Development of a PCL/gelatin/chitosan/β-TCP electrospun composite for guided bone regeneration
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Many approaches have been developed to regenerate biological substitutes for repairing damaged tissues. Guided bone/tissue regeneration (GBR/GTR) that employs a barrier membrane has received much attention in recent years. Regardless of substantial efforts for treatment of damaged tissue in recent years, an effective therapeutic strategy is still a challenge for tissue engineering researchers. The aim of the current study is to fabricate a GBR membrane consisting of polycaprolactone (PCL)/gelatin/chitosan which is modified with different percentages of β-tricalcium phosphate (β-TCP) for improved biocompatibility, mechanical properties, and antibacterial activity. The membranes are examined for their mechanical properties, surface roughness, hydrophilicity, biodegradability and biological response. The mechanical properties, wettability and roughness of the membranes are improved with increases in β-TCP content. An increase in the elastic modulus of the substrates is obtained as the amount of β-TCP increases to 5% (145–200 MPa). After 5 h, the number of attached cells is enhanced by 30%, 40% and 50% on membranes having 1%, 3% and 5% β-TCP, respectively. The cell growth on a membrane with 3% of β-TCP is also 50% and 20% higher than those without β-TCP and 5% β-TCP, respectively. Expression of type I collagen is increased with addition of β-TCP by 3%, while there is no difference in ALP activity. The results indicated that a composite having (3%) β-TCP has a potential application for guided bone tissue regeneration.
KeywordsGuided bone regeneration Electrospinning β-Tricalcium phosphate (β-TCP) Composite membrane
Serious traumas and infections may result in different types of defects in bone tissue. Several therapeutic and surgical approaches have been used for the repair and regeneration of alveolar bone such as distraction osteogenesis (Ilizarov 1989), bone grafts (Branemark 1983), osteoinduction (Reddi et al. 1987) and guided bone regeneration (GBR) (Chiapasco et al. 2009; Hämmerle and Karring 1998). Among these methods, GBR, a surgical procedure that employs a barrier membrane, has the most predictable results for regeneration of bone tissue into the defect site. The membrane acts as a physical barrier to create an excluded space around the defect by preventing the invasion of fibrous connective and epithelial tissues into the defect which allows bone tissue to regenerate naturally (Dahlin et al. 1989; Xu et al. 2012). Common materials that are used for fabrication of barrier membranes can be divided into non-absorbable polytetrafluoroethylene (e-PTFE) (Lindfors et al. 2010; Lu et al. 2012; Urban et al. 2009), titanium mesh (Degidi et al. 2003) and bio-absorbable (collagen, chitosan (Coïc et al. 2009; Jiang et al. 2015), poly(glycolic acid) (PGA), poly(lactic acid) (PLA), poly(ε-caprolactone) (PCL) (Schmidmaier et al. 2006) inorganic ceramics (Kinoshita et al. 2008). For a successful bone regeneration, barrier membranes should possess some fundamental requirements including biocompatibility, biodegradability, sufficient mechanical strength, space maintenance, manageability and adhesiveness toward surrounding bone tissues (Gottlow 1993; Smith et al. 2009). To have a membrane that meets these requirements, a combination of two or more polymers should be used.
Many researchers have investigated GBR membranes which are fabricated from a combination of different polymers. Ke Ren et al. (2017) reported an improved cell adhesion and proliferation on nanofibrous PCL/gelatin GBR membrane made by the electrospinning process due to an increased wettability. Sarasam et al. (2005) used PCL/chitosan membrane that improved the mechanical properties and cell viability compared to pure chitosan. Chen et al. made biodegradable poly(L-lactide) (PLLA)/chitosan membranes for guided periodontal tissue regeneration and found that modification of chitosan could promote hydrophilicity, enhance cell proliferation and accelerate the degradation rate of PLLA electrospun membranes (Cao et al. 2013). A β-tricalcium phosphate (β-TCP)–collagen composite membrane has been reported to hold greater osteoconductivity and better biodegradation properties than commercial Bio-Oss collagen membrane (Kato et al. 2014). Lam et al. investigated the degradability of a PCL/β-TCP scaffold in comparison to pure PCL which revealed that addition of β-TCP could decrease the surface wettability which in turn resulted in increased degradability of the scaffold (Heidemann et al. 2001).
