Characterisation of a novel poly (ether ether ketone)/calcium sulphate composite for bone augmentation
© The Author(s). 2017
Received: 15 February 2017
Accepted: 10 May 2017
Published: 19 May 2017
Calcium sulphate (CS) has been used in bone grafting since the 1800s. It has not replaced autograft as the gold standard, however, since its dissolution occurs rapidly in bodily fluids, meaning that the material cannot support long-term bone growth. Here, the polymer poly (ether ether ketone) (PEEK) was used to slow dissolution in in vitro physiological environments and augment the mechanical properties of the material.
PEEK/CS specimens were fabricated by combining powders of PEEK and CS with water, resulting in a hardening paste. To enhance physical interactions between phases, cylindrical specimens were heat-treated to melt and fuse the PEEK. Following analysis of physical and chemical interactions by SEM and FT-IR respectively, dynamic ageing in PBS and compression testing was undertaken to measure how the PEEK influenced the mechanical properties of the final parts. Changes in structure and chemistry were determined using helium pycnometry, SEM and analysis of powder XRD patterns.
Powders of PEEK and CS hemihydrate (CSH) (CaSO4.0.5H2O) were combined with PEEK at 0 wt%, 2.5 wt%, 20 wt%, 40 wt% and 80 wt% and at a P:L ratio of 0.85 g/mL. The subsequently hardened structures were heat-treated, which initiated the melting of PEEK and dehydration of CSD (CaSO4.2H2O) to the CS anhydrite (CSA) (CaSO4) phase, which changed colour and apparent volume. FT-IR and SEM analysis revealed heat treatment of PEEK/CS specimens facilitated both physical and chemical interactions between phases. Over a period of 21 days of ageing in PBS, the hydration of CS was determined by XRD and improved specimen longevity at all levels of PEEK wt% loading was measured compared with the control. Importantly, increasing PEEK wt% loading resulted in a marked increase in the mechanical properties of PEEK/CS specimens in terms of both compressive strength and modulus.
Reinforcement of CS with PEEK significantly enhanced in vitro dissolution resistance, in addition to enhancing mechanical properties. This composite therefore has significant future potential as a bone graft replacement.
Bone graft materials should support the attachment and proliferation of osteoblast cells, and facilitate the deposition of new hard tissue in bone defects . Ideally, these materials allow for the conduction of new mineral deposition and demonstrate good integration with adjacent bony tissues . Increasingly, synthetic minerals are chosen over bone harvested from patient’s own body. This is despite autologous bone graft being considered the “gold standard” graft material, due to the low risk of immunological rejection associated with its use [3, 4]. The reasons for alternative bone graft selection are that the volume of autologous bone is limited and requires additional surgery to obtain, which poses further risk to a patient in terms of contracting an infection, blood loss and experiencing unnecessary discomfort thereafter . In addition, allograft tissue suffers drawbacks in terms of disease transmission and possible rejection .
Synthetic bioceramic materials, particularly calcium (Ca2+) salts of phosphate (PO4 3−), pyrophosphate (P2O7 4−), sulphate (SO4 2−) and silicate (SiO4 4−) are proven examples of minerals that are able to regenerate areas of removed or diseased hard tissue [5–11]. Moreover, these materials can be employed directly and are available in a variety of forms that includes granules and injectable cementitious pastes, allowing surgeons to select the most appropriate product on a case-by-case basis.
Whilst resorbable graft materials are desirable, CS has been limited in its application since it undergoes rapid dissolution by hydrolytically driven degradation when placed in the body [15–17]. In contrast, biominerals such as hydroxyapatite (Ca5(PO4)3OH) (HA) are considerably less soluble in physiological conditions, offering a more stable network to support bone formation [18, 19]. Given that newly forming bone may take several weeks to fill a defect, these more stable calcium phosphate ceramics are favoured over CS for defect augmentation [6, 13].
