess high biocompatibility and osteogenesis and are a good candidate for use in bone tissue engineering.

1. Introduction

Craniofacial bone defects are a common disease and difficult to study experimentally and treat clinically. Conventional allografts and autografts have limitations such as immune rejection, disease transmission, malunion, and flap necrosis [1, 2]. Researchers are developing new alternatives to traditional methods for bone defect regeneration [3]. The development of artificial bone transplantation has been greatly facilitated by tissue engineering. The emergence and development of tissue engineering offer tremendous potential. The properties of bio-scaffolds play an important role in bone tissue engineering [4, 5]. An ideal biomaterial for bone tissue engineering should provide biocompatibility, good surface activity, appropriate pore sizes and porosity, high mechanical strength, and plasticity [6–8].

Hydroxyapatite (HA) is considered as the most studied biomaterials because of its proven biocompatibility and being the main inorganic constituent of bone [9]. Nano-hydroxyapatite (nHA) as a biomaterial is similar to the inorganic component of human bone. Therefore, it is considered to be more suitable for bone scaffolds. It is also an important source of calcium and phosphate and very important for bone regeneration and bone remodeling [10]. Collagen I (ColI) is a major organic component of bone, which has been used for cell culture, growth, and differentiation. It is an ideal base material to fabricate a composite porous scaffold [11]. Carbon nanotubes (CNTs) are a new nano-material developed by Iijima et al. [12], known as “super fibers”, which are divided into single-walled carbon nanotubes (SWCNTs) and multi-walled carbon nanotubes (MWCNTs). In recent years, MWCNTs, which possess exceptional chemical, electrical, and mechanical properties, have been advocated for application in bone tissue engineering as reinforcement materials. They have been applied to bone tissue engineering by Zanello et al. [13] to increase the physical and chemical properties of scaffolds. In addition, Narita et al. [14] reported that MWCNTs can help to prevent the development of osteolysis around the implants. Bone morphogenetic protein-9 (BMP-9) (also known as GDF-2) has direct effects on angiogenesis, chondrogenesis, and osteogenesis [15]. Recent studies have demonstrated that BMP-9 shows the most effective osteogenic behavior among BMPs in vivo and in vitro [16–18].

Our objective was to fabricate a nHA/ColI/MWCNT (nHACM) composite scaffold for bone tissue engineering to enhance osteogenesis of bone marrow mesenchymal stem cells (BMMSCs). MWCNTs have been used to improve the mechanical properties of classical nHA/ColI scaffolds. Furthermore, a series of in vitro experiments were performed to characterize and determine the best concentration of MWCNTs. Then, nHACM was used as a carrier to load BMP-9. This new BMP-9-releasing nHACM composite scaffold (nHACM/B9) was fabricated and evaluated in vitro and in vivo.

2. Materials and Methods

2.1. Materials

nHA was purchased from Emperor Nano Material (Nanjing, China). ColI was purchased from Corning (NY, USA). BMMSCs from Sprague-Dawley (SD) rats were purchased from PuheBio (Wuxi, China). MWCNTs (-COOH) were purchased from Boyu Gaoke (Beijing, China). α-Minimum essential medium (αMEM), phosphate-buffered saline (PBS), trypsin, and fetal bovine serum (FBS) were purchased from HyClone (UT, USA). BMP-9 was purchased from PeproTech (NJ, USA).

2.2. Fabrication of Scaffolds

After freeze drying, ColI was dissolved in 50 mmol/L acetic acid, and the final concentration of ColI was adjusted to 2% (w/v). nHA was added to ColI at 3:7 (w/w) [19, 20]. After preparing various concentrations of MWCNTs (0.5, 1, and 1.5% wt), they were mixed with the nHA and ColI-blended solution [21, 22]. The pH values of the mixtures were neutralized using 0.05 M sodium hydroxide solution. nHA-ColI-MWCNT solutions were stirred at low temperature for 12 h.

The solutions were poured into Teflon culture plates and lyophilized (Alpha 1-2 LD plus, Christ, Germany) for 72 h to obtain nHACM scaffolds. After a series of scaffold evaluations, BMP-9 (500ng/ml) was loaded into the scaffolds when the solution was stirred before freeze drying [23, 24] (Supplementary Figure A). We found that the most appropriate proportion of MWCNTs was 1% for bone tissue engineering in a preliminary experiment (Supplementary Figure B). Therefore, this concentration was used in subsequent experiments in vitro and in vivo.

