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Glaucoma Diagnosis and Monitoring Using Advanced Imaging Technologies

Published Online: April 19th 2013 US Ophthalmic Review, 2013;6(1):15-25 DOI: http://doi.org/10.17925/USOR.2013.06.01.15
Authors: Mitra Sehi, Shawn M Iverson
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Abstract:
Overview

Advanced ocular imaging technologies facilitate objective and reproducible quantification of change in glaucoma but at the same time, impose new challenges on scientists and clinicians for separating true structural change from imaging noise. This review examines time-domain and spectral domain optical coherence tomography, confocal scanning laser ophthalmoscopy and scanning laser polarimetry technologies and discusses the diagnostic accuracy and the ability of each technique for evaluation of glaucomatous progression. A broad review of the current literature reveals that objective assessment of retinal nerve fiber layer, ganglion cell complex and optic nerve head topography may improve glaucoma monitoring when used as a complementary tool in conjunction with the clinical judgment of an expert.

Keywords

Confocal scanning laser ophthalmoscopy (CSLO), time-domain optical coherence tomography, Fourier-domain optical coherence tomography, scanning laser polarimetry (SLP), retinal nerve fiber layer, optic nerve head, glaucoma progression

Article:

Role of Imaging in Glaucoma
Glaucoma results from accelerated loss of retinal ganglion cells (RGCs) and their axons, leading to retinal nerve fiber layer (RNFL) attenuation and optic neuropathy.1,2 Glaucomatous damage is characterized by specific pattern of damage to the optic nerve head (ONH) and visual field loss.3,4 Established methods for detecting these changes include clinical examination of the ONH and RNFL, optic disc stereophotography, and fundus photography.5,6


Role of Imaging in Glaucoma
Glaucoma results from accelerated loss of retinal ganglion cells (RGCs) and their axons, leading to retinal nerve fiber layer (RNFL) attenuation and optic neuropathy.1,2 Glaucomatous damage is characterized by specific pattern of damage to the optic nerve head (ONH) and visual field loss.3,4 Established methods for detecting these changes include clinical examination of the ONH and RNFL, optic disc stereophotography, and fundus photography.5,6

Glaucoma progresses slowly and it is important to detect real change due to disease that is beyond normal age loss and short-term and long-term fluctuations. Advanced ophthalmic imaging devices provide objective quantitative measures of neuroretinal rim, RNFL thickness and ONH topography with high repeatability and low variability.7,8 One of the challenging aspects of ocular imaging is improving signal-to-noise ratio,9–13 and detecting real structural change due to disease that is beyond the normal variability.14–25 Different imaging technologies use different algorithms for this purpose. Several reports have indicated that these technologies are capable of identifying glaucomatous damage at an early stage.26–36 A recent comprehensive review by the Ophthalmic Technology Assessment Committee Glaucoma Panel of the American Academy of Ophthalmology concluded that information obtained from imaging devices is useful in clinical practice when analyzed in conjunction with other relevant clinical parameters.37

Several imaging technologies have included progression analysis packages that compile several visit dates into trend based analysis designed to assist the clinician in monitoring glaucoma progression.38–43 In order for progression analysis to be useful in clinical practice, three criteria must be met: the measurements must be reproducible and have minimal noise, follow-up images must be accurately registered to each other, and a statistical test must distinguish between true biological change and instrument measurement variability. Preliminary studies for optical coherence tomography (OCT), confocal scanning laser ophthalmoscopy (CSLO) and scanning laser polarimetry (SLP) have shown these methods are capable of detecting change in glaucomatous eyes or eyes of glaucoma suspects over time.39–41,44–46

Confocal Scanning Laser Ophthalmoscopy (CSLO)
Heidelberg Retina Tomograph (HRT; Heidelberg Engineering, Germany) is a CSLO that uses a single diode laser with a wavelength of 670 nm. An automatic pre-scan with a depth of 4–6 mm determines the correct location of the focal plane, the required scan depth and the level of sensitivity needed to capture high quality images.47 Using the Scanning Tomography technique, three sets of three-dimensional images are acquired. The field of view is 15° x 15° and each acquisition comprises 384 x 384 pixels. Sixteen images per millimeter of scan depth are acquired. If the quality of images in at least one of the series is not good enough (for reasons such as fixation loss), the acquisition is automatically continued until three useful series are obtained.

