## 4 Discussion  
This study compared and analyzed plantar pressure parameters between the intact limbs of TF amputees and healthy individuals during gait movement. Asymmetrical values in pressure peaks were detected in this study evaluation when the participants who underwent TF amputations walked. This study's results support the hypothesis that the plantar pressure values of transfemoral amputees with intact limbs and healthy individuals are different. The study found that gait compensations can be seen in TFA individuals using an MPK prosthesis unit, according to plantar pressure data under the foot. In TF amputees, the function of the knee joint in the prosthesis they use is essential. Devices that can mechanically perform the function of the knee joint have been developed successfully over time up to the present day. In many studies, the effect of prosthetic knee joint components on gait has been examined, and positive effects on gait have been determined in parallel with technological developments [28; 29]. In particular, with the use of microprocessor-controlled prosthetic knee (MPK) units, it has been reported that the frequency of falls and tripping decreases, and user satisfaction increases compared with mechanical devices [13; 30]. [PERSON] et al. found that the prosthetic side, i.e., the closer proximity of bionic prosthesis users to the SS group, may indicate that this type of prosthetic knee performs better in targeting the physiological kinematic configuration in basic gait events. In addition, the same behavior cannot be identified on the intact side, particularly for the double-support phases. Three different prosthetic knees required similar compensation actions during the weight transfer phases, and activation profiles were recorded and showed that most of the differences in the weight transfer phases were most relevant in the hamstrings and calf muscle activity [31]. According to the results of our study, in TF patients using MPK knee joints, the result of pressure distribution under the foot in the intact limb during the stance phase in the gait cycle was the result of the fact that the pressure is higher in these regions for the duration of weight transfer, whereby the participants use the forefoot and midfoot more actively than healthy individuals; this leads us to surmise that patients can use the compensation mechanism during walking and possibly adopt a vaulting gait. Gait-compensatory mechanisms may occur depending on biomechanical demands, and adaptation mechanisms that may occur in the amputee's intact leg can also be seen through the difference in plantar pressure distribution under \begin{table}
\begin{tabular}{l l l l l} \hline \hline
**Stance Phase Plantar Pressure Distributions** & \begin{tabular}{l} **TFA Groups** \\ **n = 21** \\ \end{tabular} & \begin{tabular}{l} **Health Groups** \\ **n = 24** \\ \end{tabular} & \
\begin{tabular}{l} **\(p\)** \\ \end{tabular} &
\begin{tabular}{l} **Effect Size** \\ **Cohen’s d** \\ \end{tabular} \\ \hline
1 sensor max plantar pressure (kg/cm\({}^{2}\)) & 2.53 \(\pm\) 0.36 & 1.14 \(\pm\) 0.8 & 0.001 * & 2.24 \\
2 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.45 \(\pm\) 0.45 & 1.40 \(\pm\) 0.52 & 0.742 & 0.1 \\
3 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.91 \(\pm\) 0.34 & 1.22 \(\pm\) 0.73 & 0.001 * & 1.21 \\
4 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.87 \(\pm\) 0.56 & 1.21 \(\pm\) 0.9 & 0.006 * & 0.88 \\
5 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.36 \(\pm\) 0.76 & 1.27 \(\pm\) 0.79 & 0.696 & 0.11 \\
6 sensor max plantar pressure (kg/cm\({}^{2}\)) & 0.96 \(\pm\) 0.3 & 0.48 \(\pm\) 0.26 & 0.001 * & 1.7 \\
7 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.93 \(\pm\) 0.61 & 2.05 \(\pm\) 0.43 & 0.457 & 0.22 \\
8 sensor max plantar pressure (kg/cm\({}^{2}\)) & 1.51 \(\pm\) 0.5 & 2.65 \(\pm\) 0.63 & 0.001 * & 2.0 \\ \hline \hline \end{tabular}  
* \(p\) < 0.05, significant differences between the TFA subjects and the HS.  
\end{table}