Strategies to improve the degradation behavior of CS include combination with less soluble mineral phases and additives to from composites that possess enhanced properties. In combination with β-tricalcium phosphate (β-TCP) CS still undergoes dissolution but the calcium phosphate mineral is able to remain at the implant site for a longer period . Composites containing CS can be modified to adjust degradation rate whilst dampening the production of acidic dissolution products [17, 21]. The addition of other phases can also augment the mechanical properties of the graft materials, with previous work showing that HA addition to CS may significantly enhance mechanical properties . Attempts to combine CS with carboxymethylcellulose and hyaluronan improved mechanical properties of the material but at a cost of faster dissolution .
Standard fabrication of PEEK/CS cylinders
Double Ground Alpha Base Crystacal (calcium sulphate hemihydrate, CSH) (CaSO4.0.5H2O) (Saint-Gobain Formula, France) and 150XF PEEK (Victrex, UK) powders were combined with 0 wt%, 2.5 wt%, 20 wt%, 40 wt% and 80 wt% PEEK by mass. Pastes of each mixture were produced under manual stirring with distilled water acquired from an arium® advance EDI pure water system (Sartorius, Germany) at a powder:liquid (P:L) ratio of 0.85 g/mL, before being poured into a mold to create cylindrical specimens of dimensions 12 mm × 6 mm. The mold was then placed upon a Denstar-500 vibrating plate (Denstar, South Korea) set at high frequency to remove air bubbles. After 10 min, the mold was transferred to an Incu-line incubator (VWR International, UK) at 37°C. After 1 h, specimens were carefully removed from the mold and heated at a ramp rate of 5 oC and held at 380 oC for 2.5 h in a CWF 1300 furnace (Carbolite, UK). Specimens were then stored in ambient conditions.
Cylinder volume of PEEK/CS specimens (n = 3) before heat treatment and following heat treatment was calculated from geometric measurements and % difference determined through calculation (Additional file 1: Equation S1).
Secondary electron scanning electron microscopy (SEM) images of the fracture surfaces were obtained using a Sigma FE-SEM (Zeiss, Germany) operating at 15 kV under vacuum. PEEK/CS specimens with fracture surface exposed were secured firmly upon double adhesive carbon tapes attached to aluminium stubs before and gold coated under vacuum for 2 min using a K550X sputter coater (Quorum Technologies, UK) before images were acquired.
Fourier transform infrared spectroscopy between 500 cm−1 and 4000 cm−1 was undertaken using a Nicolet 380 FT-IR spectrometer (Thermo-Scientific, USA). For sample preparation, 2 mg starting powders and powdered PEEK/CS specimens were mixed with 198 mg KBr (99.99% trace metals basis, Sigma-Aldrich, UK) and pressed into 13 mm diameter discs using a evacuable pellet die (Specac, UK) under a 10 ton force for 30 s with a hydraulic press (Specac, UK).
Dynamic ageing protocol
Ageing was undertaken on n = 33 specimens per composition prepared as standard, with a further n = 10 specimens per composition not subjected to ageing as a control group. Individual PEEK/CS specimens were submerged in 10 mL of calcium and magnesium free Dulbecco’s phosphate buffered saline (PBS) solution (Sigma-Aldrich, UK) in screw cap 60 mL capacity clear vessels. For a fixed set of n = 3 specimens, a daily record of PBS supernatant pH value, wet mass, dry mass, wet height, dry height, wet mid-diameter, dry mid-diameter, wet end-diameter and dry end-diameter was recorded. Supernatant pH values were measured using a S220 SevenCompact™ pH/Ion meter (Mettler Toledo, USA) equipped with InLab Expert Pro-ISM pH electrode (Mettler Toledo, USA). PBS supernatant was drained from every specimen vessel and replenished with a further 10 mL. At 7 day intervals, n = 10 specimens per composition were removed from the ageing protocol until day 21.