2.3. Scaffold Characterization Studies

nHACM scaffold samples were fractured, coated with gold, and observed using a scanning electron microscope (S4800, Hitachi, Japan). Pore sizes were measured in SEM images by ImageJ software. To measure pore size, scale bars were set within the SEM image, representing a known distance. The contour of the pores was outlined and measured (μm). Different cross sections of the composites were assessed [25]. The porosity of scaffolds was evaluated using ethyl alcohol (EtOH) displacement. The primary volume of EtOH was V₁. The total volume of EtOH after scaffold immersion was V₂. The residual EtOH volume after scaffold removal was V₃. The following formula was used to calculate porosity: Porosity (%) = (V₁−V₃)/(V₂ −V₃)×100%. Water absorption mirrored quality changes after scaffolds were immersed in PBS. W₁ is the swollen weight and W₂ is the dried weight. The following formula was used: water absorption rate (%) = (W₁−W₂)/W₂ × 100%. The swelling property was indicated by volume changes after immersion in PBS. Wet and dried volumes were, respectively, recorded as and . was determined according to Archimedes’ principle, and of the scaffold was measured using a Vernier caliper. The swelling index of the scaffold was calculated using the following formula: Swelling ratio (%) = (−)/×100%. The mechanical compression of the standardized scaffolds (10 mm in diameter and 10 mm in height) was measured by a universal material testing machine (E1000, Instron, USA) with a 100 N load at room temperature. Crosshead speed was 1 mm/min.

2.4. Culture of BMMSCs

BMMSCs were cultured in αMEM with 10% FBS and 1% penicillin/streptomycin (GE Healthcare Life Sciences Hyclone Laboratory, UT, USA). The cells were cultured in 75-cm² flasks at 37°C in a humidified atmosphere of 5% CO₂ (Supplementary Figure C). The scaffolds used for cell seeding were cut with 8.00 mm in diameter × 2.00 mm height. 50 μl of BMMSCs at 4 × 10⁴ cells/well were cultured on pre-wetted nHACM scaffolds for 72 h at 37°C and 5% CO₂.

2.5. BMMSC Morphology on nHACM/B9 Scaffolds

After culture on scaffolds for 72 h, the morphologies of BMMSCs were observed. The samples were fixed in 2.5% glutaraldehyde (Solarbio, Beijing, China) at 4°C overnight. After dehydration and drying, SEM was used to observe the samples.

2.6. Counting Kit-8 (CCK-8) Assay

A CCK-8 (Beyotime, Shanghai, China) assay was used to examine the viability and activity of grafted cells after BMMSCs were cultured on nHACM and nHACM/B9 scaffolds for 1, 3, 5, and 7 days. At specific time points, the medium was removed and replaced with serum-free culture medium containing 0.5 mg/mL CCK-8 solution. Absorbance was measured at 450 nm using an enzyme-linked immunosorbent assay reader (Infinite M200, Tecan, Austria).

2.7. BMMSC Differentiation and Alkaline Phosphatase (ALP) Activity Assay

BMMSCs were cultured on nHACM loaded with BMP-9 and treated with 50 μg/ml ascorbic acid, 5 mM β-glycerophosphate, and 10 nM dexamethasone to induce osteoblast differentiation. The culture medium was changed every 2 days. After induction for 1, 4, 7, and 10 days, ALP activity was determined in cell lysates by an ALP assay kit (Beyotime, Shanghai, China), and absorbance was read at 520 nm using an ELISA plate reader.

2.8. Quantitative Reverse Transcription-Polymerase Chain Reaction (qPCR)

Isolation and reverse transcription of total RNA were carried out. The synthesized cDNA was then used to perform real-time-PCR. Briefly; after 7 days of culture, the total RNA was extracted by using TRIzol reagent (Invitrogen, Carlsbad, CA, USA). RNA was reverse-transcribed into cDNA, which was used for real-time PCR on a LightCycler Nano (Roche, Switzerland), according to the manufacturer’s instructions. The expression of osteogenic markers osteocalcin (OCN), collagen type I, alpha 1 (ColIα1), and osteopontin (OPN) was analyzed by PCR amplifications using specific primers (Table 1). All reactions were run in triplicate. Target genes were normalized against GAPDH as the housekeeping gene.

Table 1: Primer sequences of osteogenic markers.

forward primer
reverse primer

OCN
5′-TCTTTCTCCTTTGCCTGGC-3′
5′-CACCGTCCTCAAATTCTCCC-3′

ColIα1
5′-GCAACAGTCGCTTCACCTACA-3′
5′-CAATGTCCAAGGGAGCCACAT-3′

OPN
5′-TATCCCGATGCCACAGATGA-3′
5′-TGAAACTCGTGGCTCTGATG-3′

GAPDH
5′-TGTGTCCGTCGTGGATCTGA -3′
5′-TTGCTGTTGAAGTCGCAGGAG-3′

2.9. In Vivo Experiments

The in vivo experiments were approved by China Medical University’s Animal Care and Use Committee. We used 15 male 8-week-old SD rats as experimental animals. After inducing anesthesia with chloral hydrate, skin was prepared and sterilized, and an incision on the center of the scalp was made. After exposing the cranial bone, an 8 mm critical size defect (CSD) was created with an 8 mm trephine bur. Next, scaffolds with or without cells were implanted into the defects. At the end of the operation, the incision was sutured. Rats were given 5 mg/kg carprofen post-surgery for analgesia, placed in a recovery cage, and observed until awake and ambulatory.

All rats were divided into three groups: group 1, blank control; group 2, nHACM+BMMSCs; group 3, nHACM/B9+BMMSCs. Twelve weeks after the operations, animals were euthanized by cervical dislocation under deep anesthesia with isoflurane.

