|Year : 2020 | Volume
| Issue : 2 | Page : 94-100
Corneal biomechanics in glaucoma – A review of the current concepts and practice
Prasanna Venkataraman, MB Madhuri, Neethu Mohan
Department of Glaucoma, Aravind Eye Hospital, Noombal, Chennai, Tamil Nadu, India
|Date of Submission||08-Mar-2020|
|Date of Acceptance||21-Apr-2020|
|Date of Web Publication||17-Jun-2020|
Dr. Prasanna Venkataraman
Glaucoma Services, Aravind Eye Hospital, Poonamallee High Road, Noombal, Chennai - 600 077, Tamil Nadu
Source of Support: None, Conflict of Interest: None
Intraocular pressure (IOP) is currently the only modifiable risk factor in glaucoma. Since all our efforts are directed towards maintaining a stable IOP to halt glaucoma progression, proper understanding about the science behind IOP measurement and biomechanics of cornea becomes paramount. In this paper, we address the basics of corneal biomechanics, recent developments and its impact on glaucoma diagnosis and management. An extensive literature search was done using PubMed and Google Scholar with the search terms such as biomechanics, hysteresis, and glaucoma. Relevant articles published in English language were reviewed.
Keywords: Biomechanics, glaucoma, hysteresis, intraocular pressure, ocular response analyzer
|How to cite this article:|
Venkataraman P, Madhuri M B, Mohan N. Corneal biomechanics in glaucoma – A review of the current concepts and practice. TNOA J Ophthalmic Sci Res 2020;58:94-100
|How to cite this URL:|
Venkataraman P, Madhuri M B, Mohan N. Corneal biomechanics in glaucoma – A review of the current concepts and practice. TNOA J Ophthalmic Sci Res [serial online] 2020 [cited 2020 Jul 13];58:94-100. Available from: http://www.tnoajosr.com/text.asp?2020/58/2/94/286934
| Introduction|| |
Glaucoma is a chronic progressive optic neuropathy with widely known modifiable risk factor – intraocular pressure (IOP). Although there are many IOP-independent factors in glaucoma pathogenesis, we have better understanding of the IOP-dependent mechanisms in glaucoma. IOP reduction has been proven to halt glaucoma progression by many landmark studies in glaucoma. We strive to maintain a target IOP (surgically and medically), so that our patient does not become a fast progressor culminating in blindness. Since all our energy is directed toward IOP reduction, precise measurement of IOP cannot be overemphasized.
Despite the introduction of many new tonometers, the gold standard for IOP measurement is still the Goldmann applanation tonometer (GAT). It is a variable force applanation tonometer based on the Imbert-Fick principle. This principle states that the fluid pressure within a spherical body is directly proportional to the force required to flatten (or applanate) a defined area of the sphere. The assumptions include that the sphere is infinitely thin, perfectly elastic, dry, and perfectly flexible. We all know the flaws associated with this tonometer as cornea is neither a sphere nor dry. During the design of the tonometer, much thought was not invested in central corneal thickness (CCT), which was presumed to be almost the same across individuals. But with the results the Ocular Hypertension Treatment Study (OHTS), the importance of CCT came into limelight. Further research in the field of corneal biomechanics confirmed the superiority of corneal hysteresis over CCT in glaucoma management. This paper reviews impact of corneal biomechanics on glaucoma diagnosis and management. An extensive literature search was done using PubMed and Google Scholar with the search terms such as biomechanics, hysteresis, and glaucoma. Relevant articles published in English language were considered.
| Central Corneal Thickness: the Good and Bad|| |
The mean CCT of healthy controls has been shown to be 520 μ with a Gaussian distribution. CCT can be measured by contact and noncontact methods. The CCT derived from these methods are not interchangeable. Of the various tools available, ultrasonic pachymetry [Figure 1] remains the most reliable way of measuring CCT due to its high reproducibility.
GAT was designed presuming the CCT to be 500 μ, so any deviation from this value can introduce errors in measurement. Goldmann found that his tonometer underestimated IOP in thin corneas and overestimated in thick corneas. GAT considers only the external applanation force and the internal IOP. The intrinsic viscoelastic properties of the cornea can have a bigger impact on IOP measurement. The same external applanation force can cause more deformation of a soft cornea (say in corneal edema) underestimating the IOP, even though the CCT can be high. Conversely, a thin cornea with scarring may have a higher IOP reading due to increased rigidity. Collagen cross-linking used to treat keratoconus can result in corneal stiffening, leading to increase in IOP measured by GAT.
