Several studies (Sherrill and O'Brien, 1974; Southan and Jørgensen, 1974; Jones, 1983) have shown that stress corrosion fatigue occurs in dental porcelains. Morena et al. (1986) reported on an assessment of slow crack growth parameters for dental ceramics. The purpose of the study reported here was to evaluate the fatigue parameters of a model experimental porcelain using dynamic fatigue testing. This test procedure makes use of several constant stressing rates to perform strength tests. Dynamic stress testing was first described by Evans (1974) and later defined as a distinct test modality by Ritter (1978). From such data, the fatigue parameters can be calculated. These fatigue parameters, n and σ ƒ0 , are, respectively, the crack growth exponent from the crack velocity expression and a materials constant which is dependent on the test environment and the inert (moisture-free) strength. The model porcelain was made from 60% component 1 and 40% component 3 according to the Weinstein patent (Weinstein, et al., 1962). The biaxial flexure strength of 300 specimens 1 mm thick was tested in 37°C water by testing 50 samples at each of 6 constant stressing rates: 100, 10, 1 0.1, 0.01, and 0.001 MPa/s. One hundred specimens were tested in a moisture-free environment at 100 MPa/s using a servo-mechanical testing machine. A commercial porcelain (Jelenko Gingival-Lot# 2012, Jelenko Dental Health Products, Armonk, NY, USA) was chosen as a reference material. One hundred twenty specimens were tested using the same procedures as those used for the model porcelain; however, only 20 samples were tested for 5 stressing rate groups and an inert group. Fatigue parameters with their respective standard errors for the model porcelain were n = 28 ± 1.00, and σ ƒ0 = 58.7 ± 0.31 MPa . Values for the commercial porcelain were n=27.6 ± 2.00 and σ ƒ0 = 49.1 ± 0.51 MPa . These parametric values were obtained from the constants of a linear regression of LOG failure stress vs LOG time to failure obtained from constant stressing rate data for all of the stressing rate groups tested in water for each porcelain. Readers are cautioned that direct extrapolation of the results of this research to clinical applications could be misleading. The additional effects of porcelain to metal bonding on fatigue are poorly understood at this time. A report on preliminary results of porcelain-fused-to-metal disk strength has been presented (Fairhurst et al., 1992), and fatigue parameter evaluations at this laboratory are in progress.
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