2.10. Evaluation of Bone Regeneration

Three-dimensional images of the calvarias were captured with a multi-slice spiral computed tomography (CT) scanner (SOMATOM Definition AS+; Siemens Healthineers, Germany) at 12 weeks after implantation. After standard radiological image processing, the scanning images and CT values of calvarial bones were obtained using SyngoMMWP software. NIH ImageJ software was used to measure the area of new bone regeneration. The CT value (Hounsfield unit; HU) was determined to evaluate the density of regenerated tissue. The fixed calvarial bone samples were embedded in paraffin wax and then cut into 5-μm thick sections. The sections were stained with hematoxylin and eosin (H&E), and then images were captured under a microscope (CKX41; Olympus Co., Tokyo, Japan). New bone volumes of regenerated tissue were analyzed using ImageJ software.

2.11. Statistical Analysis

All quantitative data are expressed as the mean ± SD of three replicates for each test. Statistical significance was analyzed by SPSS 17.0 software (SPSS Inc., Chicago, IL). Pairwise comparisons were assessed using Student’s t-test. For all experiments, a value of less than 0.05 was considered significant.

3. Results

3.1. Synthesis and Characterization of nHACM Scaffolds

Ethyl alcohol displacement was used to analyze the porosity of scaffolds. The results showed that the porosity of 0.5% wt MWCNT group was 91.34±3.02%, the porosity of 1.0% wt MWCNT was 89.04±3.26%, and the porosity of 1.5% wt MWCNT was 82.82±2.74%. Scanning electron microscope was used to observe and analyze the inside of scaffolds. The results showed that nHACM scaffolds had a porous structure with well-oriented pores enclosed by a thin wall from the surface to inside (Figure 1). Most pores of the scaffolds were uniform. This structure benefits cells in going inside the scaffolds and forming attachment. An optimum scaffold should possess a suitable 3D structure and pore size for nutrient transport and preventing cell loss. By using ImageJ to analyze the image of SEM, we obtained the pore size of 0.5% wt MWCNT group was 153.40±31.17 μm, the pore size of 1.0% wt MWCNT group was 129.00±23.38 μm, and the pore size of 1.5% wt MWCNT group was 88.00±11.73 μm. As the concentration of MWCNT increased, the porosity and pore size of scaffolds decreased (Figures 2(a) and 2(b)). Water absorption and a swelling ability are important factors in evaluating the usefulness of a composite material for bone tissue engineering. The water absorption ability of nHACM scaffolds was measured in terms of the degree of swelling at equilibrium. The degree of swelling of the scaffolds ranged from 25.4 to 44.9%, while the degree of water absorption was between 196 and 288%. As the concentration of MWCNT increased, the swelling ability and water absorption of scaffolds decreased (Figures 2(c) and 2(d)). Mechanical strength is important to the bone tissue engineering scaffolds. The compressive modulus and compressive strength decreased with the increasing concentration of MWCNT (Figures 2(e) and 2(f)). Scaffolds containing 1.5% wt MWCNT had the highest compressive modulus (8.06±0.07 MPa) and compressive strength (0.94±0.08 MPa) among the three kinds of scaffolds, but they had lowest porosity, pore size, swelling ratios, and water absorption. And scaffolds containing 0.5% wt MWCNT were opposite. So we chose 1.0% wt MWCNT in subsequent experiments.

Figure 1: Micrographs of the scaffolds with varying MWCNT content (0.5%, 1.0%, and 1.5% wt). SEM showed that nHACM scaffolds had a porous structure with well-oriented pores enclosed by a thin wall from the surface to the inside. As the concentration of MWCNT increased, the pore size and number decreased.

(a)

(b)

(c)

(d)

(e)

(f)

Figure 2: Characterization and physicochemical properties of scaffolds. (a-d) As the concentration of MWCNT increased, the pore size, porosity, water absorption, and swelling ability decreased. (e, f) Compressive strength and compressive modulus decreased with increasing MWCNT concentrations. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001.

To further research the cytotoxicity of scaffolds, CCK-8 assay was used. And the CCK-8 assay is a general method to evaluate the cytotoxicity of scaffolds in bone tissue engineering. In our study, OD values of the three groups indicated no statistically significant differences (Figure 3). Compared with BMMSCs cultured without scaffolds in cell culture plates, the cell activity of BMMSCs cultured on the two scaffolds was not decreased. BMMSCs grew on nHACM and nHACM/B9 scaffolds without cytotoxicity. In addition, SEM images showed cells randomly distributed on the surface or inside of the nHACM scaffolds. At 72 h, some cells had adhered to the surface and pores of the scaffold. SEM showed that single round cells became flat, polygonal, or triangular. Cell microfilaments and pseudopodia were tightly connected to the scaffold (Figure 4).

Figure 3: CCK-8 assays to measure numbers of BMMSCs on nHACM and nHACM/B9 scaffolds. No statistically significant differences were seen among the three groups. Mean±SD; n=3.

