Preparation, characterization, and in vitro osteoblast functions of a nano-hydroxyapatite/polyetheretherketone biocomposite as orthopedic implant material
Authors Ma R, Tang S, Tan H, Lin W, Wang Y, Wei J, Zhao L, Tang T, Pan Y
Received 7 May 2014
Accepted for publication 3 June 2014
Published 18 August 2014 Volume 2014:9(1) Pages 3949—3961
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 4
Rui Ma,1 Songchao Tang,2 Honglue Tan,1 Wentao Lin,1 Yugang Wang,1 Jie Wei,2 Liming Zhao,2 Tingting Tang1
1Shanghai Key Laboratory of Orthopedic Implants, Department of Orthopedic Surgery, Shanghai Ninth People’s Hospital, Shanghai Jiao Tong University School of Medicine, 2Key Laboratory for Ultrafine Materials of Ministry of Education and The State Key Laboratory of Bioreactor Engineering, East China University of Science and Technology, Shanghai, People’s Republic of China
Abstract: A bioactive composite was prepared by incorporating 40 wt% nano-hydroxyapatite (nHA) into polyetheretherketone (PEEK) through a process of compounding, injection, and molding. The mechanical and surface properties of the nHA/PEEK composite were characterized, and the in vitro osteoblast functions in the composite were investigated. The mechanical properties (elastic modulus and compressive strength) of the nHA/PEEK composite increased significantly, while the tensile strength decreased slightly as compared with PEEK. Further, the addition of nHA into PEEK increased the surface roughness and hydrophilicity of the nHA/PEEK composite. In cell tests, compared with PEEK and ultra-high-molecular-weight polyethylene, it was found that the nHA/PEEK composite could promote the functions of MC3T3-E1 cells, including cell attachment, spreading, proliferation, alkaline phosphatase activity, calcium nodule formation, and expression of osteogenic differentiation-related genes. Incorporation of nHA into PEEK greatly improved the bioperformance of PEEK. The nHA/PEEK composite might be a promising orthopedic implant material.
Keywords: polyetheretherketone, nano-hydroxyapatite, biocomposite, osteoblast functions, orthopedic implant material
Hydroxyapatite (HA) ceramics with good biocompatibility and bioactivity have been widely used in clinical applications as bone-repairing materials that can bone-bond with living tissues.1,2 However, due to its brittleness and fatigue failure, HA has been restricted in low load-bearing sites as bone repairing substitute.3 Biomedical polymers, such as polyethylene (PE), polyamide (PA), Poly(ε-caprolactone) (PCL), poly(lactic acid) (PLA), poly(glycolic acid) (PGA), and poly(lactic-co-glycolic acid) (PLGA), have been used to fabricate different types of bone implant and tissue engineering scaffolds, owing to their good biocompatibility and malleable nature.4–6 Nevertheless, none of these mentioned polymers is bioactive, which means that the newly formed bone tissues cannot bond tightly to the polymer surfaces.
To obtain bone implant materials with good bioactivity and the appropriate mechanical properties, the introduction of HA into polymers to fabricate inorganic/organic composites has been highlighted.7–9 In this respect, HA-reinforced PE composite has been successfully developed for clinical application.10 Following the concept of incorporating bioactive materials into polymers to increase the bioactivity and mechanical properties of polymers, many composites containing bioactive materials (such as bioglass, HA, and tricalcium phosphate) and polymers (such as PA, PLA, and PCL) have been developed to prepare bone substitutes.11–13
“Polyetheretherketone” (PEEK) is a bone-implant material currently used in orthopedic applications.14 Although PEEK has good biocompatibility and mechanical properties, its lack of bioactivity may limit its use in bone-repair applications.15 Previous studies have reported that the addition of micron-sized HA into PEEK may improve the bioactivity of the resultant HA/PEEK composite, and that the bioactivity of the composite seems to increase with increasing HA content.16–18 Li et al fabricated a nano-hydroxyapatite (nHA)-incorporated PEEK composite by powder processing and sintering, and their results suggested that the composite possessed good bioactivity and biocompatibility.19
To the best of our knowledge, no previous studies have reported the in vitro osteoblast responses (such as cell attachment, spreading, proliferation, and osteogenic differentiation of a pre-osteoblastic cell line [MC3T3-E1]) to the nHA/PEEK composite. In this study, nHA/PEEK composite was fabricated by incorporating nHA into a PEEK matrix through a process of compounding, injection, and molding. The mechanical properties, surface morphology, chemical composition, surface roughness, and hydrophilicity of the composite were characterized. The in vitro osteoblast functions of the composite were studied by detecting cell attachment, spreading, proliferation, and osteogenic differentiation of MC3T3-E1 cells.