Ehlers et al. found that GAT-IOP was most accurate when the CCT was 520 μ with their manometric studies. They suggested a nomogram to correct GAT-IOP based on CCT, making a correction of 7 mmHg for every 100 μ deviation from 520 μ cutoff. Many investigators have attempted to design linear and nonlinear formulae to obtain a CCT-corrected GAT-IOP, but without satisfactory results. This way of correcting IOP based on CCT serves little purpose, without any measurable clinical benefit to the patient, hence best avoided.
OHTS helped us get a better insight into clinical management of our patients. Eyes that had a CCT of 555 μ or lesser had a 3-fold increased risk of conversion to glaucoma, compared with eyes that a CCT of 588 μ or greater. Furthermore, the hazard ratio for glaucoma conversion was 1.82, for each 40 μ thinning of CCT. The Early Manifest Glaucoma Trial (EMGT) also showed that a lower CCT value was a significant risk factor for progression of early manifest glaucoma in patients with a high baseline IOP. The combined OHTS European Glaucoma Prevention Study (OHTS-EGPS) model also confirmed CCT as a significant predictor for the onset of glaucoma, with every 40 μ decrease in CCT associated with a twofold risk over 5 years.
We now clearly know the impact of CCT on glaucoma, but with no validated nomogram to incorporate into clinical practice, how do we use this data? The answer lies in risk profiling of the patient. The risk factors for conversion to glaucoma in OHTS were baseline older age, higher IOP, thinner CCT, large Cup-to-Disc ratio, greater PSD in visual fields. Instead of just attempting to find the “true” corrected IOP, it would be prudent to take all the risk factors into account, determine the patient's risk and then take clinical decisions.
With the advent of refractive surgeries, CCT has gained a bigger role. The risk of intraoperative IOP spike and the post-LASIK thin CCT related IOP underestimation are the major concerns. In addition, most of these patients undergoing refractive surgery have myopia. Myopia is a known risk factor for glaucoma, compounded by the difficulty of differentiating myopic disc from glaucomatous disc. GAT and CCT-corrected IOP formulae can lead to gross underestimation of glaucoma risk in these young individuals. Hence, is there a way to circumvent CCT during tonometry?
The Pascal dynamic contour tonometer (DCT, Zeimer Ophthalmic Systems AG, Port, Switzerland) is a slit-lamp mounted, non-applanation, digital, contact tonometer [Figure 2] that provides continuous tonometry recordings to measure the IOP. It calculates the difference between systolic IOP and diastolic IOP, which is defined as the ocular pulse amplitude. It represents the pulsatile wave front produced by the varying amount of blood in the eye during the cardiac cycle [Figure 3]. The DCT measurement principle is based on contour matching of anterior corneal surface. The DCT compensates for all forces exerted on the cornea and an electronic sensor measures IOP independent of the corneal properties [Figure 4].
DCT IOP is less influenced by keratorefractive surgery than GAT IOP, as shown by Kaufmann et al. DCT IOP measurements seem to agree closely with manometric measurements as shown by Boehm et al. DCT is a constant force tonometer, measuring IOP in a continuous fashion, requiring the probe to be in contact with the cornea for about 8 s. Thus, it is a relatively difficult technique with limited clinical adoption due to the need for patient cooperation.
Rebound Tonometer (ICare, Helsinki, Finland) is a hand-held device based on impact-induction principle [Figure 5]. It measures the deceleration of a small magnetic solenoid probe on the surface of the cornea at a distance of 4–8 mm. As the process is fast, it can be done easily even in children and uncooperative patients, without the need for a topical anesthetic. The rebounding velocity closely reflects the IOP and final IOP is displayed after six consecutive measurements. Compared to GAT, ICare overestimates IOP especially at higher CCTs.
