## 3 Results  
In this section, the absorbed doses within the mandibular layers calculated for both SRIM database compositions and tissue-mimicking materials over the 50-100 keV energy range are presented in Figures 4-13. These graphs facilitate the comparison of absorbed doses across different energy levels for each layer, clearly highlighting the dose differences between the two material compositions. For the skin tissue, the SRIM database compositions generally show higher absorbed dose values compared to the tissue-mimicking materials, as shown in Figure 4. As the energy levels increase, there is a noticeable rise in absorbed doses for both material types. The variation in X-ray absorption, as seen in Figure 4, is influenced by several key parameters. These include the atomic number (Z) of the material, the photon energy, and the type of interaction between the X-rays and the material, primarily photoelectric absorption, Compton scattering, and pair production at higher energies. At lower energies (50-60 keV), photoelectric absorption dominates, especially in materials with higher atomic numbers, leading to a decrease in absorption as energy increases. However, as the energy approaches 100 keV, Compton scattering becomes the dominant interaction, which causes an increase in X-ray absorption due to the increase in scattering events. The balance between these interactions determines the observed absorption trends across the energy spectrum. However, the difference between the SRIM compositions and the tissue-mimicking materials is more pronounced at lower energy levels, while this gap narrows as the energy increases. This suggests that SRIM database compositions align more closely with tissue-mimicking materials at higher energy levels. Overall, SRIM database compositions depict higher and more varied trends in dose absorption within skin tissue, whereas tissue-mimicking materials display lower and less variable absorbed dose values. The tooth organ received an average dose of 2.8380 mGy/source. As the X-ray energy increased from 50 keV to 100 keV, a decrease in the dose absorbed by the organ was observed, averaging a reduction of 4.1%. For every 5 keV increase in energy, this difference was approximately 1.8%. Considering that higher energy X-rays are likely to exit the organ. This result is consistent with expectations. The phantom made from polymer tissue-equivalent materials received an average dose of 1.8290 mGy/source. Similar to the organ, as the energy of the X-ray increased, the total dose decreased by an average of 32.1% for every 5 keV energy increase. This difference was found to be around 3.8%. A total dose difference of approximately 35.5% was observed between the organ and the phantom. The dose values for the skin and its tissue equivalent, PMMA, are presented in Figure 4. The average dose for the skin was 0.0564 mGy/source, while for the PMMA, it was 0.0504 mGy/source. This difference was 20.6% at 50 keV but decreased to 4.7% at 100 keV. As the X-ray energy increased by 5 keV, the dose in the skin tissue increased by 3.1%, while for the PMMA the increase was 3.6%. The dose values for the parotid gland and its tissue equivalent, PMMA, are presented in Figure 5. The average dose in the parotid gland was 1.2586 mGy/source, while in the PMMA, it was 1.1737 mGy/source. At the 50 keV energy level, the difference was 13.2%, but as the energy increased to 100 keV, the difference decreased to 4.6%. For both the parotid gland and PMMA, the dose increased by an average of 3.3% with each 5 keV increase in X-ray energy. The dose values for the SMAS tissue and its tissue equivalent, PMMA, are presented in Figure 6. The average dose in the SMAS tissue was 0.0926 mGy/source, while in the PMMA, it was 0.0791 mGy/source. At the 50 keV energy level, the difference was 22.5%, but as the energy increased to 100 keV, the difference decreased to 6.6%. For both the SMAS tissue and PMMA, the dose increased by 4.6% with each 5 keV increase in X-ray energy.