Effect of printing direction on stress distortion of three-dimensional printed dentures using stereolithography technology

Fabrication of complete dentures using a 3D printer is quicker and more economic than conventional methods. However, the photopolymer resins used in 3D printers has a lower flexural strength than heat-cured resin. Furthermore, photopolymer resins exhibit anisotropic properties depending on the print...

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Bibliographic Details
Published in:Journal of the mechanical behavior of biomedical materials 2020-10, Vol.110, p.103949-103949, Article 103949
Main Authors: Hada, Tamaki, Kanazawa, Manabu, Iwaki, Maiko, Arakida, Toshio, Minakuchi, Shunsuke
Format: Article
Language:English
Subjects:
Complete denture
Computer-Aided Design
Dentures
Maxilla
Mechanical stress
Printing, Three-Dimensional
Stereolithography
Three-dimensional printing
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Summary:Fabrication of complete dentures using a 3D printer is quicker and more economic than conventional methods. However, the photopolymer resins used in 3D printers has a lower flexural strength than heat-cured resin. Furthermore, photopolymer resins exhibit anisotropic properties depending on the printing direction, but no studies have evaluated their mechanical properties. The impact of stress distribution caused by changing the printing direction of the 3D printed denture has not been clarified. This study aimed to investigate the effect of different printing directions (0°, 45°, and 90°) of stereolithography (SLA) 3D printed dentures on stress distribution. Artificial mucosa was fabricated to fit a maxillary edentulous model, which was scanned to generate a standard tessellation language (STL) file. Subsequently, the upper denture was designed using computer-aided design (CAD) software, output as an STL file (master data), and set in three different printing directions (0°, 45°, and 90°). It was printed by the SLA 3D printer using photopolymer resin (n=6, in each printing direction). The stress distributions of the dentures were monitored using four rosette strain gauges, which were cemented to the midline of each denture as follows: above the labial frenum (A), at the incisive papilla (B), at the endpoint of the denture (D), and at the mid-point of B and D (C). A load was applied to the posterior region at a loading rate of 20 N/s from 0 N to 200 N using a universal testing machine. Changes in the applied load and strain at each point were recorded. The maximum principal strain (MPS) and the direction of the MPS (θ) were calculated. Each mean MPS was compared using Kruskal–Wallis and Steel–Dwass multiple comparison tests (p 
ISSN:1751-6161
1878-0180
DOI:10.1016/j.jmbbm.2020.103949