All patients underwent comprehensive ocular examinations including measurement of the BCVA using a Landolt ring chart, intraocular pressure, indirect ophthalmoscopy, slit-lamp biomicroscopy with a preset lens, and OCTA at every visit. The OCTA images were obtained using the Zeiss Cirrus 5000 with Angioplex software (Carl Zeiss Meditec, Dublin, CA, USA),
21–23 which acquires two sequential OCT scans in the same location and generates en-face OCTA images by using the optical microangiography algorithm. The 6 × 6-mm scans centered on the fovea were obtained repeatedly until nine OCTA cubes with sufficient image quality were obtained. The scan quality was assessed on the scan quality check screen according to acceptance criteria (i.e., clear and sharp focus, few to no artifacts [e.g., motion lines], minimal saccades [identified by horizontal misalignment of vessel segments on en-face images], and a signal strength of 7 or more). Moreover, images had to be centered on the fovea and illuminated uniformly without dark corners. If acceptable scans meeting these criteria (for all nine acquisitions) were not acquired, the eye was excluded from the analysis. En-face images of the superficial retinal capillary plexus (SCP) layer, deep retinal capillary plexus (DCP) layer, and CC were obtained using the commercial default automated segmentation boundaries and exported at a size of 1024 × 1024 pixels for further analyses. The boundaries of the SCP layer extended from 3 μm below the internal limiting membrane to 15 μm below the inner plexiform layer, the DCP layer boundaries were from 15 to 70 μm below the inner plexiform layer, and the CC boundaries were 20 μm below the RPE layer. The measurements of the FAZ area were calculated using the nonflow function in the OCTA software. A proprietary and preliminary software, AngioExerciser V1.2.2 and OCTAVE, from Zeiss was used to extract the vessel density values from the OCTA scans. The software automatically segmented the OCTA cube data into the relevant SCP, DCP, and CC angio-slab images. The software subsequently binarized and skeletonized the images to arrive at the reported vessel “length” density in mm/mm
2. The authors were masked to the exact algorithm and parameters used for the processing. Although projection artifacts cause superficial vessels to appear in en-face images of structures that are below the vessel, the software automatically removes projection artifacts by subtracting them from images below the vessels.
Two independent graders (T.H. and M.A.) reviewed the images, and poor-quality images were excluded based on evidence of (1) poor fixation, including double vessel patterns, motion artifacts, and the presence of blink artifacts more than 5 pixels wide; (2) medium opacity and/or exudative changes, marked by shadowing or obscuration of the vessel signal in the field of view or a signal strength index less than 50 with reference to the corresponding structural OCT scan; and (3) segmentation errors in the outline of the vascular networks. Thus, the baseline and last examinations of this study were the examinations at which the first and the last OCTA images were adopted for analyses during this study.