For each location, several reflected light intensities are measured at different focal planes in different depth locations. The distribution of these light intensities along the optical axis ‘z’ (confocal z-profile) has a symmetrical shape with the highest intensity at the location of the lightreflecting surface. When this calculation is performed at all locations in the section image planes, the result is a matrix of 384 x 384 independent height measurements for every measured location, each with a reproducibility of about 10 to 20 microns. The matrix of height measurements can be visualized as a color-coded image.

The total acquisition time is 1.6 seconds. The acquired images are saved and the three topography images, as well as the mean topography image, are computed automatically. The only manual step in the analysis process is the definition of the optic disc margin at baseline. After defining the disc contour, the automatic analysis continues with the computation of stereometric parameters, the classification of the eye, a comparison to previous exams (if exiting), and the presentation of the results.

For the computation of stereometric parameters a defined disc contour, reference ring, reference plane, and an origin for the coordinate system are required.48 The reference ring is a hypothetical ring at the level of the ‘focal plane’ of the image. The reference plane is a hypothetical plane parallel to the peripapillary retinal surface that is located 50 microns posterior to the mean height of the disc margin contour line in temporal sector between 350º and 356º. Reference height determines the location of the reference plane relative to the mean height of the peripapillary retinal surface at the location of the reference ring. In a ‘relative and tilted’ coordinate system the z-axis is parallel to the optical axis of the laser beam and the origin of the z axis is determined by the mean height of the peripapillary retinal surface and the (x, y) plane is parallel to the mean height of the peripapillary retinal surface. In an ‘absolute and untilted’ coordinate system the z axis runs parallel to the optical axis of the laser beam. The origin of the z axis is at the focal plane of the eye and the (x, y) plane runs parallel to the focal plane of the eye. The ‘relative and tilted’ coordinate system is used by default in the HRT system.48

Monitoring Glaucoma Progression
The follow-up imaging of the ONH allows for the analysis of glaucomatous progression. The contour line that is defined at the baseline is automatically transferred to the follow-up examinations after the correction of differences in displacement, rotation, tilt and magnification so the only remaining differences at the ONH are due to topographical changes in this region. The Topographic Change Analysis (TCA) quantifies the change in the topography of the ONH using the first image as the baseline and the subsequent images as follow-up examinations.43 The TCA does not require a defined contour line to determine areas of significant change.

The height of the optic disc and retinal surface at each follow-up measurement is compared to the baseline measurement.43 Any local change between the surface heights of the two measurements in microns is colorcoded on the surface height difference image (Change image) of the follow up examination. Significantly depressed regions appear in red color, significantly elevated regions appear in green color and the rest of the image that is within the 95 % probability of being normal is black (see figure 1).

The images are further analyzed using an array of 4×4 pixels, called superpixels. At each measurement three consecutive images are acquired and hence total of 48 topographical values (3 x 4 x 4) are determined for each superpixel. Superpixels allow for pooling over a larger area and yield more repeated measures for analysis. In steep areas like the edge of the cup, the variability is greater than that in flat areas. The topographic measurement of a superpixel (4 x 4 pixels) and an analysis of variance model for each superpixel is calculated.24

The ‘Change Probability map’ is created based on an F-test analysis (see Figure 1). If the change probability at a superpixel is <0.05 then it will be signified with dark pixels meaning that there is a significant change in the surface height. White matrix dots indicate no significant change. If the significant change compared to baseline repeats at two or three consecutive measurements, then it will be marked on the ‘reflectance images’. On the reflectance images, the green color indicates significant elevation and the red color indicates significant depression of the surface height on consecutive measurements.24

The displayed ‘change’ value is in fact the change in the local surface height at each specified location in micrometers. The pooled standard deviation is the local variability of the specified superpixel among the images taken at each time. The “change probability” demonstrates the error probability to reject the hypothesis of equal variances in the F-test.

