Low_resolution_Thesis_CDD_221009_public - Visual Optics and ...
Low_resolution_Thesis_CDD_221009_public - Visual Optics and ...
Low_resolution_Thesis_CDD_221009_public - Visual Optics and ...
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METHODS<br />
direction. These calculations, performed on interpolated ablation maps, will be<br />
described in the corresponding chapters.<br />
2.3. MEASUREMENT OF OPTICAL QUALITY<br />
Estimates of optical quality in this thesis are based on measurements of corneal<br />
aberration, obtained after processing corneal elevation maps (Section 2.1), <strong>and</strong> total<br />
eye aberrations measured with a Laser Ray Tracing device (Section 2.3.2). This<br />
Section will describe the numerical procedures to calculate corneal aberrations<br />
(Section 2.3.1), <strong>and</strong> the experimental <strong>and</strong> numerical procedures to obtain ocular<br />
aberrations (Section 2.3.2). The calculation of the Strehl ratio (a metric of optical<br />
quality used in this thesis) <strong>and</strong> the simulation of retinal images <strong>and</strong> is also described<br />
(2.3.3).<br />
2.3.1. Corneal aberrations<br />
There are three steps in evaluating corneal aberrations of the anterior corneal surface:<br />
1) obtaining experimental corneal elevation; 2) representing the corneal surface from<br />
these data; 3) evaluating corneal aberrations from the corneal model surface. The<br />
corneal aberrations were obtained from videokeratoscopy <strong>and</strong> profilometry<br />
measurements in this thesis.<br />
2.3.1.1. Representing the corneal surface<br />
Corneal surface representation is limited by the distribution of videokeratoscopic data.<br />
As this distribution is not uniformly spatially sampled in XY coordinates, with no data<br />
between rings, <strong>and</strong> especially within the central clear zone (around 0.4 mm radius),<br />
strategies based on local interpolations do not work properly. In general, a smooth<br />
global interpolation by polynomial expansion offers better results. Considering the<br />
circular symmetry of the data, the Zernike polynomial expansion appears to be a good<br />
choice (Schwiegerling et al., 1995). We fitted corneal surfaces with a Zernike<br />
polynomial expansion using 37 terms, <strong>and</strong> a st<strong>and</strong>ard least squares optimization by<br />
means of the inverse matrix built-in function given in Matlab. Once the surface is<br />
modelled by Zernike polynomial expansion, discrete points are evaluated in a XY<br />
equi-space grid to be introduced in an optical design program, Zemax V.9 (Focus<br />
Software, Tucson, AZ) for the corneal ray tracing evaluation.<br />
2.3.1.2. From corneal surface to corneal wave aberration<br />
The technique used in this thesis for the estimation of the corneal wave aberration is<br />
based on the work by Barbero <strong>and</strong> colleagues (Barbero et al., 2002b, Barbero et al.,<br />
2002c). It is based on calculations of the exact difference of the ray path between two<br />
points in the real <strong>and</strong> ideal wavefront for each pupil coordinate. The surface in a XY<br />
equi-space grid is introduced in Zemax, using a finite difference method to evaluate<br />
the normals to the surface –necessary to apply Snell’s law-. The exact virtual ray<br />
tracing through the corneal surface is performed setting the index of refraction to that<br />
of the aqueous humor (1.3315). The wavelength was usually set to that used in the<br />
LRT measurement. Mean corneal Zernike coefficient variability of naked human eyes<br />
in vivo measured with Placido disk videokeratoscopy is 0.015 m (averaged across<br />
terms). The technique has been validated <strong>and</strong> extensively used in previous work in the<br />
<strong>Visual</strong> <strong>Optics</strong> <strong>and</strong> Biophotonics laboratory (Barbero et al., 2002b, Barbero et al.,<br />
2002c, Marcos et al., 2007), as described in Sergio Barbero’s <strong>Thesis</strong> (Barbero, 2004).<br />
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