With the complexity surrounding CCT, is it possible that the effect of CCT on glaucoma could just be a tonometry artifact? Not really. Many studies including EMGT, Barbados Eye Study, Los Angeles Latino Eye Study have established CCT as an independent risk factor for glaucoma development. CCT is also one of the most heritable of the risk factors for glaucoma. A thin CCT associated with a thin lamina cribrosa might have less rigidity, leading to more displacement by IOP fluctuations. Siegfried et al. associated increased trabecular exposure to oxidative damage as an important risk factor for primary open angle glaucoma (POAG) in patients with thin CCT. Further research into why CCT has an influence on glaucoma has opened up the gates to corneal biomechanics and its association with lamina cribrosa physiology.
| Corneal Biomechanics: Back to Basics|| |
Cornea is a complex composite of collagen, proteoglycans, water, and other elements, contributing to 45 D of the total 60 D refractive power of the eye. Hence, many refractive procedures are targeted at the cornea to correct Myopia/Hyperopia. Postrefractive procedures, the biomechanical properties of the residual bed and corneal flap are no longer the same. Using only CCT in this group of patients will make us complacent with respect to glaucoma identification and management. With the advent of collagen cross-linking for keratoconus, corneal biomechanics has gained a bigger role.
A material is said to be elastic when it has a linear relationship between stress-strain [Figure 6]. When a force is applied, the elastic material deforms and reverts back to its original state instantly when the force is removed. Young's modulus is defined as the ratio of the stress (load per unit area) and the strain (deformation/displacement per unit length). Viscoelastic materials, on the other hand, display both viscous and elastic properties, with a slow relaxation time as a portion of applied energy is dissipated.
Cornea is a nonlinear viscoelastic structure, comprising up to 80% water in its stroma. Viscoelastic materials are characterized by hysteresis. Hysteresis, in Greek translates to “laggingbehind.” Corneal hysteresis (CH) reflects the ability of corneal tissue to absorb and dissipate energy during a bidirectional applanation process. Hysteresis measures how a material responds to the loading and unloading of an applied force. In simple language, it measures the ability of the eye to absorb shock. CCT is a static geometric parameter, but hysteresis is a dynamic biomechanical property of the cornea. It can be measured with Ocular Response Analyser (ORA Reichert Ophthalmic Instruments, Depew, NY, USA), which was approved in 2005.
The ORA is based on noncontact tonometer technology, which uses a 25 ms air jet to apply force to the cornea [Figure 7]. This causes the cornea to bend inward, past first applanation (P1) and after few milliseconds, the air jet is shut down, bringing the cornea back to the rest stage, past second applanation (P2). The 2 applanations are completed within a short span of 20 ms. An electro-optical collimation detector system monitors the corneal deformation.
| Ocular Response Analyser Measurements|| |
Goldmann-correlated intraocular pressure
The average of P1 and P2 provides a Goldmann-correlated IOP value referred to as IOPg. Good correlation of IOPg with GAT-IOP has been established by Ehrlich et al.
The difference between P1 and P2 is termed corneal hysteresis (in mmHg) [Figure 8]. P1 and P2 will be the same if cornea was purely elastic, exhibiting a linear relationship during stress-strain. In reality, P2 is lower than P1, primarily because of the viscoelasticity of cornea. When applanation force is applied on the cornea it deforms to a certain degree. When the force is stopped, it regains its original shape, losing some of the energy in the process, leading to two different applanation pressures. Normal CH values are between 8 mm Hg and 15 mm Hg with considerable inter-individual variation. Eyes with higher CH values can adapt better when subjected to an increase in IOP, whereas eyes with lower CH values have less tissue adaptation to deal with IOP elevation. It has been suggested by Pensyl et al. that low CH eyes have higher risk of glaucomatous optic neuropathy due to reduced capacity of the eyewall to dampen IOP spikes and/or reduced ability of optic nerve structures to respond to IOP fluctuations.
Corneal compensated intraocular pressure
Corneal compensated IOP is another measurement given by ORA. It is relatively cornea-independent, unlike other tonometers. It agrees with GAT-IOP on average, hence one can use IOPcc like GAT-IOP, except that it is less affected by corneal biomechanics. It has been reported to remain fairly constant after refractive surgery.
Corneal resistance factor
Corneal resistance factor (CRF) – An index of corneal resistance is calculated as P1-kP2, where k is a constant derived from empirical observation of relationship between P1, P2, and CCT. It is CCT weighted, placing more emphasis on P1 and hence heavily weighted by the elastic properties of cornea. Normal values for CRF are similar to those for CH. CRF is more affected by CCT than CH. It is more useful in corneal pathology such as keratoconus or pellucid marginal degeneration A waveform score of at least 6.5 in a software-generated scale of 0–10 is recommended by the manufacturer for a good quality measurement. If the wave score is <6.5, the test should be repeated. Clinical significance of many other parameters derived from deformation signal waveform is also being studied.