Powder X-ray diffraction (XRD) patterns were acquired using a D8 Autosampler Powder Diffractometer (Bruker, USA) with Cu Kα line (0.154 nm). Data was collected between 5 o and 60 o 2θ with a 0.02 o step-size and a step time of 0.5 s/o. Background signal was removed and intensity normalised for each scan. Patterns were matched to those stored by the International Centre for Diffraction Data (ICDD) database.
Apparent specimen density was calculated from geometrical measurements of n = 10 heat-treated PEEK/CS specimens before and during ageing. True specimen density was obtained for the same specimens using an AccuPyc II 1340 helium pycnometer (Micrometrics, USA) over 5 cycles of 5 purges. The relative density and porosity were then calculated (Additional file 1: Equation S2 and S3).
Prior to mechanical testing, geometrical measurements of PEEK/CS specimen diameter and height were made to allow for calculations of contact area and test start height. Compression tests were undertaken on n = 10 specimens per composition with their long-axis perpendicular to the compression platen using a Z030 universal testing rig (Zwick/Roell, USA) equipped with a 50 kN load cell at a compression rate of 2 mm/min until specimen failure. Compressive strength values were determined by converting values of force into stress and plotting stress vs. strain curves from which the maximum value of stress corresponding to specimen failure could be obtained (Additional file 1: Equations S4 and S5, Figure S1). Compressive modulus was determined by obtaining the slope of the aforementioned curves within the elastic region (Additional file 1: Equation S6, Figure S1).
Statistical analysis of data sets was conducted using StatPlus software. One-way ANOVA and post-hoc Turkey honest significant difference (HSD) testing was applied to compare volumetric shrinkage of specimens after heat treatment based on PEEK wt% loading. Two-way ANOVA and post-hoc Turkey HSD testing was applied to compare mechanical data of specimens based on PEEK wt% loading and ageing time. Differences were deemed significant if p < 0.05.
Results and discussion
Physical and chemical assessment of PEEK/CS cylinders
Following addition of water to starting powders a paste was formed, which hardened to form the composite material in accordance with Equation 1. Prior to heat treatment, cylindrical specimens of each composition appeared almost identical up to the point of heat treatment (Fig. 1b). Heat treatment of PEEK/CS specimens initiated melting of PEEK and dehydration of CSD (CaSO4.2H2O) to CSA (CaSO4) (Equation 4). These changes resulted in an alteration in both colour and apparent volume. Starting powders of both CSH (CaSO4.0.5H2O) and PEEK were both cream in colouration. Specimens containing no PEEK (0% PEEK/100%CS) remained similar in appearance after heat treatment. Specimens of 2.5%PEEKCS acquired brown speckles but still retained some cream colouration. Specimens of 20%PEEK/80%CS and 40%PEEK/60%CS became fully brown, whilst specimens of 80%PEEK/20%CS became dark brown. Although the recommended processing temperature for PEEK of 380 oC was employed, polymer chain degradation can still occur leading to discoloration, which was evidently more extensive with greater loadings of PEEK (Fig. 1b).
Volumetric shrinkage of specimens also occurred as a consequence of heat treatment (Fig. 1c). Specimens with PEEK loading between 0 wt% and 40 wt% underwent a volumetric shrinkage of between approximately 9% and 15%. Specimens of 80%PEEK/20%CS however appeared significantly smaller and were confirmed to undergo the greatest extent volumetric shrinkage of 39.7 ± 0.7%. One-way ANOVA analysis confirmed that significant differences in volumetric shrinkage existed between groups based on PEEK wt% loading (F(4,10) = 87.3, p = 9.8x10−8). Post-hoc analysis utilising Turkey HSD tests found no significant differences between groups with PEEK loading between 0 wt% and 40 wt% (p > 0.05), however significant differences did exist between these groups and that of specimens loaded with 80 wt% PEEK (p < 0.001). It is recommended that fractions of CS < 40 wt% are required to maintain volumetric structure that undergoes no significant geometrical changes as a result of melting PEEK compared to unreinforced material.