Scanning Laser Polarimetry (SLP) Scanning laser polarimetry (SLP) is a CSLO with an integrated polarimeter that measures the amount of retardation (phase shift) of polarized light as it passes through birefringent tissue (e.g. RNFL).49,50 The instrument uses a near infrared (λ= 785 nm) diode laser to scan the ocular fundus in a 40° (horizontal) × 20° (vertical) field, with a density of 256 × 128 pixels.51,52 Linearly polarized light traversing the RNFL is elliptically polarized and the amount of retardation at each corresponding retinal location is proportional to RNFL thickness. A fixed concentric measurement band centered on the optic disc, with 3.2 mm outer and 2.4 mm inner diameters, is used to generate peripapillary retardation measurements.14,50,53,54 The commercial polarimeter has an integrated variable corneal compensator (GDxVCC) which determines and neutralizes eye specific corneal polarization axis and magnitude using the radial birefringence of the macula (Henle’s fiber layer) as an intraocular polarimeter.49,55-61 Atypical retardance patterns (ARP) arise from poor signal-to-noise ratio as a result of light scattering in the eye and have been observed in a subset of normal and glaucomatous eyes, particularly in the nasal and temporal peripapillary region, elderly patients, eyes with lightly pigmented fundi and myopia. The artifact introduced by ARP produces spurious RNFL thickness measurements and reduces the power to discriminate between healthy and glaucomatous eyes.14,50,52,62-68 The typical scan score (TSS) is a support vector machine value that has been reported to be highly predictive of ARP, with TSS values <80 demonstrating good specificity and sensitivity for detection of ARP.50,64,69

An enhanced corneal compensation (GD x ECC) algorithm was developed to compensate for ARP.40,50,70-75 GD x ECC introduces a predetermined birefringence bias, calculated using the birefringence pattern of the macular region, to shift the measurement of the total retardation to a higher value region to remove noise and reduce atypical patterns.14,65

Monitoring Glaucoma Progression
GD x Guided Progression Analysis (GDx-GPA) analyzes longitudinal GDx images to identify RNFL loss over time. The software performs spatial registration of all images, assesses the image quality, and removes the blood vessels and the ONH using a masking technique. Sequential GDx images are then compared to an average of two baseline images. The outcome measures, consisting of retardance pixels, temporal, superior, nasal, inferior, temporal (TSNIT) sectors, and summary parameters (average, superior, and inferior RNFL thickness), are evaluated for statistically significant change. Outcome measures are color-coded based upon a significant change compared to baseline, as yellow (unconfirmed thickness reduction), red (thickness reduction on two consecutive scans), or purple (unconfirmed thickness increase). Three methods are used in GD x -GPA for identification of progression: Method A) ≥150 contiguous pixels on the progression map (see Figure 2a); Method B) ≥4 adjacent segments on the TSNIT graph (see Figure 2b); Method C) significant change in slope of the summary parameters (see Figure 2c).52 Depending on whether one or three scans are obtained at each visit GDx-GPA has two analysis modes; the ‘Fast Mode’ compares the two last images with the two baseline images. Change is identified based on the comparison between the measurements and the predetermined threshold levels of variability.46 The ‘Extended Mode’ uses a mean of three images at each visit, measures the variability of the mean image, and identifies significant change that is greater than the variability measured for that individual eye.46 Both Fast and Extended modes can be used for the analysis of progressing in GDx-ECC and GDx-VCC images. Fast Mode tends to identify greater number of progressing eyes in GDxECC compared to GDx-VCC.76 The results of Fast Mode are more variable than Extended Mode, depending on which two scans are included in the baseline and follow-up images.77 When judging structural change using GDx-GPA, it is important to understand the GPA printout and use in conjunction with clinical judgment for final decision.

It has been shown that longitudinal images obtained with GDxECC have significantly less variability in TSS values and retardance patterns, and reduced bias produced by ARP on RNFL progression assessment compared with GDx-VCC.14,74 It has also been demonstrated that GDx-ECC significantly reduces the frequency and severity of ARP compared with GDx-VCC and improves the correlation between RNFL measures and visual function64 and that GDx-ECC performed significantly better than the GDx-VCC for longitudinal evaluation of the RNFL loss.78

Time-Domain Optical Coherence Tomography
Time-domain OCT (TDOCT, Stratus OCT, Carl Zeiss Meditec, Dublin, CA, USA) is a high-resolution, micron scale, cross-sectional imaging modality that is based on the principles of Michelson interferometry.79 The TDOCT provides quantitative assessments of the retina and optic nerve obtained by measuring the echo time delay between the reference arm and the sample arm using a near-infrared (840 nm) light beam that is split by a mirror to create sample and reference beams. The intensity of backscattered light from posterior segment structures is measured.80 The reflected beams recombine and are transmitted to a photosensitive detector. The interference patterns produced from the recombined beams are analyzed, processed into a false color image, and retinal layers are identified based on signal intensity, allowing distance and thickness measurements.79,81 The Stratus OCT is composed of 512 A-scans that is adjustable to standard density of 256 or 128 scans.82 The Fast RNFL Thickness (3.4) protocol acquires three 3.4 mm diameter circular scans, each of which using 256 A-scans in 1.92 seconds of scanning and combines them into one scan.83,84 The placement of the measurement circle around the ONH is determined by the operator. In order to have accurate RNFL measurements the ONH should be placed at the center of the circle with equal distance in all quadrants.

