# Finite Element Model of Soliosis Brace with Increased Utility Characteristics
## 4 Discussion  
To improve the utility parameters of the orthosis, an openwork model was developed based on the modified corset design described in Section 3.2. It was thickened to a degree \begin{table}
\begin{tabular}{c c c} \hline \hline
**Corset Variant** & **Mass (g)** & **\(\Delta\)X Max (\(\mu\)m)** \\ \hline Original trace & 895 & 7.1 \\ \hline Modified brace & 524 & 7.0 \\ \hline Openwork corset variant \(A\) & 532 & 7.1 \\ \hline Openwork corset variant \(B\) & 497 & 7.8 \\ \hline Openwork corset variant \(C\) & 482 & 7.8 \\ \hline \hline \end{tabular}
\end{table} 
Table 2: Comparison of masses of corset shells and their maximum displacements in the X direction after force \(F_{2}\) has been applied. Figure 10: View of the von Mises stress distributions on the surfaces of the (**a**) original corset, (**b**) modified corset, (**c**) openwork corset variant \(A\), (**d**) openwork corset variant \(B\), and (**e**) openwork corset variant \(C\). that would achieve a stiffness similar to that of the modified brace in the correction plane. The results shown in Figures 7 and 8 indicate that the different corset variants deform in a very similar manner under \(F_{2}\) force loading. The results, shown in Figures 9 and 10, indicate that the values of both the maximum principal stresses and the von Mises stresses do not differ significantly between the corset variants. Table 2 compares the masses of all the corset variants (the density of polypropylene was assumed to be 900 kg/m\({}^{3}\)) and their maximum displacements in the X axis direction under \(F_{2}\) force loading, allowing a direct comparison of the stiffness of the corsets in the X axis direction. The resulting openwork brace \(A\) was found to be 1.4% stiffer than the modified version, while its mass increased by approximately 1.5%. Changing the width of the strips along the main stress trajectories from 20 mm to 15 mm (corset \(B\)) had a similar effect on the stiffness of the brace as changing the width of the crossbars from 20 mm to 10 mm (corset \(C\)) did. Variants \(B\) and \(C\) of the corset were found to be slightly lighter than variant \(A\), but at the cost of their stiffness, which was slightly reduced. Variant \(A\), whose stiffness was found to be identical to that of the original corset, was 39% lighter than the original. The results of the study present the possibility of \"removing\" the auxiliary areas of the corset. This does not mean that their important roles, such as in stabilizing the corset relative to the torso, can be ignored. The auxiliary areas can be made much thinner and/or perforated. Such a change would improve the performance of the corset while keeping its corrective role unchanged. The results suggest that the use of principal stress trajectories in the design of the orthosis plays a key role in tailoring its mechanical properties and weight. In light of these results, it can be shown that fine tuning the structure of the orthosis, especially along the principal stress trajectories, is critical to optimizing its mechanical properties and patient comfort. The detailed numerical analyses presented in Section 3 provide a new perspective on the potential evolution of brace design for the treatment of idiopathic scoliosis. These results underscore that orthotic design can be significantly altered without sacrificing its core corrective functionality. This revelation not only paves the way for more advanced and adaptable brace designs but also underscores the importance of a holistic, patient-centered approach to orthotic design. One of the most important aspects of this research is the focus on the weight of the orthotic brace. Weight plays a multifaceted role in the overall effectiveness and patient acceptance of the brace. On a physical level, a lighter brace inherently provides greater comfort and reduces the wearer's stress during extended periods of use.