Evaluation of the Morphology and Osteogenic Potential of Titania-Based Electrospun Nanofibers

Wang, Xiaokun; Zhu, Jingxian; Yin, Ling; Liu, Shize; Zhang, Xin; Ao, Yingfang; Chen, Haifeng

doi:https://doi.org/10.1155/2012/959578

Journal of Nanomaterials

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Volume 2012 | Article ID 959578 | https://doi.org/10.1155/2012/959578

Evaluation of the Morphology and Osteogenic Potential of Titania-Based Electrospun Nanofibers

Xiaokun Wang,¹Jingxian Zhu,²Ling Yin,¹Shize Liu,¹Xin Zhang,²Yingfang Ao,²and Haifeng Chen¹

Academic Editor: Krasimir Vasilev

Received08 Feb 2012

Accepted03 Apr 2012

Published06 Jun 2012

Abstract

Submicron-scale titania-based ceramic fibers with various compositions have been prepared by electrospinning. The as-prepared nanofibers were heat-treated at 700°C for 3 h to obtain pure inorganic fiber meshes. The results show that the diameter and morphology of the nanofibers are affected by starting polymer concentration and sol-gel composition. The titania and titania-silica nanofibers had the average diameter about 100–300 nm. The crystal phase varied from high-crystallized rutile-anatase mixed crystal to low-crystallized anatase with adding the silica addition. The morphology and crystal phase were evaluated by SEM and XRD. Bone-marrow-derived mesenchymal stem cells were seeded on titania-silica 50/50 fiber meshes. Cell number and early differentiation marker expressions were analyzed, and the results indicated osteogenic potential of the titania-silica 50/50 fiber meshes.

1. Introduction

The design and preparation of nanoscale fine structures have attracted great attention because of their potential unique properties and applications. The electrospinning technique has been reported to be a simple and versatile method to produce fibrous structure with nanoscale to microscale dimensions from synthetic and natural polymers [1–5]. Moreover, the principles of electrospinning technique have been expanded to the ceramic and metal oxide systems [6–9]. The morphology and properties of the nanofibers depend on the concentration of polymer solutions, solvent, applied electric field strength, and deposition distance [10–12].

There are many studies focusing on applying electrospun fibrous scaffolds to bone tissue engineering [13, 14]. Most of the electrospun scaffolds are made of polymers or polymer-ceramic nanoparticle composite, and a few studies have been done on pure ceramic scaffolds [15–18]. Titania is well known as biocompatible surface of titanium implants, and, as the major component of bioglass, silica is also considered to have good biology performance. A number of methods have been applied to produce titania-silica nanostructures, including the sol-gel process [19], plasma-spraying [20], and chemical vapor deposition [21]. Many previous studies of nanostructured titania-silica materials focus on their optical properties, high thermal stability, and high surface area properties, and this material has been widely used as optical chemical sensors [22], supporting materials [23], and catalysts [24]. In the aspect of their biology performance, most of the applications of nanostructured titania-silica materials in the field of biomedical engineering are using titania-silica as coating material or fillers for composite scaffolds [25–29].

Recent research has showed that electrospun titania nanofibers have the osteoinductive potentials, and the effects of surface roughness on MG63 osteoblast-like cells were also discussed [30]. However, few researches are available that give an insight into how titania-silica nanofibers influence cell responses. Therefore, the aim of this study is to characterize the morphology of electrospun titania-based fibers and evaluate bone-derived mesenchymal stem cell (MSC) responses and osteoinductivity of titania-silica fibers to determine their potential application as a scaffold material for bone tissue engineering.

2. Materials and Methods

2.1. Fabrication of Titania and Titania-Silica Nanofibers

The titania and titania-silica fibrous meshes were prepared from titanium(IV) isopropoxide (TiP), tetraethyl orthosilicate (TEOS), poly(vinyl pyrrolidone) (PVP, ), and acetic acid. In a typical procedure, 0.5 mL of TiP was mixed with 0.5 mL ethanol and 0.5 mL acetic acid. After 10 min stirring, the sol was added to 1.5 mL 6% and 10% PVP ethanol solution, followed by magnetic stirring for 30 min. The starting solution of titania-silica fibers was made of sol containing 0.25 mL of TiP and 0.25 mL TEOS mixed with 0.5 mL ethanol and 0.5 mL acetic acid. Then the sol was added to 1.5 mL 10% PVP ethanol solution. In the electrospinning setup, the collection distance was 10 cm, and the applied voltage was 8 kV. The electrospun fibers were collected on the flat plate. Finally, the PVP was removed from these fibers by heating them in air at 700°C for 3 h.