The RNFL thickness is measured as the distance between the vitreoretinal interface and the inner edge of the ganglion cell layer (GCL). The fast optic disc and fast macula protocols use six radial scans and interpolate between scans to provide measurements throughout the disc and macula, respectively.85,86 The RNFL Thickness Report provides the measurements in 12 clock hours, and four quadrants of temporal, superior, nasal and inferior as well as the average of all quadrants. Average and inferior RNFL thickness measurements have the best diagnostic ability for glaucoma detection.24,69,87 Cup/disc area ratio and rim area parameters have the highest diagnostic ability when the ONH measurements are used.86,88 Stratus OCT generates a signal strength index (SS) as a measure of the quality of image with values ≥ 5 typically being acceptable, and 10 being ideal.19,89 A positive linear relationship between SS and RNFL thickness has been found.19,89-91 Stratus OCT measurements have been reported to be highly reproducible at all stages of the glaucoma continuum, well correlated with histologic measurements of RNFL thickness,83,92-95 with high sensitivity and specificity for the diagnosis of glaucoma.87,88,96-99

Monitoring Glaucoma Progression
Early diagnosis and treatment of glaucoma helps to reduce the rate of glaucoma progression significantly. Different studies have shown that glaucoma progresses faster when the disease is at a more severe stage and that the rate of RNFL loss over time is significantly higher in eyes with progressive visual field loss and progressive optic neuropathy.27,100-105 Clinicians use the results of ophthalmic examination, ocular imaging and visual field series to establish the diagnosis of glaucoma or the possibility of disease progression.106 The earlier the stage of disease, the less definite is the diagnosis and therefore, the patient is considered a ‘glaucoma suspect’ until the body of evidence is strong enough to confirm glaucoma. Advanced ocular imaging technologies have provided objective methods for the measurement of RNFL and ONH structure and have helped to monitor structural progression due to glaucoma. In order to diagnose true glaucoma progression, the instrument’s measurements need to be accurate and repeatable, should be compared with a normative database, and should be analyzed using a statistical technique that defines change beyond the normal variability.

The Stratus OCT Guided Progression Analysis (GPA) uses a simple linear regression to calculate the mean and standard deviation for the annual rate of change in average RNFL and the associated p-value. The results are presented in the GPA Report that includes a graph of the RNFL profile at different visits and a plot of average RNFL thickness against patient’s age, (see Figure 3). The average, superior and inferior RNFL thickness and the signal strength values are presented for each visit. The linear regression analysis of Stratus OCT does not consider the impact of ageing on RNFL loss. Studies have shown that Stratus GPA can supplement glaucoma progression evaluation.27,39

Fourier-domain Optical Coherence Tomography
Cirrus High Definition Optical Coherence Tomography
Cirrus High Definition (HD) (Carl Zeiss Meditec, Dublin, CA, USA) is a fourier-domain OCT that uses a superluminescent diode laser with a center wavelength of 840 nm capable of 27,000 A-scans per second with a 5 µm axial and 25 µm transverse resolution. Similar to other FDOCT devices, Cirrus HD-OCT measures the echo time delay of light, and uses the fast Fourier transformation (FFT) to convert the measured frequencies to Fourier domain (FD) and improve signal-to-noise ratio.107,108 Cirrus HD-OCT acquires images of the optic disc region by measuring a 6 x 6 x 2 mm cube of data (200 x 200 axial scans) centered on the optic disc.109 The RNFL thickness and ONH measures are driven from this cube of data. The RNFL thickness protocol generates data along a 3.46 mm diameter circle automatically centered on the optic disc from 256 A-scan samples.108,109 Since the information from the whole region around the optic disc is available, it is possible to modify the position of the measurement circle after image acquisition.110 The RNFL thickness is identified as the distance between the inner limiting membrane (ILM) and the retinal pigment epithelium (RPE) and Bruch’s membrane junction and displays the measured values by average, quadrants and clock hours.85,109 The RNFL thickness deviation map compares the measured values with the normative database. The 360º RNFL thickness profile, presented as the temporal-superior-nasal-inferior-temporal (TSNIT) graph, compares the data with the normative database and provides the significance of the amount of loss. The ONH analysis provides the measures of optic disc and neuroretinal rim areas, cup volume and horizontal and vertical cup to disc ratios.