Materials and methods
Preparation of nHA
Calcium nitrate (Ca(NO3)2·4H2O; Sigma-Aldrich, St Louis, MO, USA) and ammonium phosphate ((NH4)3PO4·3H2O; Sigma-Aldrich) were separately dissolved in aqueous solution. The calcium nitrate solution was dropped slowly into the ammonium phosphate solution while the solution was stirred and heated to 70°C. The pH value of the solution was maintained between 10 and 12 by adding ammonium hydroxide (NH4OH; Sigma-Aldrich). The chemical reaction formula was:
When the reaction ended, nHA precipitate was obtained and thoroughly washed with deionized water, after which dimethylformamide (DMF; Sigma-Aldrich) was added gradually. The water in the precipitate solution was removed above 100°C; thus, the solvent became essentially DMF. Finally, the temperature was increased to 120°C and held for 2 hours. This procedure produced nHA, which was finally dried at 100°C for 12 hours to obtain nHA powder. The size and morphology of the nHA particles were characterized by transmission electron microscopy (TEM) using a JEM-100CX transmission electron microscope (JEOL, Tokyo, Japan).
Preparation of nHA/PEEK composite
PEEK powder with a mean particle size of 20 μm was obtained from Victrex Manufacturing Ltd (Rotherham, UK). A process involving compounding, injection, and molding was used to prepare the nHA/PEEK samples containing 0, 20, 40, and 60 wt% nHA content. The PEEK and nHA powders were compounded in a QM-3B High-Speed Vibrating Ball Mill (Nanjing T-Bota Scietech Instruments & Equipment Co Ltd, Nanjing, People’s Republic of China) at a mixing speed of 500 rpm for 1 hour. Following this, the mixtures were then dried at 150°C for 24 hours. The samples were produced using a Battenfeld BA-300/050CD injection-molding machine (Awans, Belgium) at an injecting and molding temperature of 380°C.
“Ultra-high-molecular-weight polyethylene” (UHMWPE) is a commonly used prosthesis material in artificial hip and knee joints, so UHMWPE was chosen to serve as a control in cell tests. A UHMWPE slab with a molecular weight of 2 million was purchased from Röchling Engineering Plastics Ltd. (Munich, Germany). All samples were cut into 2 mm thick disks with diameters of 15 or 34 mm.
The mechanical properties (elastic modulus, tensile strength, and compressive strength) of the samples were measured using an Instron 5,567 material testing machine (Norwood, MA, USA) at a crosshead speed of 0.1 mm·min−1 according to ASTM International standard D790. The average of five readings for each sample was presented. All measurements were made in air at room temperature. By evaluating the mechanical properties of the nHA/PEEK composites with different nHA contents, we determined the optimal nHA content was 40 wt%, so this was selected to perform the other experiments in this study.
Surface morphology and chemical composition
The surface morphology and chemical composition of the nHA/PEEK composites were characterized by scanning electron microscopy (SEM; S-4800, Hitachi, Tokyo, Japan) and X-ray diffraction (XRD; Geigerflex, Rigaku Co, Akishima, Japan) with Cu Kα radiation (1.5405 Å).
Surface roughness and hydrophilicity
The surface roughness was measured as the average roughness (Ra) and root mean square roughness (Rq) using a HommelWerke T1000 surface roughness tester (Braunschweig, Germany). To determine the surface hydrophilicity, the sessile drop method was employed to measure the static water contact angle, using distilled water as the media, on a Ramé-Hart 290 Automated Goniometer/Tensiometer (Succasunna, NJ, USA) at ambient temperature. Five measurements were taken on different parts of each sample.
