## 4 Discussion
Greater joint loading on the contralateral side to the clenching side is indicated in several studies [6; 14; 24]. In the studies conducted by [29] during unilateral posterior clenching on block, the contralateral condyle was displaced cranially and ventrally. Investigation on monkeys also reported [30] that bone strain underneaththe temporomandibular ligament on the balancing side is larger. In the studies conducted by [24] during forceful static biting, the condyle-fossa distance decreases more on the contralateral (balancing) side than on the working side, and this decrease in distance is related to the degree of clenching force. Although the authors note that the method does not allow for direct interpretation of the result as increased compression of the disc, in the absence of newer, more accurate techniques for understanding this phenomenon in the human mandible, it is prudent to maintain this cautious assumption in implant design. In our team, we encountered a case of regained high clenching efficiency following the complete loss of one condyle [5], when a fracture was not diagnosed on the X-ray image due to a medical error, after which displacement and resorption of the fractured condyle occurred below the attachment of the lateral pterygoid. This intriguing case demonstrated that, without support in one of the joints, the muscular system can achieve balance on two supports and still generate a reaction force on the occlusal support comparable to that of a healthy mandible. In the work by [PERSON] [3], an assessment of asymmetric joint support conditions was conducted under the assumption of a simplified vertical occlusal force application. In our study, no simplification to a vertical force was applied; instead, an oblique force was used, which, along with asymmetric joint support, critically influences load transfer and implant load-bearing capacity. The method of load application and support differed significantly from previous studies, making direct result comparisons difficult. Vertical bite force is a specific case of loading, whereas the supports in the mandible on the articular joint surfaces and tooth cusps are naturally oriented at significant anatomical angles. Additionally, the distribution of forces may be influenced by the shape and properties of the food. Therefore, there is a general consensus in the literature that oblique forces should be assumed in the range of 20-45\({}^{\circ}\). Muscles generate horizontal components on the cusps while simultaneously inducing bending of the mandible in the horizontal plane and torsion in the joints. In [PERSON] [3], lateral pterygoid muscle detachment is observed on the side of the TM prosthesis. We aimed to analyze a case where all muscles generate forces and thus arbitrarily assumed that the attachments were preserved. The stress values obtained for the mandibular bone model in Variant IV were consistent with those reported in the study by [PERSON] et al. [15], where both FEM analysis and experimental validation were carried out. In their study, FEM simulations were performed under an occlusal load of 600 N, applied directly as an active force, with 200 N distributed on the molars and 100 N on the premolars. A shift from a vertical to an oblique occlusal force direction resulted in an increase in stress from 778 MPa to 925 MPa. Following topological optimization of the implant design, stress was reduced from 925 MPa to between 720 and 764 MPa. In contrast, our study did not include topological optimization, and the stress values did not exceed the tensile strength of pure titanium, except in areas with artifacts caused by material and geometric notches. In the study by [PERSON] et al. [15], the bone screws used had a diameter of 2.4 mm, and a 1.6 mm thick fixation plate was applied. The implant in their study, similar to our numerical model, demonstrated adequate load-bearing capacity, with the fixation plates being the critical stress area.