The ganglion cell analysis (GCA) protocol places the 6 x 6 x 2 mm cube centered in the macular region and is designed for retinal topography analysis.111 The GCA algorithm identifies the RPE-Bruch’s membrane junction and inner plexiform layer (IPL) and uses the difference as the combined ganglion cell layer and inner plexiform (GCL/IPL) thickness.111

It has been reported that the inter-visit variability of RNFL thickness is lower in Cirrus HD-OCT compared with Stratus OCT .112,113 The intraclass correlation coefficients (ICC) for average RNFL thickness and optic disc measurements have been reported to be between 0.96-0.99 in healthy and glaucomatous eyes.114,115

Monitoring Glaucoma Progression
Guided Progression Analysis (GPA) of Cirrus HD-OCT uses two baseline images and up to six follow-up images. Cirrus automatically registers the enface OCT fundus images from all exams to the first Baseline exam. Each follow-up exam (3rd through last) is compared to each baseline exam in order to determine if change in RNFL thickness has exceeded the test-retest variability. When only three exams are loaded, comparisons to both baselines must exceed test-retest variability in order to flag ‘Possible Loss’. When four or more exams are loaded, ‘Possible Loss’ requires three of four possible comparisons available for each pair of follow up exams to exceed test-retest variability in order to flag ‘Possible Loss’. If ‘Possible Loss’ occurs at the same location on consecutive visits, it is flagged as likely loss. These comparisons are done at the level of superpixels (average of 4 x 4 pixels), in which case 20 adjacent superpixels must flag in order to flag any change at all, as well as at the level of the TSNIT profile (14 profile locations must flag in order to flag change), and at the level of the presented summary parameters. The spatial and temporal confirmation requirements help prevent excessive flagging due to multiple testing scenarios common to managing glaucoma patients [personal communications with Dr. Mary Durbin at Carl Zeiss Meditec] (See Figure 4).

RTVue Fourier-domain Optical Coherence Tomography
The RTVue-100 FD-OCT (Optovue Inc., Fremont, CA, USA) uses an 840 ± 10 nm supraluminescent diode illumination source, capable of 26,000 A-scans/second, with a frame rate of 256-4096 A-scans/frame with a 5 µm axial and 15 µm transverse resolution, and similar to other FD-OCT technologies uses FFT of collected frequencies to improve the signalto-noise ratio.108,110,116,117

Glaucoma scans- The RTVue OCT provides several scan protocols. The RNFL protocol uses 13 circular scans with diameters of 1.3–4.9 mm manually centered on the optic disc to create a peripapillary RNFL thickness map. The RNFL thickness is calculated as the difference in distance between the ILM and the outer edge of the inner plexiform layer (IPL). The ONH scan protocol is a combination of 13 circular B-scans with diameter range of 1.3 mm to 4.9 mm for RNFL thickness analysis and 12 radial B-scans with a fixed length of 3.7 mm for ONH shape analysis and automatically determines the cup location based on retinal pigment epithelium (RPE) edge points (Figure 5a).118,119 The three-dimensional (3D) disc scan protocol provides high definition images of horizontal and vertical profiles of ONH. The 3D disc scan covers an adjustable square with a default 5 x 5 mm area containing 101 horizontal lines and a total of 51,813 A-scans.119 The ganglion cell complex (GCC) scan protocol provides 3D scans of the macular region and samples the macula with 14928 A-scans over a 7x7mm2 area in 0.6 seconds. The analysis and the display are presented in the form of a 6 mm diameter circle map, which is corresponding to about 20º on the visual field map (10-2 protocol on standard automated perimetry). The GCC measurement square is centered 0.75 mm temporal to the fovea, and therefore, it corresponds to 7º to nasal and 13º to the temporal direction, and 10º superiorly and inferiorly on the visual field.119,120 It has been demonstrated that the GCC is affected in glaucoma.109,120-122 The GCC thickness map provides the overall, superior and inferior hemiretina thickness values, and calculates the superior-inferior difference. It also provides two special pattern analyses based on the percent deviation map: a) the global loss volume (GLV), which measures all negative deviation values normalized by the overall map area, and, b) the focal loss volume (FLV), which measures the negative deviation values in areas of significant focal loss in the foveal region.120