“MC3T3-E1” is a mouse pre-osteoblast cell line derived from mouse calvaria, and was chosen for this research to study the interaction between cells and materials in vitro. MC3T3-E1 cells were cultured in Dulbecco’s Modified Eagle’s Medium (DMEM) supplemented with 10% fetal bovine serum (FBS), 1% penicillin (100 U·mL−1), and streptomycin sulfate (100 mg·mL−1), all from Thermo Fisher Scientific (Waltham, MA, USA) at 37°C in a humidified atmosphere of 5% CO2 and 95% air. The culture medium was changed every 3 days. For all the cell experiments, samples of the nHA/PEEK composite with 40 wt% nHA (Φ 15 mm) were used, and the PEEK and UHMWPE samples were used as controls.
To study the attachment of MC3T3-E1 cells on the material surfaces, cell counting kit-8 (CCK-8) assay was performed to analyze the numbers of attached cells on material surfaces cultured for 6, 12, and 24 hours. Before seeding the cells, three disks for each group were put into the wells of a Costar 24-well plate (Corning Incorporated, NY, USA). The cell suspension was seeded into each well at a density of 3×104 viable cells per cm2 of sample, with DMEM as a blank control. The culture plates were incubated at 37°C in a humidified atmosphere of 5% CO2. At each time point, the samples were gently rinsed with phosphate-buffered saline (PBS) to remove the unattached cells then transferred to a new 24-well plate, and 50 μL CCK-8 solution (Dojindo Molecular Technologies Inc., Kumamoto, Japan) was added to each well. The plates were then incubated for 3 hours. At the end of this period, 100 μL of the supernatant was transferred into a 96-well plate. The plates were then read at 450 nm (with 620 nm as the reference wavelength) using a Synergy HT microplate reader (Bio-Tek Instruments Ltd, Winooski, VT, USA). The mean optical density (OD) obtained from the blank control was subtracted from the ODs of the test groups.
Cell spreading was investigated by detecting the filamentous actin of the cytoskeleton of MC3T3-E1 cells. After 24 hours of incubation, the samples were washed gently three times with PBS to remove the unattached cells. Then the cells on the samples were fixed with 4% paraformaldehyde for 15 minutes at room temperature and permeabilized with 0.1% Triton X-100 in PBS for 10 minutes. After washing three times with PBS, the cells were stained with rhodamine-phalloidin (5 units·mL−1; Biotium, Hayward, CA, USA) for 30 minutes and then washed three times with PBS. The cytoskeleton was visualized by confocal laser scanning microscopy using a Leica Microsystems TCS SP2 (Heidelberg, Germany).
Cell spreading was also observed with SEM. After 24 hours, the cells on the samples were fixed with 2.5% glutaraldehyde for 15 minutes before being washed gently three times with PBS. Then the cells were dehydrated with gradient ethanol (30%, 50%, 70%, 90%, 100%, and 100% for 10 minutes each time). Finally, all the samples were air-dried at room temperature, sputter-coated with gold, and observed with SEM.
CCK-8 assay was used to study the proliferation of the MC3T3-E1 cells on the samples. The detailed procedures were nearly identical to the procedures for the cell attachment test. The differences were that the seeding density of the cells was 1×104 viable cells per cm2, and the time points were 1, 3, and 7 days. Similar to the cell seeding procedures of the cell proliferation test, the cells on the samples were also stained with 4,6-diamidino-2-phenylindole (DAPI, 0.1 μg·mL−1; Sigma-Aldrich) for 15 minutes after being cultured for 1, 3, and 7 days. After DAPI staining, the cells were observed using a fluorescence microscope (Leica AF 6000, Heidelberg, Germany). For quantitative analysis of DAPI staining, five representative images were selected for each group and the cells numbers were counted using GraphPad Prism® software (v 5.0; La Jolla, CA, USA). The MC3T3-E1 cells cultured for 3 and 7 days on the samples were also observed by SEM.
Cell culture of inductive osteogenesis
Specimens (Φ 34 mm) were placed into a six-well plate then seeded with MC3T3-E1 cells at a density of 3×104 viable cells per cm2. After co-incubation with the samples for 24 hours, the culture medium was changed to the osteogenic inductive medium, which contained DMEM supplemented with 10% FBS, 1% penicillin (100 U·mL−1), streptomycin sulfate (100 mg·mL−1), 100 nm dexamethasone (Sigma-Aldrich), 50 μg·mL−1 ascorbic acid (Sigma-Aldrich), and 10 mm β-glycerophosphate sodium (Sigma-Aldrich). The osteogenic inductive medium was replaced every 2 days.
