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Bioceramics Development and Applications
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Sol-Gel Fabrication of Glass-Ceramic Composite Materials for Dental Application

X. Chatzistavrou,1 D. Esteve,1 E. Hatzistavrou,2 E. Kontonasaki,3 K. M. Paraskevopoulos,2* and A. R. Boccaccini1

1Department of Materials, Imperial College London, Exhibition Road, London SW7 2AZ, UK

2Physics Department, Aristotle University of Thessaloniki, 54124 Thessaloniki, Greece

3School of Dentistry, Aristotle University of Thessaloniki, 54124 Thessaloniki, Greece

*Corresponding Author:
K. M. Paraskevopoulos
E-mail: [email protected]

Received date: 14 January 2011; Accepted date: 3 February 2011

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composite materials; sol-gel technique; bioactivity; coating; FTIR; SEM; DTA


Dental ceramics used in restorative dentistry exhibit a combination of properties such as durability in the oral environment, resemblance with natural tooth structure, high strength, fracture toughness and wear resistance [1]. These stringent requirements have led to further research in the field of dental ceramics in order to further develop improved materials with improved properties and bioactive function. The sol-gel process involves synthesis of materials by exploiting the transition of a system from the liquid phase to a porous solid allowing the fabrication of new inorganic materials with controlled mictrostructure and properties. One of the significant advantages of the sol-gel method is the ability to synthesize silicate glasses at low sintering temperature enabling the preparation of glass-ceramics with special compositions which are not possible to be obtained by melting [4].

This work investigates the application of the sol-gel technique for the fabrication of glass-crystalline composite materials with potential use in dental restorations. These composite materials aim to create a bioactive surface around the margins of fixed restorations which could lead to periodontal tissue attachment, providing complete sealing of the marginal gap between tooth and fixed prosthesis.

Materials and methods

Two composite materials were fabricated. The first composite (COMP1) was fabricated by modifying the sol-gel bioactive glass 58S through the incorporation of a commercial porcelain (IPS Classic Margin, Ivoclar, Schaan, Liechtenstein). Bioactive glass 58S was prepared by the sol-gel method as described in detail in the literature [5]. The other composite material (COMP2) was fabricated by mixing and stirring the precursor solution of the bioactive glass 58S with the respective precursor solution of a new sol-gel glass-ceramic in the system SiO2, 60 - P2O5 3 - Al2 O3 14 - CaO 6 - Na2O 7 - K2O 10 (wt%). The new glass-ceramic was synthesized by solgel process using DI water and nitric acid, tetraethoxysilane (TEOS), triethylphosphate (TEP), aluminum nitrate nonahydrate (Al(NO3)3·9H2O), potassium nitrate (KNO3), sodium nitrate (NaNO3) and calcium nitrate tetrahydrate (Ca(NO3)2·4H2O) as precursors. In all cases the final solution was converted to a gel by a drying process at temperatures of up to 180 °C, while the stabilization was performed by heat treatment up to 700 °C. The fabricated materials were characterized by Fourier Transform Infrared Spectroscopy (FTIR) (PerkinElmer Multiscope), in the range 5000–400 cm−1, Scanning Electron Microscopy (SEM) (JEOL JSM-840A). Differential Thermal Analysis (DTA) (Stanton Redcroft STA 780) was also performed up to Tmax = 1100 °C with heating rate 20 °C/min. The characteristics of these materials were compared to those of a commercial dental ceramic. Moreover the bioactive behaviour was investigated through immersion in Simulated Body Fluid (SBF) for 3, 7, 10, 15 and 20 days [3]. The immersed samples were in form of pellets fabricated by cold-pressing (m = 100 mg) and heat treated up to 950 °C with heating rate 80 °C/min for COMP1 and up to 980 °C with heating rate 30 °C/min for COMP2. Moreover, the ability of the novel composites to be applied as coatings on substrates of dental porcelain was investigated. In each case a thick slurry was prepared by mixing each powder of the composite materials with a modelling liquid (IPS Classic Margin Build-Up Liquid). The slurry was spread by a spatula on substrates of dental porcelain. The fabricated specimens were exposed to specific heat treatment for each case. The quality of the attachment was investigated by optical microscope and SEM on cross sections of the specimens. Microhardness measurements were performed on the coatings (Microhardness tester Indentec Zwick/Roell ZHV, Zwick GmbH, Ulm, Germany) using a Vickers diamond indenter and loads of 5N (500 g) for 10 s. The bioactivity of the fabricated coatings was also determined.