Sample topography and cell morphology were examined by scanning electron microscopy (Hitachi S-4800) using a 15 kV accelerating voltage. Fiber diameter distribution was evaluated by image analysis software (ImageJ, NIH software) from three SEM images of at least two different samples. Fiber diameter was evaluated from at least 150 fibers at 16,000x magnification.

The chemical composition of the scaffolds was examined by XPS (Axis Ultra by Kratos Analytical Ltd.) of at least two different samples with 3 spots per sample. Additionally, crystal structure X-ray diffraction (XRD) was investigated by RAPID-S (Rigaku Denkico Co., Ltd.)

2.2. Cell Culture

Bone-derived mesenchymal stem cells were extracted from two lower extremities of a Wistar rat with approval of the animal ethics committee of the Peking University Third Hospital. Briefly, the adherent soft tissues of bones were cleaned, and epiphyses were removed with a scissor. The marrow was harvested by inserting a syringe needle (16-gauge) into each end of the bone and flushing repeatedly with phosphate-buffered saline (PBS) supplemented with 100 U/mL penicillin and streptomycin into a 100 mm culture dish. Cell suspension was obtained by drawing the marrow into a 20 mL syringe through 22-gauge needles. The cells were then centrifuged, counted, seeded at a density of 1 × 10⁶ in 8 mL of α-MEM (Minimal Essential Medium) with 10% fetal bovine serum (FBS), 100 U/mL penicillin, and streptomycin per 100 mm culture dish, and cultured at 37°C in a humidified atmosphere of 95% air and 5% CO₂. Nonadherent cells were removed at 3 days after seeding by changing the medium; thereafter, the medium was changed every 3 days. Cells of the 3rd to the 5th passage were used for further study.

For cell culture on the titania-silica 50/50 meshes, MSCs were cultured in osteogenic media, containing Dulbecco’s modified Eagle medium, containing 10% fetal bovine serum (FBS) and 1% penicillin and streptomycin, 0.1 μmol/L dexamethasone, 10 mmol/L β-sodium glycero-phosphate, and 50 μmol/L ascorbic acid phosphate, at 37°C in 5% CO₂ and 100% humidity. Cells were grown on 12-well plate tissue culture polystyrene and titania-silica 50/50 meshes, at a density of 10,000 cells/cm². MSCs were fed every 48 h and harvested at Day 3 and Day 7. RNA was extracted by using Qiagen’s RNeasy Mini Kit and reverse-transcribed by using the Qiagen-Omniscript RT kit as per the manufacturer’s directions. RT-PCR and Real time PCR were performed for Runx2 (NCBI accession no. NM_009820.2) and ALP (NCBI accession no. NM_007431). Optimal oligonucleotide primers were designed by using Primer Express 2.0 software and purchased from Sigma-Geosys. Data were normalized to the endogenous reference gene GAPDH (NCBI accession no. NM_008084).

3. Results

Figure 1 shows the SEM images of electrospun fibers. These images reveal that fibers have diameters varying from around 100 nm to 300 nm. Under lower magnification (Figures 1(a), 1(c), and 1(e)), fibers in each group were evenly distributed in general, and higher-magnification images (Figures 1(b), 1(d), and 1(f)) revealed more detailed structures of the fiber. Comparing Figures 1(b) and 1(d), it is observed that the average diameter of fibers increases with the increasing starting polymer concentration. Also, even using the same concentration of starting polymer, pure titania meshes have thicker fibers than titania-silica 50/50 hybrid meshes (Figures 1(d) and 1(f)). Beside the diameter, the existence of silica also has influences on fiber surface morphology. Figure 1(d) shows that pure titania fibers form of titania crystal clusters and the titania-silica 50/50 fibers (Figure 1(f)) have smoother surfaces.

(a)

(b)

(c)

(d)

(e)

(f)

Figure 2 shows the diameter distribution of calcined fibers analyzed by ImageJ. It confirms the observation of SEM images, which is 6% PVP titania fibers, and 10% PVP titania-silica 50/50 fibers have thinner diameter than 10% PVP titania fibers.

Chemical analysis by XPS (Table 1) showed no N, indicating PVP was removed thoroughly by the heat treatment. 6% PVP and 10% PVP titania fiber meshes were generally composed by Ti, O, and small amount of silica as well. The titania-silica 50/50 fiber mesh has Ti, Si, and O, and the ratio of Ti to Si was 1 : 1, consistent with the initial molar ratio of TiP to TEOS.