These studies clearly show that by taking advantage of two or more polymers, higher osteoconductivity, biodegradability and better mechanical properties could be achieved. Gelatin has several superior properties such as good biocompatibility, low immunogenicity, good tissue integration and hemostatic property, which makes it a great material for GBR membranes (Jiang et al. 2015; Postlethwaite et al. 1978). Chitosan, as a suitable natural polymer candidate, possesses many advantages such as low cost, biocompatibility, biodegradability, weak immunogenicity and most importantly antimicrobial characteristics (Kong et al. 2010; Mota et al. 2012; Xu et al. 2012). However, chitosan exhibits low mechanical strength (Hürzeler et al. 1998; Ko et al. 2010) and a high degradation rate (Kong et al. 2010). PCL has been also extensively investigated in bone tissue engineering due to its good biocompatibility, biodegradability and good mechanical properties, but displays low wettability (Bosworth and Downes 2010), poor cell adhesion (Kim et al. 2006; Li et al. 2006) and slow biodegradation rate (Jeong et al. 2004; Li et al. 2006).
Although chitosan/PCL, gelatin/PCL and PCL/TCP membranes have been studied previously, there is no report on PCL/gelatin/chitosan membrane that particularly formed composites with β-TCP in GBR applications. In this study, composite substrates by combining poly(ε-caprolactone), gelatin, chitosan and different ratios of β-TCP (0, 1%, 3% and 5% w/v) were fabricated by the electrospining method. β-TCP is added to the substrates as it has demonstrated good osteoinductivity, excellent biocompatibility and bioactivity (Zhou and Lee 2011). β-TCP can also serve as a precursor for Ca2+ and PO43− ions that encourage new bone formation (Lam et al. 2007). The characteristics of fabricated substrates including mechanical properties, elemental makeup, surface roughness and wettability are examined. In vitro cell culture experiments by human osteoblast-like cells MG63 are performed to evaluate cell adhesion, proliferation, alkaline phosphatase activity and collagen I gene expression on the surface of composite samples. Also, in vitro degradation behavior, antibacterial activity and bacterial adhesion of samples are investigated.
Materials and methods
Chitosan (medium molecular weight), polycaprolactone (PCL) (Mn 80,000 g/mol), gelatin and β-TCP (particle size < 0.063 µm) were purchased from Sigma-Aldrich. Dulbecco’s Modified Eagle Medium (DMEM). MTT [3-4,5-dimethylthiazol-2yl(-2,5diphenyl-2H-tetrazoliumbromide)], fetal bovine serum (FBS), acetic acid and formic acid were purchased from Sigma-Aldrich.
The PCL (5% w/v) solution was prepared in acetic acid/formic acid (1:1, v/v) solvent mixture by stirring the mixture at 500 rpm for 2 h, and gelatin (5% w/v) was dissolved in acetic acid/formic acid (1:1, v/v) by stirring the mixture at 500 rpm for 3 h. Similarly, chitosan solution (3% w/v) was prepared in acetic acid at 500 rpm for 2 h. All the polymeric solutions were prepared at room temperature (37 ± 1 °C). After preparation of polymeric solutions, PCL (40 wt%), gelatin (40 wt%) and chitosan (20 wt%) were mixed to obtain a stock solution. Different ratios of β-TCP (0, 1%, 3% and 5% w/v) were added to the final uniform polymeric solution under slow magnetic stirring for 24 h. After 24 h, an immiscible polymeric blend of PCL/gelatin/chitosan/β-TCP was obtained which was used for electrospinning.
Nanofibrous substrates from PCL/chitosan/gelatin/β-TCP (0, 1%, 3% and 5%) were fabricated using electrospinning (ES). The polymer blend of PCL, chitosan, gelatin and β-TCP (0, 1%, 3% and 5%) was loaded into a 5 mL plastic syringe with a 22G× 32 mm needle and injected using a syringe pump. The flow rate of the polymer solution was maintained at 0.9 mL/h. A high voltage of 10 kV was applied at the tip of the needle and a distance of 10 cm between needle and collector was sustained throughout the process. The electrospinning process was carried out at 25 ± 1 °C and humidity of 45%. Substrates were collected on a flat aluminum plate and cross-linked with EDC and N-hydroxyl succinimide (NHS). Next, 2.5 mM EDC and 1.25 mM NHS were dissolved in ethanol/PBS solution (80/20) and the substrates were placed in the prepared solution for 1 h. Cross-linked substrates were washed thoroughly with deionized water to remove excess EDC/NHS. All the samples were gamma-sterilized for 2 h prior to biological experiments and referred as PGC (PCL/chitosan/gelatin), PGCT1 (PCL/chitosan/gelatin plus 1% β-TCP), PGCT3 (PCL/chitosan/gelatin plus 3% β-TCP) and PGCT5 (PCL/chitosan/gelatin plus 5% β-TCP).