FT-IR spectra of PEEK contained peaks indicative of the chemical moieties present in its chemical structure (Figs. 1a and 2c), including aromatic and carbonyl groups [27–30]. Peaks associated with aromatic groups are located at 3072 cm−1 and 3034 cm−1 representative of = C-H stretching, and at 1592 cm−1 and 1486 cm−1 due to C = C stretching. Additional peaks at 850 cm−1 and 832 cm−1 are indicative of ring deformation vibrational modes. Peaks corresponding to carbonyl groups are found at 1652 cm−1, 1647 cm−1 and 1257 cm−1. Due to peak overlap at 1652cm−1 and 1647cm−1, separate bands are hard to distinguish, but indicates carbonyl stretching in amorphous and crystalline regions of PEEK respectively.
Vibrational modes of the SO4 2− anion within CSH (CaSO4.0.5H2O) were identified on the corresponding FT-IR spectrum [31–33] (Fig. 2c). A peak at approximately 1010 cm−1 can be assigned to SO3 2− symmetric stretching. Peaks at 1114 cm−1 and 1080 cm−1 are assignable to SO4 2− anti-symmetric stretching, whilst peaks at 658 cm−1 and 596 cm−1 are present due to SO4 2− anti-symmetric bending. Peaks relating to O-H stretching can be found between 3000 cm−1 and 3800 cm−1; peaks in the spectrum of CaSO4.0.5H2O are located at 3603 cm−1 and 3551 cm−1. A singular O-H vibrational band is also present at 1620 cm−1, indicative of CSH (CaSO4.0.5H2O) hydration degree.
Vibrational bands relating to both PEEK and SO4 2− anions are present in the spectrum of 20%PEEK/80%CS. The symmetric stretching peak of SO4 2− remains located at approximately 1010 cm−1, consistent with spectra of both CSA (CaSO4) and CSH (CaSO4.0.5H2O). Substantial reduction of O-H stretching peak intensity between 3000 cm−1 and 3800 cm−1 indicates dehydration of CS phase as expected (Equation 4). The singular O-H vibrational band found at 1620 cm−1 in the spectrum of CSH (CaSO4.0.5H2O) is no longer visible and is instead overlapped by peaks indicative of C = C stretching (1592 cm−1) and carbonyl stretching (1652 and 1647 cm−1) of PEEK polymer chains. Shaping of antisymmetric SO4 2− bending modes between 550 cm−1 and 750 cm−1, consisting of 4 overlapping bands (591 cm−1, 612 cm−1, 667 cm−1 and 671 cm−1) suggests a mixture of CSA (CaSO4) and CSH (CaSO4.0.5H2O). Peaks previously assigned within the FT-IR spectrum of PEEK are visible in the spectrum of 20%PEEK/80%CS including ring deformation peaks at 850 cm−1 and 832 cm−1, the C = C stretching peak at 1592 cm−1 and carbonyl stretching peaks 1652 cm−1 and 1647 cm−1 appeared at a relatively lower intensity, compared to in the spectrum of PEEK starting powder (Fig. 2c). Unexpectedly, this suggests PEEK is able to interact with CSA (CaSO4) not only physically, but also chemically through highly electron rich regions of PEEK polymer, including aromatic rings and carbonyl groups.
Characterisation of dynamically aged PEEK/CS specimens
Powder XRD patterns were acquired in order to assess CS phase changes as a consequence of ageing (Fig. 3d). The powder XRD pattern for PEEK consisted of broad peaks in keeping with PEEK’s semi-crystalline nature. Peaks located at 2θ values of 19 o, 21 o, 23 o and 29 o are in-keeping with those reported in the literature for PEEK . Sharp and narrow peaks within CSH (CaSO4.0.5H2O) pattern indicated a crystalline material that matched to ICDD pattern 01-081-1448. Following heat treatment, the corresponding powder XRD pattern of a 20%PEEK/80%CS specimen contained peaks corresponding to both PEEK and CS phase components, namely CSA (CaSO4) and CSH (CaSO4.0.5H2O) matching ICDD patterns 01-070-0909 and 01-081-1448 respectively. After 7, 14 and 21 days of ageing, powder XRD patterns of 20%PEEK/80%CS specimens possessed peaks corresponding to CSD (CaSO4.2H2O), which were matched to ICDD pattern 00-033-0311, in addition to peaks corresponding to PEEK.