Alkaline phosphatase (ALP) staining and ALP activity assay
After 7, 10, and 14 days of culturing in the osteogenic inductive medium, ALP staining was performed following our previously published procedure.20 ALP activity was determined by quantifying the amount of p-nitrophenol, the yellow-colored end product of hydrolysis of p-nitrophenyl phosphate, using an ALP microplate test kit (Nanjing Jiancheng Bioengineering Institute, Nanjing, People’s Republic of China). The quantity of ALP in the cell lysates was measured at 405 nm using the Synergy HT microplate reader, while the total protein content was determined using a BCA protein assay kit (Thermo Fisher Scientific) according to the provided protocol. Finally, the ALP activity was normalized to the corresponding total protein content.
Alizarin-red staining and quantitative analysis
After osteogenic induction for 21 and 28 days, the samples were washed three times with PBS and fixed in 4% paraformaldehyde for 15 minutes before being stained with 1% alizarin-red solution (pH 4.2; Sigma-Aldrich) for 45 minutes at room temperature. Next, the samples were washed with deionized water until the deionized water did not appear orange, then dried at 37°C.
Additionally, the samples with no cells were stained with 1% alizarin-red solution as just described. For the quantitative analysis of alizarin-red staining, the orange dye was dissolved in 10% cetylpyridinium chloride (Sigma-Aldrich) in 10 mm sodium phosphate (pH 7.0; Sigma-Aldrich), and the OD values were measured at 620 nm using the microplate reader.21 The mean ODs obtained from the samples with no cells were subtracted from the ODs of each test group.
Expression of osteogenic differentiation-related genes
The expression of MC3T3-E1 osteogenic differentiation-related genes on the samples was quantitatively determined by real-time polymerase chain reaction (PCR). Messenger ribonucleic acid (mRNA) levels of mouse ALP, type I collagen (COL1), osteopontin (OPN), and osteocalcin (OC) were evaluated and normalized to the transcript levels of the housekeeping gene b-actin. The sequences of the forward and reverse primers, and the lengths of the products for the osteogenic differentiation-related genes are shown in Table 1. The quantification of gene expression was based on the cycle threshold (CT) values of each measurement. After osteogenic induction for 7, 14, and 21 days, the total RNA was collected from the cell lysates using Trizol reagent (Invitrogen, Carlsbad, CA, USA) according to the manufacturer’s protocol. One microgram of the total RNA from each sample was added to the oligo(dT)18 primers, heated at 65°C for 5 minutes then cooled on ice for 1 minute before reaction buffer, RNase-inhibitor, deoxy-ribonucleoside triphosphate (dNTP), and reverse transcriptase were added according to RevertAid First Strand cDNA Synthesis Kit (Thermo Fisher Scientific) protocol. Quantitative real-time PCR was undertaken using a SYBR premix EX TaqTM PCR kit (Takara Biotechnology Co Ltd, Dalian, People’s Republic of China). PCR amplification was performed in triplicate for each group in an independent PCR amplification and repeated in two independent experiments.
Table 1 Primers used in this study
All data are presented as the means ± standard deviations. All experiments were repeated three times. Statistical analysis was performed using a two-way analysis of variance (ANOVA) test to determine the presence of any significant differences between different groups, and multiple comparisons were performed using the least significant difference (LSD) test to determine any significant differences between each pair of groups. P<0.05 was considered statistically significant, and P<0.01 was considered highly statistically significant. All statistical analyses were performed using SPSS software (v 13.0; IBM Corp, Armonk, NY, USA).
TEM of nHA
Figure 1 is a TEM image of nHA. It can be seen that the prepared nHA exhibited a rod-like morphology with an average length of 80 nm and diameter of 10 nm.
Figure 1 Transmission electron microscope image of nano-hydroxyapatite.