Composite sample characterization
After fabrication of composite samples, surface wettability, surface roughness, mechanical properties, chemical composition and morphology were characterized. The surface wettability of PGC, PGCT1, PGCT3 and PGCT5 was determined by measuring the contact angles of deionized water on each sample using a surface analysis system equipped with Image Analyzer software (OCA 15 plus; Data physics(. An autopipette was used to ensure a uniform volume of water droplets (0.5 µL). The experiments were run at room temperature on four membrane samples at three different times. The surface roughness of the samples was evaluated through AFM) Auto; Probe; Veeco (in tapping mode. The mechanical properties of the substrates were analyzed with a universal materials machine at room temperature with a cross-head speed of 5 mm/min. Rectangular samples with dimensions of 3 × 0/5 cm2 were prepared (n = 5) and used for the measurements. The elemental composition of each sample’s surface was evaluated using an energy-dispersive X-ray spectrometer (EDAX) to explore calcium and phosphate presence and distribution of particles. Chemical analysis of all components was performed by Thermo Nicolet FTIR (Nexus, USA) spectroscopy over a range of 4000 and 500 cm−1. The morphology of PGC, PGCT1, PGCT3 and PGCT5 membrane samples was examined using (EM3200/KYKY) scanning electron microscopy (SEM). Before imaging, samples were coated with gold for 30 min using a sputter coater for 60 s at an accelerating voltage of 12 kV. Fiber diameter of samples was studied based on SEM images at 5000× magnification. Five images were used for each sample and 40 different fibers were randomly selected. The average fiber diameter was calculated using Image Analysis software (Image J, NIH, USA). The pore size of fabricated samples was also analyzed based on SEM images.
MG63 osteoblast-like cell line was used for this study and cultured in DMEM supplemented with 10% fetal bovine serum (FBS) and 1% penicillin/streptomycin at 37 °C in a 5% CO2. The culture medium was changed every 2 days. For biological experiments, cultured cells were detached by trypsinization, suspended in new culture medium and used for designed experiments.
Cell attachment and proliferation
MTT assays determine the ability of mitochondrial dehydrogenases enzymes of living cells to oxidize a tetrazolium salt [3-(4,5-dimethylthiazolyl-2-y)-2,5 diphenyltetrazolium bromide] into an insoluble purple formazan product. The concentration of the purple formazan product was directly proportional to the number of metabolically active cells. MTT assay was performed to study the attachment and proliferation of MG63 cells on PGC, PGCT1, PGCT3 and PGCT5 samples. The sterilized samples were placed in a 48-well culture plate and seeded with 50,000 cell/mL for adhesion and 15,000 cell/mL for proliferation and incubated for different time points for each test (2, 4 and 6 h for adhesion, 1, 3 and 7 days for proliferation). Cells cultured in culture plates were used as control. After each time point, the samples were transferred into a new culture plate and washed with phosphate-buffered saline (PBS) to remove the unattached cells. Freshly prepared media of complete DMEM and 10 µl of MTT solution (5 mg/mL stock in 1 × fresh medium) were added into each well to make a final volume of 100 µL. The plate was placed in a CO2 incubator for 3 h until purple color of formazan crystals was formed. After 3 h, the formazan crystals were dissolved in solubilizing solution and transferred into a 96-well plate. The absorbance was measured at a wavelength of 570 nm with subtraction of 650 nm background using a UV–Vis spectrophotometer. A standard curve was drawn to estimate the cell number.