Figure 4: Scanning electron microscopy (SEM) of BMMSCs seeded onto nHACM/B9 scaffolds after 72 h of incubation. SEM images show a random distribution of cells on the surface of the nHACM/B9 scaffold.

3.2. nHACM/B9 Scaffolds Promote Osteogenic Differentiation of BMMSCs In Vitro

The experiments have testified that nHACM/B9 scaffold possessed good physicochemical properties and biocompatibility. The study to evaluate the ability of promoting osteogenic differentiation of BMMSCs in vitro was carried out. ALP activity is an important consideration for evaluating osteoblast differentiation. ALP activity was significantly increased in cells cultured on nHACM and nHACM/B9 compared with the control group (Figure 5(a)). qPCR showed that OCN, ColIα1, and OPN gene expression was increased in the nHACM/B9 group compared with the nHACM group (Figure 5(b)). And nHACM/B9 group was the highest of all. The results indicated that nHACM enhances osteoblast differentiation of BMMSCs in vitro, and the effect increases after BMP-9 loading.

(a)

(b)

Figure 5: nHACM/B9 scaffolds promote osteogenic differentiation of BMMSCs in vitro. (a) There was a significant difference between the BMMSC group and nHACM and nHACM/B9 groups after 4 days of culture. (b) qPCR analysis of osteogenic marker genes indicated that BMMSCs cultured on nHACM scaffolds had increased expression of ColIα1, OCN, and OPN that are important genes to evaluate osteogenic differentiation of BMMSCs. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001.

3.3. nHACM/B9 Scaffolds Improve Bone Regeneration In Vivo

To further evaluate the efficacy of improving bone regeneration in vivo, an 8 mm CSD in SD rats was used. All 15 rats survived the surgery and recovered well postoperatively, without infection. Cranial bones samples were harvested at 12 weeks after implantation and analyzed by radiology and histology analysis. The HU of cranial bones samples showed that the nHAC/B9+BMMSC group had the significantly highest, and the HU of the nHACM+BMMSC group was higher than the control group (Figure 6). Analysis of CT images by software ImageJ showed that the nHACM/B9+BMMSC group had the significantly largest area of new bone regeneration, and the nHACM+BMMSCs group had a larger area of new bone regeneration than the control group (Figure 7) (Supplementary Figure D). Histological analysis confirmed that new bone tissue had formed in nHACM/B9+BMMSCs and nHACM+BMMSCs groups with a difference reflected in quantity (Figure 8). That indicated that the scaffold could stimulate new bone formation, and the effect will be enhanced after loading with BMP-9.

Figure 6: nHACM/B9 scaffolds reinforce bone regeneration in vivo. CT values of cranial bone specimens in the control, nHACM+BMMSC, and nHACM/B9+BMMSC groups. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001.

(a)

(b)

Figure 7: In vivo radiographic examinations at 12 weeks of repair. (a) Analysis of the CT images showed that the nHACM/B9+BMMSC group had a significantly larger area of new bone regeneration among the three groups. The nHACM+BMMSCs group had a significantly larger area of new bone regeneration than the control group. Red circles denote the original bony defects. (b) The proportion of newly formed bone in the control, nHACM+BMMSC, and nHACM/B9+BMMSC groups. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001.

(a)

(b)

Figure 8: H&E staining on the sectioned slices at 12 weeks postoperatively. (a) There was new bone regeneration (Bone) in nHACM+BMMSC and nHACM/B9+BMMSC groups. Some fragments of nHACM were not completely biodegradable (nHACM). (b) New bone volumes of nHACM+BMMSC and nHACM/B9+BMMSC groups were much higher than the control group. There was connective tissue (CT) in the control group. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001.

4. Discussion

In 1993, Langer and Vacanti [26] published an article entitled “Tissue engineering” in Science, which first proposed the basic implication of tissue engineering. As a development in bone tissue engineering, cells cultured with a specific scaffold to construct composite materials to repair bone defects have achieved initial success. It is an urgent task to develop suitable scaffolds with good physiochemical properties and biocompatibility for seeded cells in bone tissue engineering. An ideal scaffold should possess optimal mechanical properties, biocompatibility, and architecture for cell colonization and organization, ensuring the integration of the scaffold with bone tissue [27]. In several previous studies, nHA and ColI were blended together to effectively combine their beneficial properties. In recent years, carbon-based nanomaterials, such as CNTs, carbon nanohorns, and carbon nanodots, have attracted extensive attention as important candidates in the fields of nanomedicine and tissue engineering for their nano-size scale, their high electrical conductivity, and their unique mechanical strength [28, 29]. Cheng et al. [30] previously reported that the incorporation of CNT into PLGA scaffolds facilitates both the proliferation and osteogenic differentiation of MC3T3-E1 osteoblasts. In our study, nHA, ColI, and MWCNT were mixed to develop a new 3D scaffold that provided unique chemical, structural, and mechanical properties for bone tissue engineering and regeneration applications. MWCNT was used to enhance the mechanical strength and biocompatibility of the scaffold [31].