Mechanical properties of the composite
Table 2 shows the mechanical properties of the nHA/PEEK composite with different contents of nHA. The elastic modulus and compressive strength of the composite increased with increasing nHA content from 0 to 40 wt%. The highest nHA content (60 wt%) yielded a lower elastic modulus (3.9 MPa) and compressive strength (89 MPa) than the composite containing 40 wt% nHA. The composite containing 40 wt% nHA resulted in the highest elastic modulus (4.6 MPa) and compressive strength (160 MPa), indicating that the addition of nHA into PEEK improved the mechanical properties to a point. Further, the tensile strength of the composites decreased slightly as nHA content increased and was lower than that of PEEK.
Table 2 Mechanical properties of the nano-hydroxyapatite/polyetheretherketone (nHA/PEEK) composite with different nano-hydroxyapatite (nHA) contents
SEM and XRD of the composite
Figure 2 presents an SEM image and the XRD pattern of the nHA/PEEK composite. Many high-electron-density nHA particles were found uniformly distributed on the composite’s surface (Figure 2A). Figure 2A presents the XRD pattern of the nHA/PEEK composite. The diffraction peaks of the composite at around 2θ =25.5°, 32°, 33°, 40°, and 49.5° ascribe to the characteristic peaks of HA,22 while the two peaks at around 2θ =21° and 22.5° are the characteristic peaks of PEEK.23 The results indicate that the composite contained both the nHA and PEEK.
Figure 2 Scanning electron microscope image (A) and X-ray diffraction pattern (B) of the nano-hydroxyapatite (nHA)/polyetheretherketone (PEEK) composite.
Surface roughness and the hydrophilicity of the composite
Table 3 shows the surface roughness of the nHA/PEEK composite and PEEK. The Ra and Rq of the composite were 0.118 and 0.183, and those of PEEK were 0.063 and 0.095, respectively. The results indicate that, compared with PEEK, the Ra and Rq of the composite increased by 87% and 93%, respectively. Figure 3 shows the results of the water contact angles of the nHA/PEEK composite and PEEK, which were 51° and 74°, respectively. These results indicate that the hydrophilicity of the composite was significantly improved compared with PEEK (P<0.01).
Figure 4 illustrates the numbers of attached cells on the nHA/PEEK composite, PEEK, and UHMWPE. The number of cells attached to the composite was significantly higher than the numbers on PEEK and UHMWPE after 12 and 24 hours (P<0.05). This indicates that the addition of nHA into PEEK improved cell attachment on the composite.
Figure 5A shows the cytoskeleton of MC3T3-E1 cells observed by confocal laser scanning microscopy after culture for 24 hours. The cells on the nHA/PEEK composite exhibit clustering, confluent, and multilayer morphology with more actin filaments linking adjacent cells, whereas the cells on PEEK and UHMWPE appear dispersive and monolayer, with fewer actin filaments. Figure 5B presents the SEM images of MC3T3-E1 cells after 24 hours. The cells on the nHA/PEEK composite surface spread well; the cells were polygonal, with numerous pseudopods anchored to the material’s surface. In contrast, on PEEK and UHMWPE, cell spreading appeared less efficient; the cells were rod-like, with fewer pseudopods.
Figure 6 presents the proliferation of MC3T3-E1 cells cultured on the nHA/PEEK composite, PEEK, and UHMWPE as determined by CCK-8 assay. The cell numbers on the composite increased significantly from 1 to 7 days. In addition, the cell numbers on PEEK and UHMWPE increased obviously from 3 to 7 days and from 1 to 3 days, respectively (P<0.05). However, the cell numbers on PEEK and UHMWPE exhibited no significant increase from 1 to 3 days and from 3 to 7days, respectively (P>0.05). Figure 6B indicates that the cells on the composite exhibited a higher relative proliferation rate than on PEEK at 3 days and UHMWPE at 7 days (P<0.05). Further, the relative proliferation rate of MC3T3-E1 cells on the nHA/PEEK composite was a little less than on PEEK at 7 days, but no significant difference existed between them (P>0.05).
The qualitative and quantitative analysis of DAPI staining of MC3T3-E1 cells cultured on the nHA/PEEK composite, PEEK, and UHMWPE is shown in Figure 7. The results indicate that more cells grew on the composite than on PEEK and UHMWPE at each time point (P<0.01).
Figure 8 presents the SEM images of cells cultured on the samples at 3 and 7 days. The cells on the nHA/PEEK composite spread better than on PEEK and UHMWPE at 3 days. Further, the cells on the composite and PEEK spread well and covered almost the entire material’s surface at 7 days, whereas the cells on UHMWPE were in a poor state and exhibited no apparent proliferative trend from 3 to 7 days.