Cell morphology of MG63 on PGC, PGCT1, PGCT3 and PGCT5 substrates was studied by SEM analysis. Sterilized membrane samples were placed in 48-well culture plates and seeded with 4 × 103 cells and incubated for 2 days. Following the incubation period, samples were rinsed three times with PBS and fixed with 2.5% glutaraldehyde, dehydrated with gradient concentration of ethanol (30, 40, 50, 60, 70, 80, 90 and 100%). Finally, they were air-dried overnight sputter-coated with gold and examined with scanning electron microscopy (SEM; EM3200) for investigating cell morphology.
DNA content of grown cells
DNA quantification was performed to study the cell growth on PGC, PGCT1, PGCT3 and PGCT5 substrates. The samples were placed in 48-well culture plate, seeded with 15 × 103 cells and incubated for 1, 3 and 5 days. After the incubation period, samples were rinsed with PBS and DNA content of cells was isolated with lysis buffer (10%Triton X-100, 5% Tween 20, 100 m mol−1 Tris–Hcl (pH 8), 10 mmol−1 EDTA). A NanoDrop 1000 spectrophotometer (Thermofisher, USA) was used to calculate the total DNA content of cells based on the read at absorbance wavelength of 260 nm.
Roughness and contact angle measurement of samples
34.55 ± 0.56
52.55 ± 1.2
32.42 ± 0.11
61.12 ± 1.8
26.78 ± 0.34
69 ± 1.3
25.54 ± 0.48*
79.24 ± 1.4**
Antibacterial activity of the membranes
In this study, the antibacterial activity of the PGC, PGCT1, PGCT3 and PGCT5 membrane samples was evaluated by agar disc diffusion method against E. coli and S. aureus. For disc diffusion, bacteria suspension with concentration in the range of 1.5 × 108 UFC/mL was seeded by swabbing evenly in three directions to form a lawn. Sterile samples with 9 mm diameter along with control disc were placed on the surface of each inoculated MHA (Mueller–Hinton agar). The plates were incubated at 37 °C for 24 h and inhibition zones were observed.
Microbial adhesion (accumulation) and connectivity on a substrate can be observed by scanning electron microscopy (SEM). For this purpose, substrates were exposed to bacterial suspension for 6 and 72 h. After each time point, the samples were washed with PBS, fixed with 2.5% glutaraldehyde for 24 h, dehydrated in graded ethanol series (30, 40, 50, 60, 70, 80, 90 and 100), dried in a vacuum oven overnight, sputter-coated with gold and examined with scanning electron microscopy (SEM; EM3200).
In vitro degradation and swelling
Changes in the sample weights and pH during in vitro degradation tests were measured. After 4 weeks, samples were removed from the solution and morphological evaluation of the samples was done with SEM.
All data are presented as the mean ± SD of at least three experiments. Statistical analysis was performed with GraphPad Prism software (GraphPad, San Diego, CA, USA) using a two-way ANOVA followed by Tukey’s multiple comparison test. The results were considered statistically significant when p < 0.05.
Results and discussion
The water contact angles of the substrates are presented in Table 1. The results clearly show that surface wettability was significantly increased with increase in β-TCP concentration (Fig. 1). The contact angle of the samples is considered one of the physical parameters which could relate the affinity of cells and proteins onto a surface.
Cell attachment and proliferation
Cell proliferation on the membrane samples was also evaluated through MTT assay and DNA content measurement after cultivation of cells for 1, 3 and 7 days (Fig. 5b). After 1 day of culture, the number of cells on PGC was lower compared to other samples. After 3 days, PGCT3 and PGCT5 showed slightly higher cell number and DNA concentration than PGC and PGCT1 membranes. After 7 days of culture, the cell number on PGCT3 was significantly higher than that of PGCT5. These results suggested that 3% w/v of β-TCP could have a positive effect on the proliferation rate of the cells in longer periods of culture) Fig. 5c).