The Corneal Visualisation Scheimpflug Technology tonometer (Corvis ST tonometry: CST; Oculus, Wetzlar, Germany) is the latest instrument that allows quantitative and visual assessment of corneal biomechanics. It is a combination of noncontact air pulse tonometer with an ultrahigh speed scheimpflug camera, capturing 4330 images per se cond, helping us to directly visualize the associated corneal movement [Figure 9]. It measures CCT, deformation amplitude, applanation length and corneal velocity. It also generates a biomechanical corrected IOP, which is corrected for CCT and other corneal properties. Matsuura et al. showed repeatability and usefulness in identifying glaucoma progression. Among the parameters derived from this relatively new tonometer, eyes with large highest concavity deformation amplitude [Figure 10], a large A2 length, or, small A1 deformation amplitude are at high risk of glaucoma progression. Corvis ST is also used to visualize and quantify the effect of cross-linking.
Corneal Hysteresis: How It Behaves in Normal and Abnormal Eyes?
CH is influenced by many factors: Age, CCT, IOP, glycosylated hemoglobin, glaucoma diagnosis and glaucoma severity. CH and CRF have a negative correlation with age, as cornea stiffens with age with reduced ability to dissipate energy. The mean values for CH and CRF respectively were 10.49 ± 1.67 mmHg for CH and 10.50 ± 1.44 mmHg for CRF, in a study published by Pillunat et al. Africans were found to have low CH and CRF than Caucasians in a study by Detry-Morel et al. Corneal hysteresis is lower in patients with glaucoma, acquired optic nerve pits and corneal disorders such as Fuchs', keratoconus. Many studies have reported a positive correlation between CCT and CH and also with CRF. A thicker cornea with more collagen fibers and ground substance can better resist the load of the IOP than a thinner one.
Garcia-Porta noted 1–3 mmHg reduction in CH and CRF after different laser refractive treatments in their review article. The native structure of cornea is altered after these refractive surgeries which involve severing of collagen fibers to varying extent. The biomechancics of laser ablated residual stromal bed and corneal flap will not be the same as native cornea. Mardelli et al. in their study on effect of photorefractive keratectomy on GAT-IOP, found a mild lowering of IOP. They proposed that the presence or absence of Bowman's membrane could alter the corneal resistance, leading to errors in GAT-IOP measurements.
Collagen cross-linking for keratoconus management significantly improves elastic modulus of cornea, but corresponding increase in CH has not been reported in many studies. This likely arises from a simultaneous change in corneal viscosity, which masks the increase in elastic modulus in the viscoelastic response measured by hysteresis. In similar lines, CH is reported to be higher in diabetics, due to glycosylation of proteoglycans and/or increased collagen cross-linking.
Postpenetrating keratoplasty (PK) and Deep Anterior Lamellar Keratoplasty (DALK) eyes were reported to have low CH and CRF, with post DALK eyes faring better than post PK eyes (in terms of CH and CRF). The proposed mechanism was the intact Descemet membrane, which supports the overlying stroma in these lamellar surgeries.
Increasing IOP also has an effect on CH. As IOP increases, CH decreases. As the globe stiffens from high IOP its dampening capacity decreases, resulting in larger increases in IOP from small increases in intraocular volume. The collagen fibers do not yield further and the CH becomes low. This transmits the IOP load to the weakest portion of the eye around the optic nerve head. Wells et al. in their experimental study on changes in optic disc depth during IOP elevation found that CH and not CCT, had a relationship with optic disc surface compliance. CH hence reflects properties of the entire eye rather than just the cornea. It serves as a surrogate measure of the ability of the posterior segment to withstand stress.
| Corneal Hysteresis in Glaucoma: What to Expect?|| |
CH and CRF are lower in POAG and pseudoexfoliation glaucoma as shown by many studies including Mangouritsas et al. and Abitbol et al. Narayanaswamy et al. reported that the effect was less pronounced in angle closure glaucoma, however CH values were lower compared with controls. CH has a significant role to play in ocular hypertensives (OHT). CH, CRF were found to be higher in OHT than POAG in studies by Pillunat et al. and Shah et al. The damping effect of CH may explain why, despite high IOP, OHT patients are protected from glaucoma. As expected, CH and CRF were reported to lower in normal tension glaucoma, compared to POAG in studies by Kaushik et al. and Shah et al. Morita et al. studied IOP and corneal mechanical properties of normal and NTG eyes and found high IOPcc, low CRF and CH in NTG eyes.