Figure 8 Scanning electron microscope images of MC3T3-E1 cells on the samples at 3 and 7 days.
ALP staining and ALP activity
Figure 9A illustrates the ALP staining of the MC3T3-E1 cells cultured on the samples. The ALP staining became stronger with induction time on all samples, and the staining on the nHA/PEEK composite was considerably stronger than on PEEK and UHMWPE at each time point. Figure 9B shows the ALP activity of the MC3T3-E1 cells cultured on the samples. The ALP activity on the composite was significantly higher than on PEEK and UHMWPE on days 7, 14, and 21.
Alizarin-red staining and quantitative analysis
Figure 10A shows the alizarin-red staining of the MC3T3-E1 cells cultured on the samples. The alizarin-red staining on the nHA/PEEK composite was clearly stronger than on PEEK and UHMWPE at 21 and 28 days. Figure 10B shows the quantitative analysis of the alizarin-red staining of the MC3T3-E1 cells on the samples. The results indicate that the calcium nodule-formation of the cells on the composite was significantly more than on PEEK and UHMWPE at 21 and 28 days (P<0.01).
Expression of osteogenic differentiation-related genes
Figure 11 shows the expression of osteogenic differentiation-related genes of MC3T3-E1 cells cultured on the samples. The mRNA of ALP for the composite was obviously higher than PEEK and UHMWPE at 7 and 14 days, and the mRNA of OC for the composite was obviously higher than PEEK and UHMWPE at 21 days. Moreover, the mRNA of COL1 for the composite was obviously higher than PEEK and UHMWPE at 14 and 21 days, and the mRNA of OPN for the composite was obviously higher than UHMWPE at 14 and 21 days.
In this study, a bioactive composite of nHA/PEEK was prepared by introducing nHA into PEEK using a process of compounding, injection, and molding. The SEM and XRD results show that the nHA particles were uniformly distributed on the PEEK matrix.
After the incorporation of nHA into PEEK, the elastic modulus and compressive strength mechanical properties of the nHA/PEEK composite (from 0 to 40 wt%) increased obviously, while the tensile strength decreased slightly when compared with PEEK. In the composite system, the compressive strength and elastic modulus of the composite containing 40 wt% nHA were significantly higher than in those containing 20 wt% and 60 wt%, suggesting that a weight ratio of about 40 wt% would be optimal. Composites containing a high nHA content (for example, 60 wt%) resulted in a dramatic reduction in the mechanical strength of the composite. Therefore, the composite with 40 wt% nHA was chosen for other investigations in this study.
The biocompatibility of a biomaterial is affected by its surface characteristics, such as surface roughness and hydrophilicity.24 In this study, the results revealed that the Ra and Rq of the nHA/PEEK composite were 87% and 93%, respectively, greater than those of PEEK, indicating that the incorporation of nHA into PEEK obviously increased the surface roughness of the composite. The rougher surface of implant biomaterials may exert a positive influence on the proliferation and differentiation of osteoblasts.25,26 Hydrophilic testing revealed that the water contact angles of nHA/PEEK and PEEK were 51° and 74°, respectively, indicating that addition of nHA into PEEK enhanced the hydrophilicity of the composite. Contact angle depends on many factors, for instance, surface roughness, surface chemistry, and grain size.27 Because nHA is more hydrophilic as an inorganic material than PEEK, and the nHA/PEEK composite is rougher than PEEK, the improvement in hydrophilicity seen with the nHA/PEEK composite may stem from changes in the surface roughness and chemistry,27,28 which may have affected the functions of the osteoblasts in this study.
