In a first step, intensity images are generated by standard SD-OCT preprocessing procedures (mean spectrum subtraction, rescaling from wavelength to wavenumber space, zero padding, dispersion correction, and inverse Fourier transform). In a second step, the phase difference of adjacent A-scans is calculated. In order to eliminate background phase noise, we compute this phase difference only for pixels above a certain intensity threshold level (typically four times the intensity noise level). This leaves us with three independent phase difference tomograms of the same position in the sample. Due to the mono-block construction of the miniature collimator mount and the bulk optics interferometer setup, our system is very phase stable. No phase drift correction is needed along one B-scan. However, it is necessary to correct for the phase shift introduced by the galvo scanner. To do so, we apply a histogram-based method^{13} for each channel. Under the assumption that more static than dynamic tissue is imaged, we compute a phase histogram of an entire B-scan. This histogram reveals the phase shift introduced by the scanner and bulk motion (e.g., head movement during the measurement). Subtracting the most populated histogram value from all the other pixel values in the B-scan results in a phase shift corrected image.