For tissue engineering scaffolds, adequate porosity, a suitable pore size, and interconnecting pores are important for in-growth, cellular adherence, and metabolite transport of cells [32, 33]. In present study, nHACM scaffolds had interconnected pores and a high degree of porosity. Pore sizes of nHACM scaffolds were between 88 and 153 μm, which are an ideal biomaterial to interact and integrate with bone tissue. With the proportion of MWCNT increasing, the compressive strength and compressive modulus of nHACM scaffolds increased, but pore size, porosity, and water absorption decreased. Considering the above characterization, the most appropriate proportion of MWCNT, which is the most suitable for bone tissue engineering, was 1.0%.

There have been considerable investigations into the cytotoxicity of CNTs, with discrepancies reported in terms of its biological effects [34]. For instance, Bottini et al. [35] studied the toxicity of CNTs on human T cells and observed that CNTs could induce T lymphocyte apoptosis in a dose-dependent manner. However, Song et al. [36] found that HA-MWCNTs have a favorable biocompatibility, with no obviously detrimental effects on bone marrow-derived stem cells. The CCK-8 assay was used to evaluate the proliferation of cells seeded on the scaffolds and in the control group in vitro. The activity of cells was demonstrated through absorbance readings of the groups. The 0.5%MWCNT scaffolds exhibited similar proliferative activities to the 1%MWCNT and 1.5%MWCNT scaffolds, with no significant difference in the results. Therefore, taking into consideration the results of the physical characterization and CCK-8 assay, nHACM scaffolds containing 1.0% wt MWCNT were used for subsequent experiments. Compared with BMMSCs cultured without scaffolds in cell culture plates, the cell activity of BMMSCs cultured on the nHACM and nHACM/B9 scaffolds was not decreased. It indicated that nHACM and nHACM/B9 scaffolds were without cytotoxicity to BMMSCs. SEM images showed BMMSCs to be well spread out and integrated within the porous scaffolds, with fully protruded filopodia, confirming that the 3D scaffolds were conducive to cellular anchorage and guided cytoskeletal extensions. It is important to note that a similar phenomenon has been observed in other studies. Valverde et al. [37] showed that biocomposite scaffolds, fabricated by incorporating MTA and/or MWCNT into ColI scaffolds, promoted MC3T3-E1 adhesion, viability, and proliferation. BMP-9 was added to fabricate BMP-9-releasing nHACM scaffolds for bone tissue engineering. The BMP superfamily plays an important role in bone tissue engineering because of their effective osteogenic functions. BMPs are essential in various stages of bone healing [38]. Previous studies have focused on promoting osteogenesis by incorporating BMP-2, which has been shown to be strongly osteoinductive. However, recent studies have found BMP-9 to be more osteogenic than BMP-2 both in vitro and in vivo [39, 40]. Teven et al. [41] investigated the osteogenic potential of BMP-9 on mesenchymal progenitor cells using a recombinant BMP-9-expressing adenovirus (adBMP-9) system and found that BMP-9 effectively facilitates both osteogenic differentiation and new bone formation. Previous studies have employed adenovirus-mediated BMP gene therapy, but there are side effects such as tumorigenesis and immunogenicity [42]. Using biomaterials as carriers may provide controlled and sustained delivery of a growth factor and mimic the temporal profile during bone healing in vivo [43]. ColI and MWCNT, which are widely used as drug delivery systems in tissue engineering and pharmacology [44, 45], were employed together to develop a new system to release BMP-9 in this study. In vitro, analysis of ALP activity indicated that nHACM conferred a stimulatory effect on the differentiation of osteoblasts, especially when loaded with BMP-9. In addition, we found a significant elevation in the expression of osteogenesis-related markers in both nHACM and nHACM/B9 groups when compared with the control group, demonstrating that the composite scaffold can effectively induce the osteogenic differentiation of BMMSCs, even in the absence of BMP-9.

As reported in a previous study, the honeycomb-like scaffolds developed by the combination of poly (D, L-lactic acid) (PDLLA) and MWCNT could effectively promote osteogenic differentiation of osteoblast-like MG-63 cells [46]. Jing et al. [47] characterized composites of ColI-HA and MWCNT-ColI-HA and found that the inclusion of MWCNT increased new bone formation in calvarial bone defects. In the present study, BMMSCs were seeded on nHACM and nHACM/B9 scaffolds, and ColI and MWCNT were employed as the carrier to deliver BMP-9, which were implanted into critically sized rat calvarial bone defects. Blanks (no scaffold and no BMMSCs) were used as controls. CT results showed that the HU of the nHACM/B9+BMMSC group was much higher than that of the other groups. Analysis of CT images also showed that the effect of the nHACM/B9+BMMSCs group was better than that of other groups. These results indicated that the density and area of tissue regenerated in the nHACM/B9+BMMSCs group was the highest, and the osteogenic activity of the nHACM/B9+BMMSC group was the strongest with almost complete closure of bony defects. Histological analysis complemented the CT results. Compared with untreated control defects, nHACM and nHACM/B9 scaffolds with cells enhanced defect closure and mineralization compared with untreated control defects, indicating that the nHACM scaffold itself is osteoconductive. After loading with BMP-9, it can provide an even more effective approach to repair bone defects. Notably, BMP-9 promoted the effect of nHACM scaffolds that possess the potential for use in bone tissue engineering and correcting malunion of fractures. Interestingly, in some specimens, we found a small amount of MWCNT scattered around the new bone at the 12-week post-operative time point. This may be because MWCNT can functionalize as a specific nucleation site and effectively stimulate the initial crystallization of HA. In particular, Xiao et al. [48] demonstrated that MWCNTs acted as core for the growth and nucleation of the apatite crystallites.

