## 3 Results
### Hemodynamic Monitoring  
The hemodynamic monitoring (\(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) measurements) following a simulated patient neuronal stimulation (see Section 2.7) is represented In Figures 10 and 11. In Figure 10, the \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) values were computed with the optimal spectral combination of the hyperspectral camera; see Figure 7. In Figure 11, the \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) values were computed with the RGB camera. In these figures, the modified Beer-Lambert law was computed 10\({}^{3}\) times, using different Monte Carlo and intensity noise occurrences for each time iteration. When using the 121 wavelengths included between 780 nm and 900 nm [23] to quantify the concentration changes during the stimulation period (from \(t=18\) s to \(t=38\) s), there is a 12% overestimation of the \(\Delta C_{HbO_{2}}\) values and a 34% underestimation of the \(\Delta C_{Hb}\) values compared to the theoretical measurements. When using the eight wavelengths identified by [PERSON] et al. [27] to quantify the concentration changes during the stimulation period, there is a 13% overestimation of the \(\Delta C_{HbO_{2}}\) values and a 31% underestimation of the \(\Delta C_{Hb}\) values compared to the theoretical measurements. In Figure 10, the hemodynamic monitoring following a simulated neuronal stimulation was computed using hyperspectral imaging. The optimal corrected and uncorrected spectral configurations of the hyperspectral camera were used to quantify the \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) values. The quantification dispersion ranges of the corrected and uncorrected spectral configurations have approximately the same range of magnitude. The standard deviation averaged over all time measurements for \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) are equal to 0.9 \(\upmu\)mol\(\cdot\)L\({}^{-1}\) and 0.7 \(\upmu\)mol\(\cdot\)L\({}^{-1}\), respectively. When the spectral bands are corrected, the \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\) values averaged over the \(10^{3}\) noisy measurements have a good match with the theoretical hemodynamic responses. During the stimulation period, there is on average a 14% overestimation of the \(\Delta C_{HbO_{2}}\) values and a 18% underestimation of the \(\Delta C_{Hb}\) values compared to the theoretical measurements. When the spectral bands are not corrected, there is on average a 17% underestimation of the \(\Delta C_{HbO_{2}}\) values and a 58% underestimation of the \(\Delta C_{Hb}\) values compared to the theoretical measurements. The correlation coefficients computed between the theoretical HbO\({}_{2}\) response and the \(\Delta C_{HbO_{2}}\) time courses are higher when the spectral bands are corrected (\(r=0.951\pm 0.013\)) than when they are not (\(r=0.904\pm 0.026\)). In the same way, the correlation coefficients computed between the theoretical Hb response and the \(\Delta C_{Hb}\) time courses are higher when the spectral bands are corrected (\(r=0.932\pm 0.018\)) than when they are not (\(r=0.783\pm 0.059\)). The correlation coefficient values are summarized in Table 4.  
In Figure 11, the hemodynamic monitoring following a simulated neuronal stimulation was computed using RGB imaging. The standard deviation averaged over all time measurements is equal to 0.35 \(\upmu\)mol\(\cdot\)L\({}^{-1}\) and 0.20 \(\upmu\)mol\(\cdot\)L\({}^{-1}\) for \(\Delta C_{HbO_{2}}\) and \(\Delta C_{Hb}\), respectively. The \(\Delta C_{HbO_{2}}\) values values averaged over the \(10^{3}\) noisy measurements do not have a good match with the theoretical HbO\({}_{2}\) response; however, the match is rather good between the \(\Delta C_{Hb}\) values and the theoretical Hb response. During the stimulation period, there is on average a 48% underestimation of the \(\Delta C_{HbO_{2}}\) values and a 4% underestimation of the \(\Delta C_{Hb}\) values compared to the theoretical measurements.