Porosity (%) of PEEK/CS specimens after heat treatment and during ageing (n = 10)
Ageing time (Days)
PEEK content (%)
70.7 ± 3.15
72.1 ± 0.49
73.9 ± 1.3
73.5 ± 1.6
54.6 ± 3.4
65.8 ± 2.4
67.7 ± 1.4
52.0 ± 3.9
68.0 ± 1.0
68.2 ± 2.9
50.0 ± 2.8
65.9 ± 1.7
66.5 ± 1.4
49.7 ± 3.7
Mechanical properties of PEEK/CS specimens
The compressive strength and modulus of CS (typically hydrated CSD (CaSO4.2H2O)) is typically in the range of 10 MPa to 20 MPa and between 3 GPa and 6 GPa respectively when prepared at P:L ratios between 1.5 g/mL and 2 g/mL [39, 40]. Critically, the mechanical properties of CS in this study were several orders of magnitude lower, resulting in compressive strength of 1.2 ± 0.3 MPa and compressive modulus of 0.084 ± 0.1 GPa. Preparation of pastes at P:L ratio of 0.85 g/mL (greater volume liquid fraction) evidently introduces porosity and areas of poor resistance to stress (Table 1). Further optimization of the composite may be enabled by increasing P:L ratio during PEEK/CS fabrication . Furthermore, compressing specimens prior to heat treatment, and preparing pastes under vacuum may both lower the relatively high porosity of structures prior to ageing and provide additional mechanical stability during exposure to in vitro physiological conditions [42, 43].
Mechanism of PEEK reinforcement of CS
We propose that the strengthening and subsequent augmentation of degradation behaviour of PEEK/CS composites is due to enhanced interactions between CS crystals from the physical and chemical intercalation of PEEK following heat treatment. Without PEEK, CS is unable to retain its structure during microstructural and phase transitions initiated by PBS media. 0%PEEK/100%CS specimens likely fall apart from the infiltration of PBS solution that initiates dissolution. Heating the composites containing PEEK allows the polymer content to coat the CS crystal matrix. Even at low loadings of PEEK, such as 2.5 wt%, composites demonstrate enhanced strength and degradation response when compared to 0%PEEK/100%CS. However, the further physiochemical improvements observed at PEEK loadings of at least 20 wt% suggests that at these levels the polymer phase is able to infiltrate the entirety of structures and form a polymeric reinforcing network that binds to crystalline structures. As PEEK does not deteriorate in hydrolytic environments, the PEEK network retains structural dimensions of composites whilst protecting CS crystals from rapid deterioration in PBS media. Additionally, PEEK facilitates microstructural and compositional phase conversion of CS material from CSA (CaSO4) to CSD (CaSO4.2H2O) (Equation 2), which suggests that some CS crystals remain exposed to PBS. Positively therefore, bone-forming cells may still utilise the resorbable CS content available within PEEK/CS composite materials as an osteogenic scaffold for bone deposition.
Acquisition of physical interactions between PEEK and CS was achieved by heating of PEEK/CS specimens. Consequentially, this led to specimen discoloration regarding specimens that contained PEEK, as well as volumetric shrinkage. Excitingly however, evidence of chemical interactions between PEEK with CS through aromatic and carbonyl moieties of the polymer chain were found to exist. The nature of these interactions significantly enhances in vitro dissolution behavior and physical attributes. As such, PEEK can be utilised to fundamentally improve CS attributes directly relevant to bone graft requirements, especially considering large defect volumes that require a protracted presence of osteogenic scaffold and mechanical stability.