Many studies have explored CCT and CH in primary congenital glaucoma (PCG), but with mixed results. Paletta Guedes et al. in their longitudinal study on PCG eyes, found that the mean CCT in PCG was thicker before surgery and became comparable to the mean CCT in a normal population after surgical treatment. Kirwan et al. found CH to be lower in majority of congenital glaucoma patients.
Due to the lack of prospective studies, it is not clear whether CH is a risk factor for glaucoma progression or progressing glaucoma produces long term changes in corneal hysteresis. De Moraes et al. found that progressing eyes had lower CH and CCT measurements compared with nonprogressing eyes. Medeiros et al. sought to find the association between CH and glaucoma progression. They studied 68 glaucoma patients with ORA, GAT-IOP, CCT and Visual fields every 6 months for 4 years and found that eyes with CH, lesser than 10 mm Hg had significantly faster glaucoma progression. They also analyzed CH's versus CCT's predictive abilities, and found CH had greater prognostic ability than CCT; each 1 mmHg lower CH was associated with a 0.25% per-year faster rate of visual field index decline.
| Prostaglandins and Biomechanics: What Are We Really Measuring Clinically?|| |
Topical medications used to treat glaucoma can have an effect on CCT and CH. Many reports have been published with conflicting results on their effect on corneal properties. Prostaglandin analogues (PGA), by activating matrix metalloproteinases, can degrade extracellular matrix compounds with a possible effect on CCT and CH.
Birt et al. studied the effect of CCT on response to PGA therapy found that the thinner corneas had greater IOP reduction when analyzed at 12 weeks. In OHTS, patients with thicker corneas showed smaller IOP response to medical treatment than patients with thinner corneas. Thicker corneas which are inherently less mechanically compliant may impair drug penetration. This concept of differential corneal compliance has to be kept in mind when treating patients with thicker and thinner corneas, before labeling them as “nonresponders/high responders” to certain classes of topical medications.
Bolivar et al. analyzed the effect of latanoprost on CH and found it increased CH that is not related to the amount of decrease in GAT-IOP. Wu et al. studied the changes in biomechanics after long term PGA therapy in POAG patients with Corvis ST and found that PGA treated eyes had higher deformation amplitude. In addition to the IOP and CCT decrease, PGA increases the corneal deformation properties also. PGA definitely produces extracellular matrix remodeling, but their direct, long-term effect on CCT and CH needs further longitudinal analyses.
| Corneal Hysteresis in Daily Glaucoma Practice: Treat Versus Monitor|| |
ORA can help us measure IOP in a more objective way, making it more patient-friendly as it avoids anesthetic drops and fluorescein as well. As it is non-contact, the risk of cross-infection and sterilization concern is also eliminated.
CH has great potential in managing glaucoma suspects. These include patients with borderline IOP, inconclusive visual fields, or poor structure-function correlation. Although many investigations including ganglion cell analysis, OCT angiography and electrophysiological testing can help the clinician, CH is an easy alternative with potential role in glaucoma progression assessment. When considered together with IOP, CCT, optic disc examination, visual fields and OCT, CH can help us in risk profiling of our patients. For example, an OHT patient with thin CCT and low CH deserves more attention than a patient with thick CCT and high CH. This can help us escalate therapy in high risk individuals and provide longer follow-ups in low risk patients, thus reducing strain on patient and clinician resources. It can provide clues in understanding progression despite achieving “target IOP “and in those patients with bilateral but asymmetric disease.
| Conclusion|| |
CCT is a strong independent risk factor for conversion from OHT to POAG. OHTS unveiled its importance in glaucoma management. CH is a newly described corneal biomechanical parameter which reflects the ability of the cornea to dampen IOP fluctuations. With the advent of modern refractive surgeries, CH will be a valuable addition to IOP and CCT in our understanding about glaucoma. While the hunt for an ideal tonometer is still on, understanding the inherent flaws of current tonometers and fluctuations of IOP is paramount. More longitudinal studies in the field of biomechanics can help us better incorporate CH in our everyday glaucoma practice.
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Conflicts of interest
There are no conflicts of interest.
| References|| |
Hansen FK. A clinical study of the normal human central corneal thickness. Acta Ophthalmol (Copenh) 1971;49:82-9.