Oligonucleotide primers used for PCR amplification
Primer sequence: sense/antisense
Collagen type 1
ALP (alkaline phosphatase activity)
5′-ACTCCCATCTCCTTA CCT CT-3′
Figure 8 shows the scanning electron microscopy (SEM) micrographs of the bacterial adhesion after 6 h and 72 h. In all samples, no significant difference in S. aureus and E. coli adhesion on different substrates was detected. However, bacterial adhesion was increased as the amount of β-TCP was increased after 72 h and a large population of bacteria was observed on the samples. Bacterial adhesion to biomaterial surfaces can lead to bacterial infections, which can be difficult to treat with antibiotics (Al-Ahmad et al. 2011). Generally, it is accepted that due to the enhanced contact area, as a result of increase in surface roughness, bacterial adhesion may be promoted. However, it is important to note that the size and shape of bacterial cells and other environmental factors can play a crucial role in bacterial adhesion and biofilm formation (Renner and Weibel 2011). In a similar study using PLLA/TCP scaffolds, it has been observed that addition of TCP unexpectedly could decrease bacterial adhesion (Al-Ahmad et al. 2011). Xing et al. (2015) found that bacterial adhesion on TiZr dental implant abutment is highly correlated to the surface roughness. In contrast, Lin et al. (2013) observed that increase in the roughness of ceramic surfaces could not assist biofilm formation of S. mutans. These conflicting results may be due to the levels of roughness, bacterial strain, culture conditions and distinctive material compositions (Song et al. 2015).
In vitro degradation and swelling
Swelling is another consideration when fabricating a scaffold for tissue regeneration, as it influences the absorption of body fluids, the transfer of cell nutrients, and metabolites throughout the materials and can generate unnecessary stress on surrounding tissues (Jin et al. 2015). The results showed that the swelling of samples was stable after 3 h (Fig. 9g). However, β-TCP enhanced hydrophilicity and swelling of the samples, but the swelling with 5% β-TCP decreased compared to other samples. This can be related to the cross-linking effect of β-TCP (Aryaei et al. 2015). It has been found that with increase in β-TCP concentration; more cross-linked networks would form between polymeric chains which in turn reduce the substrate pore size. This probably has a negative influence on the degree of water intake by the substrates (Khan and Ranjha 2014).
Calcium phosphate-based composite materials have been investigated as a superior candidate for bone regeneration in GTR/GBR. In this study, different PCL/chitosan/gelatin membrane samples by addition of various amounts of β-TCP were fabricated to investigate their biocompatibility and osteogenic properties for potential GTR/GBR applications. The results showed that MG63 cell attachment, proliferation rate, morphology, type I collagen gene expression, degradation rate and swelling as well as mechanical properties were optimized in a sample containing 3% β-TCP. It was found that the amounts of β-TCP used in this study could create no significant antibacterial effect on the composite samples. In summary, PCL/chitosan/gelatin/β-TCP substrate with 3% β-TCP would be considered a promising material candidate for generation of bone in GBR applications.
This study was funded by the National Institute of Genetic Engineering and Biotechnology (Grant No: M-470).
Compliance with ethical standards
Conflict of interest
The authors declare that there is no conflict of interest in this study.
This article does not contain any studies with human participants or animals performed by any of the author.
- Chiapasco M, Casentini P, Zaniboni M (2009) Bone augmentation procedures in implant dentistry. Int J Oral Maxillofac Implant 24:237–259Google Scholar
- Dahlin C, Sennerby L, Lekholm U, Linde A, Nyman S (1989) Generation of new bone around titanium implants using a membrane technique: an experimental study in rabbits. Int J Oral Maxillofac Implant 4:19–25Google Scholar
- Ilizarov GA (1989) The tension-stress effect on the genesis and growth of tissues: part I. The influence of stability of fixation and soft-tissue preservation. Clin Orthop Relat Res 238:249–281Google Scholar
- Jin RM, Sultana N, Baba S, Hamdan S, Ismail AF (2015) Porous pcl/chitosan and nha/pcl/chitosan scaffolds for tissue engineering applications: fabrication and evaluation. J Nanomater 16:138Google Scholar
- Reddi AH, Wientroub S, Muthukumaran N (1987) Biologic principles of bone induction. Orthop Clin N Am 18:207–212Google Scholar
- Urban IA, Jovanovic SA, Lozada JL (2009) Vertical ridge augmentation using guided bone regeneration (GBR) in three clinical scenarios prior to implant placement: a retrospective study of 35 patients 12 to 72 months after loading. Int J Oral Maxillofac Implant 24:502–510Google Scholar
- Zhang R, Ma P (2001) Composite scaffolds for bone tissue engineering: degradation. In: 47th Annual meeting, Orthopaedic Research Society, San FranciscoGoogle Scholar
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