SEM was performed at TWI Ltd (Cambridge, UK), who we thank for use of the facilities. XRD was performed at the Advanced Materials Facility (School of Chemistry, University of Birmingham, UK), who we thank for the use of the facilities and for the help provided by Jackie Deans.
The work was funded by the EPSRC (Project 1294393 – medical materials) and was undertaken in association with TWI Ltd (Cambridge, UK).
Availability of data and materials
Supporting information accompanies this article. Supporting evidence includes equations, stress vs. strain curves acquired from mechanical testing, and images of PEEK/CS specimens exposed to physiological conditions.
EABH performed all experimental work and drafted the manuscript. LMG supported the design of experiments and drafted the manuscript. Both authors read and approved the final manuscript.
The authors declare that they have no competing interests.
Consent for publication
The authors approve of the publication of this article.
Ethics approval and consent to participate
No data was collected from humans or animals and as such no ethics approval or consent to participate was required in order to undertake this work.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.
- Hing HA. Bone repair in the twenty-first century: biology, chemistry or engineering? Philos Trans A Math Phys Eng Sci. 2004;362(1825):2821–50.View ArticleGoogle Scholar
- Kumar P, Vinitha B, Fathima G. Bone grafts in dentistry. J Pharm Bioallied Sci. 2013;5 Suppl 1:S125–S7.View ArticleGoogle Scholar
- Shegarfi H, Reikeras O. Bone transplantation and immune response. J Orthop Surg. 2009;17(2):206–11.View ArticleGoogle Scholar
- Figueiredo A, Silva O, Cabrita S. Inflammatory reaction post implantation of bone graft materials. Exp Pathol Health Sci. 2012;6(1):15–8.Google Scholar
- Dorozhkin SV. Calcium orthophosphate bioceramics. Ceram Int. 2015;41(10):13913–66.View ArticleGoogle Scholar
- Hughes E, Yanni T, Jamshidi P, Grover LM. Inorganic cements for biomedical application: calcium phosphate, calcium sulphate and calcium silicate. Adv Appl Ceram. 2015;114(2):65–76.View ArticleGoogle Scholar
- Grover LM, Wright AJ, Gbureck U, Bolarinwa A, Song J, Liu Y, et al. The effect of amorphous pyrophosphate on calcium phosphate cement resorption and bone generation. Biomaterials. 2013;34(28):6631–7.View ArticleGoogle Scholar
- Lee KS, Han HS, Kim YC, Lo Han JH, Seung RH, Lee HS, et al. Evaluation of porous s orphous pyrophosphate on calcium phosphate cement resorption and bone generation. Biomaterinnovations. 2014;19(2):86–90.Google Scholar
- Dressmann H. Ueber Knockenplombierung bei Hohlenforming Defekten des Knochens. Beitr Klin Chir. 1892;9:804–10.Google Scholar
- Clayer M. Injectable Form Of Calcium Sulphate As Treatment Of Aneurysmal Bone Cysts. ANZ J Surg. 2008;78(5):366–70.View ArticleGoogle Scholar
- Liu D, Lei W, Wu Zx, Gao Mx, Wan SY, Fu Sc, Shi L. Augmentation of Pedicle Screw Stability With Calcium Sulfate Cement in Osteoporotic Sheep: Biomechanical and Screw-bone Interfacial Evaluation. Clinical Spine Surgery. 2011;24(4):235–41.Google Scholar
- Orsini G, Ricci J, Scarano A, Pecora G, Petrone G, Iezzi G, et al. Bone-defect healing with calcium-sulfate particles and cement: An experimental study in rabbit. J Biomed Mater Res B Appl Biomater. 2004;68B(2):199–208.View ArticleGoogle Scholar
