Low_resolution_Thesis_CDD_221009_public - Visual Optics and ...

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$XXX Congress of the European Society of Cataract and Refractive ...$

CHAPTER 2 2.3.2.2. LRT evolution Two different LRT devices, both built at the Instituto de Óptica, Madrid (Spain), were used to measure ocular aberrations in this thesis. The first device (LRT1) was built by Esther Moreno during her thesis (Moreno-Barriuso and Navarro, 2000, Moreno- Barriuso et al., 2001a, Moreno-Barriuso et al., 2001b, Navarro et al., 1998), with help from the author of this thesis, especially in the data processing and calibrations. Extensive validation of this instrument has been presented including comparison with other aberration measurement techniques, such as Hartmann-Shack and the Spatially Resolved Refractometer (Moreno-Barriuso and Navarro, 2000, Moreno-Barriuso et al., 2001a, Llorente et al., 2003, Marcos et al., 2002). This device was used in the work presented in Chapter 9. The second device (LRT2), which will be described briefly in the next section, was developed at the first stages of this thesis, with a high number of improvements over LRT1, and used in the work presented in Chapters 8 and 10. LRT2 incorporates some additional features specially advantageous for measurements in ametropic eyes (Dorronsoro et al., 2003a, Llorente et al., 2004b). The most important advantages of LRT2 over LRT1 are: 1) the use of infrared light in addition to visible green light; 2) increase of the speed to less than 1.5 seconds for an entire typical run; 3) continuous display of pupil images during the measurement and simultaneous recording of pupillary and retinal aerial images; 3) easy selection of the pupil sampling density and pattern by software; 4) fully automated control software; 5) compact and lighter instrument; 6) the possibility to correct large amounts of spherical defocus continuously by means of a Badal system (see Section 2.3.2.3 of this chapter); 7) the presence of a plane conjugate to the pupil plane, where trial lenses can be placed, without altering pupil and retinal magnification; 8) a channel for dynamic projection of visual stimuli; 9) the recording on pupilary images during the measurement (and synchronized with the retinal images) allows for passive eyetracking correction of head and eye movements. 2.3.2.3. LRT Experimental setup A schematic diagram of the LRT2 set-up is shown in Fig. 2. 20, a photograph from above in Fig. 2. 21, and an overview (with patient) in Fig. 2. 22. The system consists of 4 channels; 1) Illumination channel, with two possible light sources (green 532-nm or infrared 785nm laser diodes), focused on x-y scanner, and then collimated by the lens L3 in order to compose the desired sampling pattern on the pupil plane. 2) Retinal imaging channel, where the light reflected back from the retina is captured by the retinal CCD. 3) Pupil monitoring channel, where the pupil CCD captures the corresponding image of the eye’s pupil, simultaneously with the retinal spots on the retinal CCD; 4) Fixation channel, where a target is displayed on a CRT monitor during the measurement. All channels share a Badal system, for compensation of defocus, formed by lenses L1 and L2 and mirrors M1, M2 and M3. P marks the position of a pupil conjugate planes, and R marks the position of retinal conjugate planes. The light source can be selected between two diode lasers emitting in green (532 nm; Brimrose, Baltimore, USA) and IR wavelengths (785 nm; Schäfter + Kirchhoff, Hamburg, Germany). Prior to the systematic use of infrared wavelength in the measurements, we confirmed the equivalence of infrared and green light in the measurement of ocular aberrations (Llorente et al., 2001). Both lasers are attenuated below safety limits using neutral density filters: the maximum permitted exposure 80
METHODS (1993) power thresholds for 532 nm and 785 nm were 6.9 w and 7.6 m respectively. We used at least three ND4 neutral density filters to attenuate the power down to 4.1w and 6.8 w, and more filters were added when possible/necessary. Exposure times (about 1.5 seconds for a typical run with 37 samples) are controlled by an electronic shutter (Vincent Associates, Rochester NY, USA). Fig. 2. 20. Schematic diagram of the LRT2 setup described in the text. L1 and L2 are 100-mm focal length lenses, and L3 and L4 are 50.8-mm focal length lenses, M1, M2, and M3 are plane mirrors, HM is a hot mirror, CBS1 and CBS2 are cube beam splitters, PBS is a pellicle beam splitter, F1 and F2 are interferometric filters for 785 and 532 nm, respectively, and P and R are planes conjugate to the pupil and the retina, respectively. The XY scanner (mod.6210, Cambridge technologies, Lexington, USA), consists of two rotating mirrors that deflect the incoming unexpanded laser pencil in such a way that in combination with collimating lens L3 (f’=50.8 mm) compose the sequential sampling pattern. Due to the distance between the two mirrors (~5 mm), some astigmatism is induced in the system (Navarro and Moreno-Barriuso, 1999), and therefore a trial lens attached to the collimating lens (+2.50 at 0º) is used to correct this astigmatism (see Section 2.3.2.7). Lens L4 (f’=50.8 mm) forms the image of the laser waist on the scanner in order to obtain the smallest sampling aperture on the pupil plane (~400 m). The flexibility provided by the scanner to configure sampling patterns with different distributions and densities of the samples was essential for the 81
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Doctoral thesis Corneal Ablation an
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Contents Corneal Ablation and Conta
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2.2.1. Fitting surfaces............
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5.3.3. Ablation efficiency factors
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10.5. DISCUSSION...................