It has been reported that the intra-session coefficient of variability (COV) of RTVue is between 1.3 % and 5.69 %123 , and the inter-session COV of RTVue is between 2.64 % to 6.26 % in normal and glaucoma patients for GCC and RNFL parameters, and that the intra-session COV is unaffected by the severity of disease. Different studies have demonstrated that the RTVue RNFL and inner macular thickness measures are best to discriminate between normal and glaucoma.118,120,123–126

Monitoring Glaucoma Progression
There is no change analysis software available in the current version of RTVue for the evaluation of significant RNFL loss over time. The available option at the moment is a printout that includes several RNFL measurements, the superimposed TSNIT profiles of several visits, the amount of change from one exam to the next, and a trend graph showing the average RNFL thickness values over time, without statistical analysis (see Figure 5b).

Spectralis Fourier-domain Optical Coherence Tomography
Spectralis OCT (Heidelberg Engineering, Heidelberg, Germany) uses dual diode lasers, with wavelengths of 870 nm for FDOCT and 820 nm for CSLO to simultaneously produce OCT and infrared reflectance images. To achieve the highest repeatability, Spectralis OCT incorporates a real time eye tracking system (TruTrack™) that continuously monitors the position of the eye and directs the OCT beam to the correct position. The noise reduction technique combines multiple B-scans captured in the exact same location, filters out random speckle noise, and retains only data common to the entire set of images. The ‘speckle noise reduction’ technique retains data reflected from physical structures while mitigating image noise, and producing higher quality images with finer detail. This technique significantly improves the visualization and measurement of the RNFL and ganglion cell layer (GCL) in the macular region.127–129 TruTrack can also precisely track change over time by automatically looking for the same area on the retina. After selecting any prior scan as a reference scan, the Spectralis OCT can align the reference fundus image with the patient’s current fundus image at a follow-up visit. A rescan function (AutoRescan™) adjusts for eye movement and allows repeat analysis of a precise location.130

RNFL thickness is determined by averaging 16 consecutive circular B-scans of 3.5 mm diameter centered on the optic disc.108,131 The RNFL thickness OU report (see Figure 6) provides the RNFL measurements in six sectors that correspond to the sectors generated by the HRT Moorfields Regression Analysis (MRA) and Glaucoma Probability Score (GPS) reports. RNFL thickness is measured as the difference between the inner margin of the ILM and the outer margin of the RNFL.131

It has been reported that the COV of Spectralis OCT is between 0.46 % and 3.22 % in normal and glaucoma patients for macular and RNFL parameters.130,132–134 The diagnostic accuracy of Spectralis has been compared with Cirrus and RTVue OCTs and it has been reported that at a fixed specificity of 80 %, the sensitivities of these technologies are around 80 % or higher and are not significantly different from each other.110

Monitoring Glaucoma Progression
Currently there is no change analysis software available for the evaluation of significant RNFL or ONH loss over time using Spectralis OCT. The available option at the moment is called “RNFL Change Report” that includes individual baseline and follow-up scans for the overall and sectoral RNFL measurements and classifications. However, there is no statistical analysis available to compare the follow-up RNFL measurement with the baseline. Spectralis OCT also provides an RNFL Trend Report similar to HRT Trend Report that demonstrates the trend of normalized RNFL thickness values in different sectors over time.104

Conclusion
Advanced imaging technologies provide large amounts of reproducible data and have enabled us to discriminate between normal and glaucomatous optic nerves in a more systematic way. Currently, most imaging technologies have comparable diagnostic accuracies but each also has its own limitations. Progression detection software is still relatively new, and we still need to better characterize what constitutes a clinically significant change in glaucoma as gold standard. The scan quality affects the diagnostic accuracy of every device. Poor quality scans can produce unreliable data, even with the most sophisticated technologies. The normative database in each device is also different, which results in ‘outside normal limits’ message that may not always indicate true pathology.135 Therefore, it is essential that clinicians pay attention to the limitations of each technology when choosing their method of imaging and interpreting the tests results and not rely on any single analysis for the diagnosis or monitoring of glaucoma.

Article Information:
Disclosure

The authors have no conflicts of interest to declare.

Correspondence

Mitra Sehi, PhD, Bascom Palmer Eye Institute, University of Miami Miller School of Medicine, 7101 Fairway Drive, Palm Beach Gardens, FL 33418, USA. E: msehi@med.miami.edu

Received

2012-11-10T00:00:00

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