Cell attachment is the first step in the interaction of cells with substrate materials, which can affect cell growth and proliferation on the biomaterial surfaces.29,30 It has been reported that the attachment of fibroblasts on the biomaterials is more evident on hydrophilic surfaces than hydrophobic ones.31 In this study, the nHA/PEEK composite significantly promoted the attachment of the MC3T3-E1 cells compared with PEEK and UHMWPE, which may be due to the composite’s increased surface hydrophilicity and roughness. The nHA/PEEK composite possessed a hydrophilic surface that facilitated cell attachment, whereas PEEK had a relatively hydrophobic surface that limited cell attachment. Additionally, the surface roughness of the composite favored the adsorption of greater amounts of protein, thereby promoting the attachment of osteoblasts.32 In this study, cells spread well on the composite, with more actin filaments and pseudopods compared with on PEEK and UHMWPE, indicating good biocompatibility and bioactivity. This could be attributed to the hydrophilic surface of the composite, and it has been reported that the actin fibers of fibroblasts are evident on hydrophilic surfaces than on hydrophobic ones.31
After attaching to the material surfaces, the MC3T3-E1 cells enter a proliferation stage. Our results show that the nHA/PEEK composite could promote the proliferation of MC3T3-E1 cells, as compared with PEEK and UHMWPE. Studies have shown that HA can stimulate the cell proliferation of human and animal osteoblasts.33 Thus, the active effect on the cell proliferation of the composite was mainly attributed to the biological benefits of nHA. Further, the surface roughness and hydrophilicity of biomaterials have been reported to positively influence the proliferation potential of MG-63 cells (a human osteosarcoma cell line).34 Therefore, the increased surface roughness and hydrophilicity of the composite also favored cell proliferation on the composite.
After attachment and proliferation, the cells on the biomaterial surfaces further differentiate to synthesize collagen and other proteins, and induce their own in vitro mineralization in certain culture medium conditions.35 ALP is a marker for the early differentiation of osteoblasts; it regulates the inorganic phosphate metabolism by hydrolyzing phosphate esters and functions as a plasma membrane transporter for inorganic phosphates.36 Alizarin-red staining is commonly used to detect the formation of calcium nodules (mineralization) – formed by osteoblasts in the late stage of differentiation – in osteoblast cultures.37 In the present study, the MC3T3-E1 cells on the composite exhibited higher ALP activity and more calcium nodule-formation than PEEK and UHMWPE, indicating that the composite could promote the cell differentiation of MC3T3-E1 cells.
To further study osteogenic differentiation, real-time PCR was used to monitor the changes in the expression levels of osteogenic differentiation-related genes (ALP, COL1, OPN, and OC) of the MC3T3-E1 cells on the composite and the PEEK and UHMWPE controls. The MC3T3-E1 cells cultured on the composite exhibited a significantly higher expression of ALP at 7 and 14 days than on PEEK and UHMWPE, which was in accordance with the results of ALP activity quantification. OC expression on the composite was significantly higher than on PEEK and UHMWPE at 21 days, consistent with the results of the mineralization measured by quantification of alizarin-red staining. In addition, the composite exhibited higher expression of COL1 at 14 and 21 days compared with PEEK and UHMWPE. These results indicate that the nHA/PEEK composite can promote the osteogenic differentiation of the MC3T3-E1 cells. HA is bioactive and can promote the osteogenic differentiation of osteoblasts,33 especially nHA.38 A study has reported that a rougher surface of the substrate material improves the differentiation of osteoblasts;25 therefore, the promotion of the osteogenic differentiation of the MC3T3-E1 cells on the nHA/PEEK composite was mainly due to the biological benefits of nHA and the rougher surface of the composite.
In the study reported here, a bioactive composite of nHA/PEEK was prepared through a process of compounding, injection, and molding. The results show that nHA was uniformly distributed on the PEEK matrix, and the mechanical properties (elastic modulus and compressive strength) of the composite were significantly increased compared with those of PEEK. In addition, the surface roughness and hydrophilicity of the nHA/PEEK composite increased due to the introduction of nHA into PEEK. In the evaluation of the osteoblast functions on material surfaces, the nHA/PEEK composite was found to promote cell attachment, spreading, proliferation, and osteogenic differentiation with higher ALP activity, increase calcium nodule-formation, and generate higher expression levels of osteogenic differentiation-related genes compared with PEEK and UHMWPE. The bioactive nHA/PEEK composite may have potential in orthopedic applications.
This research was financially supported by the National Natural Science Foundation of China (numbers 31271015, 81271705, and 51173041) and the Shanghai Science and Technology Development Fund (numbers 13DZ2294000, 13JC1403900, 12nm0500400, and 12441903600).
The authors declare no conflicts of interest in this work.
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