5. Conclusions

In this study, a nHACM scaffold was developed by blending and freeze drying, and the proportion of 1.0% wt MWCNT was ideal for bone tissue engineering. The nHACM scaffold was biocompatible and showed no negative effects on rat BMMSCs in vitro. After loading with BMP-9, effects on promoting osteoblast differentiation in vitro and bone formation in vivo were stronger. This scaffold appears to be a suitable candidate for use in bone tissue engineering.

Data Availability

The data used to support the findings of this study are included within the article.

Conflicts of Interest

The authors declare that there are no conflicts of interest regarding the publication of this paper.

Acknowledgments

This study was financially supported by National Natural Science Foundation of China (Grant no. 81600825) and Science & Technology Foundation of Shenyang (17-231-1-50).

Supplementary Materials

Supplementary Figure: (A) To investigate the optimal content of BMP-9 loaded in each nHACM scaffold, ALP activity assay was conducted. BMMSCs were inoculated into the scaffolds with various concentrations of BMP-9 (250ng, 500ng and 750ng). After co-cultured for 1, 4, 7, and 10 days, there was no significant difference between 500ng group and 750ng group, while 500ng group was higher than 250ng group. Mean±SD; n=3; p<0.05, p<0.01, and p<0.001. (B) CCK-8 assays for cell proliferation of BMMSCs that cultured on nHACM scaffolds with various concentrations (0.5, 1, and 1.5% wt). There were no significant differences in cell proliferation among the three groups. Mean±SD; n=3. (C) Cell morphology of BMMSCs in passage 3 examined under an inverted light microscope after cultured for 1, 2, 3, and 6 days. Most of the BMMSCs deformed as triangular or polygonal, and cells density was increasing obviously. (D) The blue parts represent the incomplete closure of the bone defects; the red parts represent the new bone regeneration. The new bone proportion means the red area minus the blue area. (Supplementary Materials)

References

C. M. Teven, S. Fisher, G. A. Ameer, T. He, and R. R. Reid, “Biomimetic approaches to complex craniofacial defects,” Annals of Maxillofacial Surgery, vol. 5, no. 1, p. 13, 2015.

N. Shibuya and D. C. Jupiter, “Bone graft substitute: allograft and xenograft,” Clinics in Podiatric Medicine and Surgery, vol. 32, no. 1, pp. 21–34, 2015.

E. Akbay and F. Aydogan, “Reconstruction of isolated mandibular bone defects with non-vascularized corticocancellous bone autograft and graft viability,” Auris Nasus Larynx, vol. 41, no. 1, pp. 56–62, 2014.

R. Mishra, T. Bishop, I. L. Valerio, J. P. Fisher, and D. Dean, “The potential impact of bone tissue engineering in the clinic,” Journal of Regenerative Medicine, vol. 11, no. 6, pp. 571–587, 2016.

J. O. de Carvalho, F. de Carvalho Oliveira, S. A. Freitas et al., “Carbon nanomaterials for treating osteoporotic vertebral fractures,” Current Osteoporosis Reports, vol. 16, no. 5, pp. 626–634, 2018.

K. M. Alghazali, Z. A. Nima, R. N. Hamzah, M. S. Dhar, D. E. Anderson, and A. S. Biris, “Bone-tissue engineering: Complex tunable structural and biological responses to injury, drug delivery, and cell-based therapies,” Drug Metabolism Reviews, vol. 47, no. 4, pp. 431–454, 2015.

R. Tevlin, A. McArdle, D. Atashroo et al., “Biomaterials for craniofacial bone engineering,” Journal of Dental Research, vol. 93, no. 12, pp. 1187–1195, 2014.

A. Roffi, G. S. Krishnakumar, N. Gostynska, E. Kon, C. Candrian, and G. Filardo, “The role of three-dimensional scaffolds in treating long bone defects: evidence from preclinical and clinical literature - a systematic review,” BioMed Research International, vol. 2017, Article ID 8074178, 13 pages, 2017.

C. V. M. Rodrigues, P. Serricella, A. B. R. Linhares et al., “Characterization of a bovine collagen-hydroxyapatite composite scaffold for bone tissue engineering,” Biomaterials, vol. 24, no. 27, pp. 4987–4997, 2003.

E. Pepla, L. K. Besharat, G. Palaia, G. Tenore, and G. Migliau, “Nano-hydroxyapatite and its applications in preventive, restorative and regenerative dentistry: a review of literature,” Annali di Stomatologia, vol. 25, no. 4, pp. 108–114, 2014.