Results and discussion

The SEM images of the fabricated composites (Figure 1) show the porous morphology of both composites.


Figure 1: SEM images of the porous structure of the fabricated composite materials.

The thermal analysis of the fabricated materials shows evidence of the crystallization process corresponding to the characteristic crystalline phases expected (Figure 2). Exothermic peaks were observed in both DTA curves in the temperature range 800–1000 °C, which is the temperature range where crystallization of wollastonite phase occurs (∼900 °C). The DTA curve of the commercial glassceramic does not present any characteristic feature in the same temperature range.

bioceramics-development-applications-DTA-curves-composite materials

Figure 2: DTA curves of composite materials. The respective curve of the commercial glass-ceramic is presented for comparison.

The transmittance spectra of COMP1, COMP2 and the commercial material are presented in Figure 3, before (black lines) and after (red lines) the application of a heat treatment up to 1000 °C with 20 °C/min. The specific heat treatment was selected for the identification of the phases which are formed regarding the results occurred by the DTA analysis. The spectra of the composites after heat treatment show the raise of some new peaks. These new peaks around ∼645 cm−1, ∼685 cm−1 and in the range 900–1080 cm−1 are assigned to the formation of wollastonite phase, while the replacement of the broad peak at 700–800 cm−1 by the shoulder at 720 cm−1and the sharper peak at 780 cm−1 in the spectra confirm the growth of the leucite crystalline phase [2]. The increase of crystallinity of the apatite phase after the applied heat treatment is also observed. Additionally, heat treatment causes the disappearance of the peak at 1384 cm−1, which confirms the release of the NO3 − groups from the network of the fabricated composites. Moreover, the spectra of the commercial glass-ceramic present all the characteristic peaks of an aluminosilicate network without having any change in the structure after the applied heat treatment.


Figure 3: FTIR spectra of the new glass-ceramic material (black line) and the commercial glass-ceramic (blue line).

SEM images of the surface of the pellets of the composite materials before and after immersion in SBF are shown in Figure 4. The composite samples exhibited the growth of a thick, uniform and crystalline carbonated hydroxyapatite layer (HCAp) on the surface of the pellets even after 3 days of immersion in SBF, while further immersion in SBF for up to 20 days confirmed that the developed layer is retained on the surface of the samples.


Figure 4: SEM images of the formed HAp layer on the surface of both COMP1 and COMP2 pellets after 3 days in SBF.

In order to assess the feasibility of using the developed materials as coatings in dental applications, the bioactive composite materials were applied on substrates of dental ceramics and the coating attachment to the substrate as well as the hardness of the fabricated coatings were investigated.

Images were taken by optical microscope from cross sections of the coated specimens (Figure 5). The very good attachment of the coatings on the substrates was confirmed qualitatively. Microhardness indentations gave an average value of ∼ 30HV for COMP1 and ∼ 60HV for COMP2. The higher value for COMP2 is related to the applied heat treatment. The microhardness of COMP2 is similar to values of sol-gel derived materials.


Figure 5: Coated specimens.

Coated specimens after their immersion in SBF presented bioactive behavior similar to the one which was observed in case of the respective pellets. The growth of HAp layer on their surface occurred after 7 days of immersion in SBF (Figure 6).


Figure 6: SEM images of the formed HAp layer on the surface of both COMP1 and COMP2 coated specimens after 7 days in SBF.


The fabrication of two novel glass-ceramic composite materials with potential use in dental restorations by the sol-gel technique was demonstrated. The new glass-ceramic composites present characteristics slightly different to those of a commercial leucite based dental ceramic. The bioactive behavior of the fabricated materials was assessed. The feasibility of using the developed materials as coating in dental applications was confirmed. The very good attachment of the coatings to the substrate in both cases was observed, while the higher microhardness value of the specimens coated by COMP2 is attributed to the specific applied heat treatment.


One of the authors (X. Chatzistavrou) acknowledges the funding of European Commission via a Marie Curie Fellowship.


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