Typical XRD patterns of titania fibers and titania-silica 50/50 fibers with heat treatment are shown in Figure 3. Two groups of titania fibers have similar spectra, which is presented in Figure 3(a). The peaks of rutile and anatase crystal structures were found in the two groups of pure titania fibers. For titania-silica 50/50 fibers, only the peaks of anatase were found and the peak intensity of hybrid fibers was also weaker than that of pure titania fibers.

(a)

(b)

MSC morphology on titania-silica 50/50 fiber meshes was observed by SEM and confocal microscope. The cells grew throughout the surfaces with elongated morphology (Figures 4(a) and 4(b)). Cell number on fibrous mesh groups was lower than that on TCPs. However, Runx2 and alkaline phosphatase gene expressions were affected in the opposite way, with cells on the hybrid mesh groups having the higher level of relative gene expression (Figures 5(a)–5(c)). In general, the cell behavior was sensitive to the fibrous surface.

(a)

(b)

(a)

(b)

(c)

4. Discussion

In this study, pure titania and titania-silica 50/50 ceramic fibrous meshes were made by electrospinning process, and MSC responses on titania-silica fibers were evaluated.

Factors which can influence the fiber diameter and fiber morphology of electrospun nanofibers were discussed in previous studies [10, 11]. The concentration of starting polymer solution is the most commonly used method to adjust the electrospun fiber diameter. Generally, increasing polymer concentration is one of the major methods to increase electrospun fiber diameter [11]. For the pure ceramic electrospun fibers which need heat treatment to remove the polymer component, the sol-gel content and calcination temperature can also contribute to fiber morphology [31]. SEM images show that 10% PVP titania meshes have thicker fiber diameter than 6% PVP titania meshes; the result is consistent with previous study [30]. When silica is added into the sol-gel system, even with the same concentration of starting polymer and same gel content, the fiber diameter is thinner than pure titania fibers. In addition, the addition of silica had influence on fiber surface morphology, too. The surface of titania-silica fiber is smoother than that of pure titania fiber. This result is further supported by XRD spectrum, which shows that titania-silica has lower degree of crystallization under the same calcination temperature. After heating up to 700°C for 3 h, two groups of pure titania fibers formed rutile-anatase mixed crystals while titania-silica 50/50 fibers formed not well-crystalized anatase crystals. Similar results were reported by heating the mixture of silica and titania nanoparticles [32], which shows that the addition of silica affects crystal phase transformation of titania-silica particles. XPS results with the lack of N support the point that PVP was removed during calcination and the substrates are composed of silica and titania. The small amount of silica in titania fibers may be caused by calcining the fiber meshes on a silicon wafer.

Cell number on the meshes was affected by the fibrous structure of the titania-silica meshes, which had lower cell number than TCPs. This effect of fibrous surfaces and rough surfaces on cell number has been previously reported by many studies for Ti/TiO₂ surfaces that promote osteoblast or MSCs differentiation toward osteoblast [30, 33, 34]. Beside cell number, the differentiation of MSCs was also affected by surface structure. Runx2, a transcription factor belonging to the Runx family, determines the osteoblast lineage from multipotent MSCs. Runx2 induces osteoblastic differentiation at early stage [35]. The relative gene expression of Runx2 of this study is significantly higher than control. Also alkaline-phosphatase-specific activity, which is also an early marker of osteogenic differentiation, was significantly higher in titania-silica 50/50 when compared to the TCP control. The cell results show that titania-silica 50/50 fiber meshes have osteogenic potential.

5. Conclusion

In this study, submicron-scale composite fiber titania-based ceramics with various compositions have been prepared by electrospinning. Pure ceramic fibers were obtained by heat treatment at 700°C for 3 h. SEM images showed that the diameter and morphology of the nanofibers were influenced by starting polymer concentration and sol composition. The titania and titania-silica nanofibers have the average diameter around 100~300 nm. The fiber surface morphology and crystal phase were influenced by silica content. Bone-marrow-derived MSCs were seeded on titania-silica 50/50 fiber meshes. Cell number and early differentiation marker expressions were analyzed, and the results indicate osteogenic potential of the titania-silica 50/50 fiber meshes. In conclusion, the present work has shown that both the morphology and crystal phase of titania-based electrospun nanofibers are able to be controlled by starting polymer concentration and chemical composition. And these titania-based electrospun nanofibers may have potential use as a new scaffold material for bone tissue engineering.

Acknowledgments

The work is supported by the Ministry of Science and Technology of China (Grants 2012CB933903, 2011AA030102) and the Wallace H. Coulter Foundation.

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Copyright © 2012 Xiaokun Wang 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.

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