A. M. Ferreira, P. Gentile, V. Chiono, and G. Ciardelli, “Collagen for bone tissue regeneration,” Acta Biomaterialia, vol. 8, no. 9, pp. 3191–3200, 2012.

S. Iijima, “Helical microtubules of graphitic carbon,” Nature, vol. 354, no. 6348, pp. 56–58, 1991.

L. P. Zanello, B. Zhao, H. Hu, and R. C. Haddon, “Bone cell proliferation on carbon nanotubes,” Nano Letters, vol. 6, no. 3, pp. 562–567, 2006.

N. Narita, Y. Kobayashi, H. Nakamura et al., “Multiwalled carbon nanotubes specifically inhibit osteoclast differentiation and function,” Nano Letters, vol. 9, no. 4, pp. 1406–1413, 2009.

X. L. Li, Y. B. Liu, E. G. Ma, W. X. Shen, H. Li, and Y. N. Zhang, “Synergistic effect of BMP9 and TGF-β in the proliferation and differentiation of osteoblasts,” Genetics and Molecular Research, vol. 14, no. 3, pp. 7605–7615, 2015.

M. Fujioka-Kobayashi, K. Sawada, E. Kobayashi, B. Schaller, Y. Zhang, and R. J. Miron, “Recombinant human bone morphogenetic protein 9 (rhBMP9) induced osteoblastic behavior on a collagen membrane compared with rhBMP2,” Journal of Periodontology, vol. 87, no. 6, pp. e101–e107, 2016.

M. Beederman, J. D. Lamplot, G. Nan et al., “BMP signaling in mesenchymal stem cell differentiation and bone formation,” Journal of Biomedical Science and Engineering, vol. 6, no. 8A, pp. 32–52, 2013.

Q. Kang, M. H. Sun, H. Cheng et al., “Characterization of the distinct orthotopic bone-forming activity of 14 BMPs using recombinant adenovirus-mediated gene delivery,” Gene Therapy, vol. 11, no. 17, pp. 1312–1320, 2004.

G. Chen, Y. Lv, C. Dong, and L. Yang, “Effect of internal structure of collagen/hydroxyapatite scaffold on the osteogenic differentiation of mesenchymal stem cells,” Current Stem Cell Research & Therapy, vol. 10, no. 2, pp. 99–108, 2015.

D. A. Wahl and J. T. Czernuszk, “Collagen-hydroxyapatite composites for hard tissue repair,” European Cell & Materials, vol. 11, pp. 43–56, 2006.

E. Steven, W. R. Saleh, V. Lebedev et al., “Carbon nanotubes on a spider silk scaffold,” Nature Communications, vol. no. 4, p. 2435, 2013.

S. Gholizadeh, F. Moztarzadeh, N. Haghighipour et al., “Preparation and characterization of novel functionalized multiwalled carbon nanotubes/chitosan/β-Glycerophosphate scaffolds for bone tissue engineering,” International Journal of Biological Macromolecules, vol. 97, pp. 365–372, 2017.

X. He, Y. Liu, X. Yuan, and L. Lu, “Enhanced healing of rat calvarial defects with MSCs loaded on BMP-2 releasing chitosan/alginate/hydroxyapatite scaffolds,” PLoS ONE, vol. 9, no. 8, Article ID e104061, 2014.

S. Tong, D. Xu, Z. Liu, Y. Du, and X. Wang, “Synthesis of and in vitro and in vivo evaluation of a novel TGF-β1-SF-CS three-dimensional scaffold for bone tissue engineering,” International Journal of Molecular Medicine, vol. 38, no. 2, pp. 367–380, 2016.

A. R. C. Duarte, J. F. Mano, and R. L. Reis, “Novel 3D scaffolds of chitosan-PLLA blends for tissue engineering applications: preparation and characterization,” The Journal of Supercritical Fluids, vol. 54, no. 3, pp. 282–289, 2010.

R. Langer and J. P. Vacanti, “Tissue engineering,” Science, vol. 260, no. 5110, pp. 920–926, 1993.

A. Ho-Shui-Ling, J. Bolander, L. E. Rustom, A. W. Johnson, F. P. Luyten, and C. Picart, “Bone regeneration strategies: Engineered scaffolds, bioactive molecules and stem cells current stage and future perspectives,” Biomaterials, vol. 180, pp. 143–162, 2018.

L. Niu, H. Kua, and D. H. C. Chua, “Bonelike apatite formation utilizing carbon nanotubes as template,” Langmuir, vol. 26, no. 6, pp. 4069–4073, 2010.

H.-F. Cui, S. K. Vashist, K. Al-Rubeaan, J. H. T. Luong, and F.-S. Sheu, “Interfacing carbon nanotubes with living mammalian cells and cytotoxicity issues,” Chemical Research in Toxicology, vol. 23, no. 7, pp. 1131–1147, 2010.