Miglior S, Albe E, Guareschi M, Mandelli G, Gomarasca S, Orzalesi N. Intraobserver and interobserver reproducibility in the evaluation of ultrasonic pachymetry measurements of central corneal thickness. Br J Ophthalmol 2004;88:174-7.
Kymionis GD, Grentzelos MA, Kounis GA, Portaliou DM, Detorakis ET, Magarakis M, et al
. Intraocular pressure measurements after corneal collagen crosslinking with riboflavin and ultraviolet A in eyes with keratoconus. J Cataract Refract Surg 2010;36:1724-7.
Ehlers N, Bramsen T, Sperling S. Applanation tonometry and central corneal thickness. Acta Ophthalmol (Copenh) 1975;53:34-43.
Bolivar G, Moreno-Arrones JP, Teus MA. Cornea and Glaucoma, In: S. Rumelt (Ed.), Glaucoma – Basic and Clinical Aspects, InTech, Rijeka, 2013.
Kaufmann C, Bachmann LM, Thiel MA. Intraocular pressure measurements using dynamic contour tonometry after laser in situ
keratomileusis. Invest Ophthalmol Vis Sci 2003;44:3790-4.
Boehm AG, Weber A, Pillunat LE, Koch R, Spoerl E. Dynamic contour tonometry in comparison to intracameral IOP measurements. Invest Ophthalmol Vis Sci 2008;49:2472-7.
Belovay GW, Goldberg I. The thick and thin of the central corneal thickness in glaucoma. Eye (Lond) 2018;32:915-23.
Siegfried CJ, Ying-Bo S, Bai F, Beebe DC. Central corneal thickness correlates with oxygen levels in the human anterior chamber angle. Am J Ophthalmol 2015;159:457-62.
Deol M, Taylor DA, Radcliffe NM. Corneal hysteresis and its relevance to glaucoma. Curr Opin Ophthalmol 2015,26:96-102.
Luce DA. Determiningin vivo
biomechanical properties of the cornea with an ocular response analyzer. J Cataract Refract Surg 2005;31:156-62.
Ehrlich JR, Haseltine S, Shimmyo M, Radcliffe NM. Evaluation of agreement between intraocular pressure measurements using Goldmann applanation tonometry and Goldmann correlated intraocular pressure by Reichert's ocular response analyser. Eye (Lond) 2010;24:1555-60.
Liu J, Roberts CJ. Influence of corneal biomechanical properties on intraocular pressure measurement: Quantitative analysis. J Cataract Refract Surg 2005;31:146-55.
Pensyl D, Sullivan-Mee M, Torres-Monte M, Halverson K, Qualls C. Combining CH with CCT and IOP for glaucoma risk assessment. Eye 2012;26:1349-56.
Medeiros FA, Weinreb RN. Evaluation of the influence of corneal biomechanical properties on intraocular pressure measurements using the ocular response analyzer. J Glaucoma 2006;15:364-70.
Pepose JS, Feigenbaum SK, Qazi MA, Sanderson JP, Roberts CJ. Changes in corneal biomechanics and intraocular pressure following LASIK using static, dynamic, and noncontact tonometry. Am J Ophthalmol 2007;143:39-47.
Matsuura M, Murata H, Fujino Y, Yanagisawa M, Nakao Y, Nakakura S, et al
. Repeatability of the Novel Intraocular Pressure Measurement From Corvis ST. Transl Vis Sci Technol 2019;8:48.
Sharifipour F, Panahi-Bazaz M, Bidar R, Idani A, Cheraghian B. Age-related variations in corneal biomechanical properties. J Curr Ophthalmol 2016;28:117-22.
Pillunat KR, Hermann C, Spoerl E, Pillunat LE. Analyzing biomechanical parameters of the cornea with glaucoma severity in open-angle glaucoma. Graefes Arch Clin Exp Ophthalmol 2016;254:1345-51.
Detry-Morel M, Jamart J, Hautenauven F, Pourjavan S. Comparison of the corneal biomechanical properties with the Ocular Response Analyzer® (ORA) in African and Caucasian normal subjects and patients with glaucoma. Acta Ophthalmol 2012;90:e118-24.
Franco S, Lira M. Biomechanical properties of the cornea measured by the Ocular Response Analyzer and their association with intraocular pressure and the central corneal curvature. Clin Exp Optom 2009;92:469-75.