- Stubbs D, Deakin M, Chapman-Sheath P, Bruce W, Debes J, Gillies RM, et al. In vivo evaluation of resorbable bone graft substitutes in a rabbit tibial defect model. Biomaterials. 2004;25(20):5037–44.View ArticleGoogle Scholar
- Peltier LF, Jones RH. Treatment of unicameral bone cysts by curettage and packing with plaster-of-Paris pellets. J Bone Joint Surg. 1978;60(6):820.View ArticleGoogle Scholar
- Hing KA, Wilson LF, Buckland T. Comparative performance of three ceramic bone graft substitutes. Spine J. 2007;7(4):475–90.View ArticleGoogle Scholar
- Jamali A, Hilpert A, Debes J, Afshar P, Rahban S, Holmes R. Hydroxyapatite/calcium carbonate (HA/CC) vs. plaster of Paris: a histomorphometric and radiographic study in a rabbit tibial defect model. Calcif Tissue Int. 2002;71(2):172–8.View ArticleGoogle Scholar
- Zhou J, Yuan F, Peng S, Xie H, Wu P, Feng P, et al. Tunable Degradation Rate and Favorable Bioactivity of Porous Calcium Sulfate Scaffolds by Introducing Nano-Hydroxyapatite. Appl Sci. 2016;6(12). doi:10.3390/app6120411.
- Liljensten E, Adolfsson E, Strid K-G, Thomsen P. Resorbable and Nonresorbable Hydroxyapatite Granules as Bone Graft Substitutes in Rabbit Cortical Defects. Clin Implant Dent Relat Res. 2003;5(2):95–102.View ArticleGoogle Scholar
- Poinern GEJ, Brundavanam RK, Le Thi X, Nicholls PK, Cake MA, Fawcett D. The synthesis, characterisation and in vivo study of a bioceramic for potential tissue regeneration applications. Sci Rep. 2014;4:6235.View ArticleGoogle Scholar
- Podaropoulos L, Veis AA, Papadimitriou S, Alexandridis C, Kalyvas D. Bone Regeneration Using B-Tricalcium Phosphate in a Calcium Sulfate Matrix. J Oral Implantol. 2009;35(1):28–36.View ArticleGoogle Scholar
- Hu G, Xiao L, Fu H, Bi D, Ma H, Tong P. Study on injectable and degradable cement of calcium sulphate and calcium phosphate for bone repair. J Mater Sci Mater Med. 2010;21(2):627–34.View ArticleGoogle Scholar
- Nilsson M, Fernández E, Sarda S, Lidgren L, Planell JA. Characterization of a novel calcium phosphate/sulphate bone cement. J Biomed Mater Res. 2002;61(4):600–7.View ArticleGoogle Scholar
- Lewis KN, Thomas MV, Puleo DA. Mechanical and degradation behavior of polymer-calcium sulfate composites. J Mater Sci Mater Med. 2006;17(6):531–7.View ArticleGoogle Scholar
- Dandy LO, Oliveux G, Wood J, Jenkins MJ, Leeke GA. Accelerated degradation of Polyetheretherketone (PEEK) composite materials for recycling applications. Polym Degrad Stab. 2015;112:52–62.View ArticleGoogle Scholar
- Kurtz SM, Devine JN. PEEK Biomaterials In Trauma, Orthopedic, And Spinal Implants. Biomaterials. 2007;28(32):4845–69.View ArticleGoogle Scholar
- Kahraman S, Daneyemez M, Kayali H, Solmaz I, Bedük A, Akay M. Polyetheretherketone (Peek) Cages For Cervical Interbody Replacement: Clinical Experience. Turk Neurosurg. 2006;16(3):120–3.Google Scholar
- Ellis G, Naffakh M, Marco C, Hendra PJ. Fourier transform Raman spectroscopy in the study of technological polymers Part 1: poly(aryl ether ketones), their composites and blends. Spectrochim Acta A. 1997;53:2279–94.View ArticleGoogle Scholar