Q. Cheng, K. Rutledge, and E. Jabbarzadeh, “Carbon nanotube-poly(lactide-co-glycolide) composite scaffolds for bone tissue engineering applications,” Annals of Biomedical Engineering, vol. 41, no. 5, pp. 904–916, 2013.

J. R. Meredith, C. Jin, R. J. Narayan, and R. Aggarwal, “Biomedical applications of carbon-nanotube composites,” Frontiers in Bioscience - Elite, vol. 5, no. 2, pp. 610–621, 2013.

M. E. Gomes, C. M. Bossano, C. M. Johnston, R. L. Reis, and A. G. Mikos, “In vitro localization of bone growth factors in constructs of biodegradable scaffolds seeded with marrow stromal cells and cultured in a flow perfusion bioreactor,” Tissue Engineering, vol. 12, no. 1, pp. 177–188, 2006.

A. Przekora, “The summary of the most important cell-biomaterial interactions that need to be considered during in vitro biocompatibility testing of bone scaffolds for tissue engineering applications,” Materials Science and Engineering C: Materials for Biological Applications, vol. 41, pp. 1036–1051, 2019.

K. Bhattacharya, S. P. Mukherjee, A. Gallud et al., “Biological interactions of carbon-based nanomaterials: From coronation to degradation,” Nanomedicine: Nanotechnology, Biology and Medicine, vol. 12, no. 2, pp. 333–351, 2016.

M. Bottini, S. Bruckner, K. Nika et al., “Multi-walled carbon nanotubes induce T lymphocyte apoptosis,” Toxicology Letters, vol. 160, no. 2, pp. 121–126, 2006.

G. Song, X. Guo, and X. Zong, “Toxicity of functionalized multi-walled carbon nanotubes on bone mesenchymal stem cell in rats,” Dental Materials, vol. 38, no. 1, pp. 127–135, 2019.

T. M. Valverde, E. G. Castro, M. H. S. Cardoso et al., “A novel 3D bone-mimetic scaffold composed of collagen/MTA/MWCNT modulates cell migration and osteogenesis,” Life Sciences, vol. 162, pp. 115–124, 2016.

R. C. de Guzman, J. M. Saul, M. D. Ellenburg et al., “Bone regeneration with BMP-2 delivered from keratose scaffolds,” Biomaterials, vol. 34, no. 6, pp. 1644–1656, 2013.

B. Khorsand, S. Elangovan, L. Hong, A. Dewerth, M. S. D. Kormann, and A. K. Salem, “A comparative study of the bone regenerative effect of chemically modified RNA encoding BMP-2 or BMP-9,” The AAPS Journal, vol. 19, no. 2, pp. 438–446, 2017.

T. Nakamura, Y. Shirakata, Y. Shinohara et al., “Comparison of the effects of recombinant human bone morphogenetic protein-2 and -9 on bone formation in rat calvarial critical-size defects,” Clinical Oral Investigations, vol. 21, no. 9, pp. 2671–2679, 2017.

C. M. Teven, M. T. Rossi, D. S. Shenaq, G. A. Ameer, and R. R. Reid, “Bone morphogenetic protein-9 effectively induces osteogenic differentiation of reversibly immortalized calvarial mesenchymal progenitor cells,” Genes and Diseases, vol. 2, no. 3, pp. 268–275, 2015.

Y. Liu, S. Zhang, G. Ma, F. Zhang, and R. Hu, “Efficacy and safety of a live canine adenovirus-vectored rabies virus vaccine in swine,” Vaccine, vol. 26, no. 42, pp. 5368–5372, 2008.

C. Qi, X. Yan, C. Huang, A. Melerzanov, and Y. Du, “Biomaterials as carrier, barrier and reactor for cell-based regenerative medicine,” Protein & Cell, vol. 6, no. 9, pp. 638–653, 2015.

P. K. Sehgal and A. Srinivasan, “Collagen-coated microparticles in drug delivery,” Expert Opinion on Drug Delivery, vol. 6, no. 7, pp. 687–695, 2009.

S. Boncel, P. Zaja̧c, and K. K. K. Koziol, “Liberation of drugs from multi-wall carbon nanotube carriers,” Journal of Controlled Release, vol. 169, no. 1-2, pp. 126–140, 2013.

E. Silva, L. M. R. D. Vasconcellos, B. V. M. Rodrigues et al., “PDLLA honeycomb-like scaffolds with a high loading of superhydrophilic graphene/multi-walled carbon nanotubes promote osteoblast in vitro functions and guided in vivo bone regeneration,” Materials Science and Engineering C: Materials for Biological Applications, vol. 73, pp. 31–39, 2017.

Z. Jing, Y. Wu, W. Su et al., “Carbon nanotube reinforced collagen/hydroxyapatite scaffolds improve bone tissue formation in vitro and in vivo,” Annals of Biomedical Engineering, vol. 45, no. 9, pp. 2075–2087, 2017.

Y. Xiao, T. Gong, and S. Zhou, “The functionalization of multi-walled carbon nanotubes by in situ deposition of hydroxyapatite,” Biomaterials, vol. 31, no. 19, pp. 5182–5190, 2010.