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We thank José Antonio Sánchez-Gil
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BOZR Back Optic Zone Radius BCVA Be
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INTRODUCTION 1.1. MOTIVATION The fr
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INTRODUCTION 1.2. THE OPTICAL SYSTE
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INTRODUCTION Myopia is a very commo
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INTRODUCTION a point focus: the dif
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INTRODUCTION system, and tilt repre
Page 29 and 30: INTRODUCTION term Z 0 2 stands for
Page 31 and 32: INTRODUCTION which image was shadow
Page 33 and 34: INTRODUCTION The defocus Zernike te
Page 35 and 36: INTRODUCTION 1.4.6.3. Internal Aber
Page 37 and 38: INTRODUCTION 1.5.2.3. Alternating v
Page 39 and 40: INTRODUCTION and further-more, at l
Page 41 and 42: INTRODUCTION alcohol is used to loo
Page 43 and 44: INTRODUCTION changes in reflectivit
Page 45 and 46: INTRODUCTION Marcos et al. (Marcos
Page 47 and 48: INTRODUCTION 1.7.3. Ablation effici
Page 49 and 50: INTRODUCTION corneal surface may be
Page 51 and 52: INTRODUCTION Algorithm design: The
Page 53 and 54: INTRODUCTION contact lenses the fie
Page 55 and 56: INTRODUCTION 1.10.1. Tear studies A
Page 57 and 58: INTRODUCTION there are still many u
Page 59 and 60: INTRODUCTION 6. Evaluation and unde
Page 61 and 62: METHODS 2Chapter Chapter 2 - Method
Page 63 and 64: METHODS 2.1. MEASUREMENT OF OPTICAL
Page 65 and 66: METHODS In both profilometers, cust
Page 67 and 68: METHODS The measurement method that
Page 69 and 70: METHODS Fig. 2. 9. Set of points in
Page 71 and 72: METHODS Slit lamp Scheimpflug Camer
Page 73 and 74: METHODS representing the deviation
Page 75 and 76: METHODS 2.2.2.2. Ablation pattern f
Page 77 and 78: METHODS direction. These calculatio
Page 79: METHODS eye through the whole pupil
Page 83 and 84: METHODS alignment (frontal-illumina
Page 85 and 86: METHODS Fig. 2. 24. Example frame f
Page 87 and 88: METHODS 4) New image processing too
Page 89 and 90: METHODS Fig. 2. 28. Corrected entra
Page 91 and 92: METHODS Badal lens, corresponds to
Page 93: METHODS Each VA measurement consist
Page 99: REFRACTIVE SURGERY PMMA MODEL 3.1.
Page 102 and 103: CHAPTER 3 optimization of refractiv
Page 104 and 105: CHAPTER 3 These data demonstrate th
Page 106 and 107: CHAPTER 3 regression line, since it
Page 108 and 109: CHAPTER 3 Figure 3.3 shows one of t
Page 110 and 111: CHAPTER 3 Ablation efficiency facto
Page 112 and 113: CHAPTER 3 considering the same set
Page 114 and 115: CHAPTER 3 3.5.3 Impact of correctio
Page 117: ABLATION PROPERTIES OF FILOFOCON A
Page 121 and 122: ABLATION PROPERTIES OF FILOFOCON A
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ABLATION PROPERTIES OF FILOFOCON A
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ABLATION PROPERTIES OF FILOFOCON A
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OPTIMIZED LASER PLATFORMS 5.1 ABSTR
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CHAPTER 5 pulses. Fluence, repetiti
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CHAPTER 5 ablations. The slit-confo
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CHAPTER 5 (Anera et al., 2003): d S
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CHAPTER 5 asymmetries also appeared
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CHAPTER 5 5.3.4. Ablation patterns
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CHAPTER 5 a) b) : 6.5 mm c) Fig. 5.
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CHAPTER 5 achieve proper reflection
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CHAPTER 5 Both the ablation algorit
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HYBRID PORCINE/PLASTIC MODEL 6.1. A
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CHAPTER 6 6.3.1. Hybrid porcine-pla
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CHAPTER 6 is detected. Therefore, i
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CHAPTER 6 no preferential orientati
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ANTERIOR AND POSTERIOR CORNEAL ELEV
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183
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SOFT CONTACT LENS FITTING USING MOD
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SOFT CONTACT LENS FITTING USING MOD
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ON-EYE OPTICAL PERFORMANCE OF RIGID
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SOFT MONOFOCAL AND MULTIFOCAL CONTA
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SOFT MONOFOCAL AND MULTIFOCAL CONTA
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CORRELATION BETWEEN RADIUS AND ASPH
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CONCLUSIONS Conclusions This thesis
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CONCLUSIONS 5We have developed a pr
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CONCLUSIONS LIST OF METHODOLOGICAL
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CONCLUSIONS FUTURE RESEARCH LINES T
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CONCLUSIONS LIST OF PUBLICATIONS AN
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REFERENCES References AIZAWA, D., S
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REFERENCES PHOTODECOMPOSITION (APD)
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REFERENCES DORRONSORO, C., CANO, D.
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REFERENCES GISPETS, J., ARJONA, M.
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REFERENCES KOPF, M., YI, F., ISKAND
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REFERENCES MARCOS, S., DORRONSORO,
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REFERENCES NOVO, A., PAVLOPOULOS, G
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REFERENCES SAKIMOTO, T., ROSENBLATT
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REFERENCES WANG, L., DAI, E., KOCH,
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RESÚMENES pacientes reales fue com
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RESÚMENES experimentales de cirug
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RESÚMENES cada punto de las cornea
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RESÚMENES plástico medidas anteri
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RESÚMENES 8 Evaluación óptica de
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RESÚMENES 9 Prestaciones ópticas
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RESÚMENES 10 Calidad óptica y cal
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RESÚMENES A Correlación entre rad
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CONCLUSIONES clínicos. La descripc
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CONCLUSIONES 12 Las superficies ocu
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CONCLUSIONES IMPLICACIONES DE ESTA
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CONCLUSIONES contribuyen a la compr
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(y muchísimo más difícil). Me da
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