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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CHAPTER 2<br />
2.3.2.2. LRT evolution<br />
Two different LRT devices, both built at the Instituto de Óptica, Madrid (Spain), were<br />
used to measure ocular aberrations in this thesis. The first device (LRT1) was built by<br />
Esther Moreno during her thesis (Moreno-Barriuso <strong>and</strong> Navarro, 2000, Moreno-<br />
Barriuso et al., 2001a, Moreno-Barriuso et al., 2001b, Navarro et al., 1998), with help<br />
from the author of this thesis, especially in the data processing <strong>and</strong> calibrations.<br />
Extensive validation of this instrument has been presented including comparison with<br />
other aberration measurement techniques, such as Hartmann-Shack <strong>and</strong> the Spatially<br />
Resolved Refractometer (Moreno-Barriuso <strong>and</strong> Navarro, 2000, Moreno-Barriuso et<br />
al., 2001a, Llorente et al., 2003, Marcos et al., 2002). This device was used in the<br />
work presented in Chapter 9. The second device (LRT2), which will be described<br />
briefly in the next section, was developed at the first stages of this thesis, with a high<br />
number of improvements over LRT1, <strong>and</strong> used in the work presented in Chapters 8<br />
<strong>and</strong> 10. LRT2 incorporates some additional features specially advantageous for<br />
measurements in ametropic eyes (Dorronsoro et al., 2003a, Llorente et al., 2004b).<br />
The most important advantages of LRT2 over LRT1 are: 1) the use of infrared light in<br />
addition to visible green light; 2) increase of the speed to less than 1.5 seconds for an<br />
entire typical run; 3) continuous display of pupil images during the measurement <strong>and</strong><br />
simultaneous recording of pupillary <strong>and</strong> retinal aerial images; 3) easy selection of the<br />
pupil sampling density <strong>and</strong> pattern by software; 4) fully automated control software;<br />
5) compact <strong>and</strong> lighter instrument; 6) the possibility to correct large amounts of<br />
spherical defocus continuously by means of a Badal system (see Section 2.3.2.3 of this<br />
chapter); 7) the presence of a plane conjugate to the pupil plane, where trial lenses can<br />
be placed, without altering pupil <strong>and</strong> retinal magnification; 8) a channel for dynamic<br />
projection of visual stimuli; 9) the recording on pupilary images during the<br />
measurement (<strong>and</strong> synchronized with the retinal images) allows for passive eyetracking<br />
correction of head <strong>and</strong> eye movements.<br />
2.3.2.3. LRT Experimental setup<br />
A schematic diagram of the LRT2 set-up is shown in Fig. 2. 20, a photograph from<br />
above in Fig. 2. 21, <strong>and</strong> an overview (with patient) in Fig. 2. 22. The system consists<br />
of 4 channels; 1) Illumination channel, with two possible light sources (green 532-nm<br />
or infrared 785nm laser diodes), focused on x-y scanner, <strong>and</strong> then collimated by the<br />
lens L3 in order to compose the desired sampling pattern on the pupil plane. 2) Retinal<br />
imaging channel, where the light reflected back from the retina is captured by the<br />
retinal CCD. 3) Pupil monitoring channel, where the pupil CCD captures the<br />
corresponding image of the eye’s pupil, simultaneously with the retinal spots on the<br />
retinal CCD; 4) Fixation channel, where a target is displayed on a CRT monitor<br />
during the measurement. All channels share a Badal system, for compensation of<br />
defocus, formed by lenses L1 <strong>and</strong> L2 <strong>and</strong> mirrors M1, M2 <strong>and</strong> M3. P marks the<br />
position of a pupil conjugate planes, <strong>and</strong> R marks the position of retinal conjugate<br />
planes.<br />
The light source can be selected between two diode lasers emitting in green (532<br />
nm; Brimrose, Baltimore, USA) <strong>and</strong> IR wavelengths (785 nm; Schäfter + Kirchhoff,<br />
Hamburg, Germany). Prior to the systematic use of infrared wavelength in the<br />
measurements, we confirmed the equivalence of infrared <strong>and</strong> green light in the<br />
measurement of ocular aberrations (Llorente et al., 2001). Both lasers are attenuated<br />
below safety limits using neutral density filters: the maximum permitted exposure<br />
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