Garcia-Porta N. Corneal biomechanical properties in different ocular conditions and new measurement techniques. ISRN Ophthalmol 2014;2014:724546.
Mardelli PO, Piebenga LW, Whitacre MM, Siegmund KD. The effect of excimer laser photorefractive keratectomy on intraocular pressuremeasurements using the goldmann applanation tonometer. Ophthalmology 1997;104:945-49.
Vinciguerra P, Albè E, Mahmoud AM, Trazza S, Hafezi F, Roberts CJ. Intra and postoperativevariation in ocular response analyzer parameters in keratoconic eyes after corneal cross-linking. J Refract Surg 2010;26:669-76.
Wells AP, Garway-Heath DF, Poostchi A, Wong T, Kenneth CY, Sachdev CN. Corneal hysteresis but not corneal thickness correlates with optic nerve surface compliance in glaucoma patients. IOVS 2008;49:3262–68.
Mangouritsas G, Morphis G, Mourtzoukos S, Feretis E. Association between corneal hysteresis and central corneal thickness in glaucomatous and non-glaucomatous eyes. Acta Ophthalmol 2009;87:901-5.
Abitbol O, Bouden J, Doan S, Hoang-Xuan T, Gatinel D. Corneal hysteresis measured with the Ocular Response Analyzer in normal and glaucomatous eyes. Acta Ophthalmol 2010;88:116-9.
Narayanaswamy A, Su DH, Baskaran M, Tan AC, Nongpiur ME, Htoon HM, et al
. Comparison of ocular response analyzer parameters in Chinese subjects with primary angle-closure and primary open-angle glaucoma. Arch Ophthalmol 2011;129:429-34.
Shah S, Laiquzzaman M, Mantry S, Cunliffe I. Ocular response analyzer to assess hysteresis and corneal resistance factor in low tension, open angle glaucoma and ocular hypertension. Clin Exp Ophthalmol 2008;36:508-13.
Kaushik S, Pandav SS, Banger A, Aggarwal K, Gupta A. Relationship between corneal biomechanical properties, central corneal thickness, and intraocular pressure across the spectrum of glaucoma. Am J Ophthalmol 2012;153:840-900.
Morita T, Shoji N, Kamiya K, Fujimura F, Shimizu K. Corneal biomechanical properties in normal-tension glaucoma. Acta Ophthalmol 2012;90:e48-53.
Paletta Guedes RA, Pena AB, Paletta Guedes VM, Chaoubah A. Longitudinal evaluation of central corneal thickness in congenital glaucoma. J Fr Ophtalmol 2016;39:706-10.
Kirwan C, O'Keefe M, Lanigan B. Corneal hysteresis and intraocular pressure measurement in children using the reichert ocular response analyzer. Am J Ophthalmol 2006;142:990-2.
de Moraes CV, Hill V, Tello C, Liebmann JM, Ritch R. Lo wer corneal hysteresis is associated with more rapid glaucomatous visual field progression. J Glaucoma 2012;21:209-13.
Medeiros FA, Meira-Freitas D, Lisboa R, Kuang TM, Zangwill LM, Weinreb RN. Corneal hysteresis as a risk factor for glaucoma progression: A prospective longitudinal study. Ophthalmology 2013;120:1533-40.
Birt CM, Buys YM, Kiss A, Graham E. Trope and the Toronto Area Glaucoma Society. The influence of central corneal thickness on response to topical prostaglandin analogue therapy. CJO 2012;47:51–4.
Brandt JD, Beiser JA, Gordon O, Kass MA. The Ocular Hypertension Treatment Study (OHTS) Group. Central corneal thickness and measured IOP response to topical ocular hypotensive medication in the ocular hypertension treatment study. Am J Ophthal 2004;138:717-22. [Doi: 10.1016/j.ajo.2004.07.036].
Bolivar G, Sanchez-Barahona C, Teus M, Castejon MA, Paz-Moreno-Arrones J, Gutiérrez-Ortiz C, et al
. Effect of topical prostaglandin analogues on corneal hysteresis. Acta Ophthalmol 2015; 93:e495-8.
Wu N, Chen Y, Yu X, Li M, Wen W, Sun X. Changes in corneal biomechanical properties after long-term topical prostaglandin therapy. PLoS One 2016;11:e0155527.
[Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5], [Figure 6], [Figure 7], [Figure 8], [Figure 9], [Figure 10]