## 4 Discussion  
This study utilized the finite element stress analysis method to investigate the stress distribution in class II DO cavities filled with dental amalgam and resin cement, with the enamel, dentin, dental amalgam, and resin cement having varying Poisson's ratios and stress values. The results demonstrate that the thickness of the resin cement influenced the concentration of stress at the restoration interface and in the dental tissues. Therefore, the hypothesis was refuted based on the findings of this investigation. In this study, a 3D dental model was generated using CT-based data. This approach allowed for the creation of an accurate 3D finite element model of a tooth, and it is essential in exploring various clinical issues in dentistry [29; 30]. Advancements in milling technology and modeling methodologies have made FEA an effective method in biomechanical  
Figure 7: Maximum principal stress (MPa) distribution within the enamel, dentin, restoration, and different thicknesses of resin cement under 600 N of total force applied to the occlusal surface (V2; Poisson’s ratio: 0.24) with the amalgam. applications. FEA is particularly useful in dentistry when experimental applications do not provide sufficient information [30; 31]. FEA provides dependable information regarding stress areas, especially in structures where the analyzed surface is not smooth. It also allows for a swift analysis of intricate computer-designed components and minimizes costs and time by reducing the number of required test subjects [32]. During simulations, our study utilized surface sliding-type contact elements in a 3D FEA. However, different Young's modulus values were considered for the bolus, and a stable occlusive loading force of 600 N was applied [9]. According to a previous study, the average human bite forces in the molar region are 847 Newtons for men and 597 Newtons for women [33]. In general, loads can be applied directly to a tooth/filling through concentrated or distributed means or indirectly using a ball or bite [8]. The quantity, location, and angle of the load are influenced by various factors, such as chewing patterns and food type. Such complex loading conditions can lead to different and potentially more critical stress scenarios. Moreover, an anisotropic elastic material model was utilized to examine all tissue types [34]. In a previous study, it was noted that the finite element analysis method is a valuable tool for researchers and clinicians to enhance and strategize oral health [35]. It is known that molar teeth account for approximately 50% of all dental fractures [36]. As such fractures are common in molars, this study utilized a molar tooth for modeling purposes. Functional restorations utilizing dental amalgam can have a lifespan of over 60 years if appropriately prepared and maintained, owing to its properties. Therefore, any material aiming to replace it must first be proven mechanically, biologically, practically, and socio-economically superior, which has yet to be achieved [7]. Dental amalgam is one of the most commonly used restorative materials in posterior teeth due to its high fracture resistance and tensile qualities. The chewing forces exerted on dental amalgam are absorbed not only by dental hard tissues but also by periodontal tissues and alveolar bone [8]. Materials with a higher shear modulus and lower compressibility are generally more rigid, but they also tend to be brittle [37]. The elasticity modulus of a material indicates its relative hardness within elastic ranges, and this can be determined through various techniques, such as tensile and compression testing. Restorative materials with a low modulus have been shown to aid in stress release [38]. Restorative materials with a high elasticity modulus can reduce the flexure of tubercles in class II cavities [24].