- Henneuse C, Goret B, Marchand-Brynaert J. Surface carboxylation of PEEK film by selective wet-chemistry. Polymer. 1998;39(4):835–44.View ArticleGoogle Scholar
- Henneuse C, Boxus T, Duliere E, Pringalle C, Tesolin L, Adriaensen Y, et al. Surface amination of PEEK film by selective wet-chemistry. Polymer. 1998;39(22):5359–69.View ArticleGoogle Scholar
- Díez-Pascual AM, Martínez G, Gómez MA. Synthesis and Characterization of Poly(ether ether ketone) Derivatives Obtained by Carbonyl Reduction. Macromolecules. 2009;42(18):6885–92.View ArticleGoogle Scholar
- Bensted J, Varma SP. Infrared Spectroscopic Studies of Calcium Sulphate heated to High Temperatures. Z Naturforsch. 1971;26:690–3.View ArticleGoogle Scholar
- Putnis A, Winkler B, Fernandez-Diaz L. In situ IR spectroscopic and thermogravimetric study of the dehydration of gypsum. Mineral Mag. 1990;54:123–8.View ArticleGoogle Scholar
- Fernandez-Carrasco L, Torrens-Martín D, Morales LM, Martínez-Ramírez S. Infrared Spectroscopy in the Analysis of Building and Construction Materials. Infrared Spectroscopy - Materials Science, Engineering and Technology. Rijeka: InTech; 2012.Google Scholar
- Balaji SM. Recent Advances in Oral Surgery. Textbook of Oral & Maxillofacial Surgery. Chennai: Elsevier India; 2007.Google Scholar
- Baradari H, Damia C, Dutreih-Colas M, Laborde E, Pécout N, Champion E, et al. Calcium phosphate porous pellets as drug delivery systems: Effect of drug carrier composition on drug loading and in vitro release. J Eur Ceram Soc. 2012;32(11):2679–90.View ArticleGoogle Scholar
- Shah MR, Patel RR, Solanki RV, Gupta SH. Estimation of drug absorption in antibiotic soaked bone grafts. J Orthop. 2016;50(6):669–76.Google Scholar
- Kameda T, Mano H, Yamada Y, Takai H, Amizuka N, Kobori M, et al. Calcium-Sensing Receptor in Mature Osteoclasts, Which Are Bone Resorbing Cells. Biochem Biophys Res Commun. 1998;245:419–22.View ArticleGoogle Scholar
- Walsh WR, Morberg P, Yu Y, Yang JL, Haggard W, Sheath PC, et al. Response of a calcium sulfate bone graft substitute in a confined cancellous defect. Clin Orthop Relat Res. 2003;406:228–36.View ArticleGoogle Scholar
- Liu W, Wu C, Liu W, Zhai W, Chang J. The effect of plaster (CaSO4.1/2H2O) on the compressive strength, self-setting property, and in vitro bioactivity of silicate-based bone cement. J Biomed Mater Res B Appl Biomater. 2013;101(2):279–86.View ArticleGoogle Scholar
- Koh I, Lopez A, Helgason B, Ferguson SJ. The compressive modulus and strength of saturated calcium sulphate dihydrate cements: implications for testing standards. J Mech Behav Biomed Mater. 2014;34:187–98.View ArticleGoogle Scholar
- Fleming G. Influence of powder/liquid mixing ratio on the performance of a restorative glass-ionomer dental cement. Biomaterials. 2003;24(23):4173–9.View ArticleGoogle Scholar
- Barralet JE, Grover LM, Gbureck U. Ionic modification of calcium phosphate cement viscosity. Part II: hypodermic injection and strength improvement of brushite cement. Biomaterials. 2004;25(11):2197–203.View ArticleGoogle Scholar
- Macaulay W, DiGiovanni CW, Restrepo A, Saleh KJ, Walsh H, Crossett LS, et al. Differences in bone–cement porosity by vacuum mixing, centrifugation, and hand mixing. J Arthroplasty. 2002;17(5):569–75.View ArticleGoogle Scholar