This guest editorial is one of a series looking back at landmark articles published in the JCRS. This special series commemorates the 25th anniversary of the joint Journal of Cataract & Refractive Surgery. This issue: Determining in vivo biomechanical properties of the cornea with an ocular response analyzer. J Cataract Refract Surg 2005;31:156–162.
The publication of Dave Luce's visionary article on corneal hysteresis (CH), a new biomechanical parameter produced by the ocular response analyzer (ORA), not only sparked a completely new line of inquiry but also made corneal biomechanics relevant for the clinician.1 The ORA was the first clinical tool that allowed studies of biomechanics in multiple subspecialties across the globe, from keratoconus and refractive surgery to glaucoma. Prior to 2005, ocular biomechanics were analyzed with ex vivo models and computer simulations. After 2005, clinicians developed new collaborations with basic scientists and engineers as they sought to understand how biomechanics affected disease development and progression in a pressurized, fluid-filled shell and how biomechanical response to surgical interventions affected outcomes. Since 2005, nearly 800 clinical articles that directly investigated CH in cross-sectional and longitudinal studies have been published. Many biomechanical technical articles have also been published including advanced algorithms based on deep learning and artificial intelligence, all of which advance our understanding in this important field.
Ocular biomechanical assessment quantifies the response to an applied load. That load can be destructive, as in ex vivo studies, or nondestructive to be of clinical value. For the ORA, an air puff is used to deform the cornea, making it function also as a noncontact tonometer. It is important to understand what CH represents and what it does not. It does not correspond to stiffness or elastic modulus, as is often misinterpreted in the literature. It does not represent elastic resistance to deformation.2 Low CH can be associated with a more compliant cornea, as in keratoconus, or with a stiffer cornea, as with aging or higher intraocular pressure (IOP).1,3 The inverse relationship with IOP is well documented, such that CH is reduced as IOP increases.3 CH is a viscoelastic parameter that represents the different pathways between loading and unloading, such that the applanation pressure inward is greater than the unloading applanation pressure in the outward direction due to energy dissipation in the viscoelastic material. For example, a stiffer eye with higher IOP is less capable of dissipating energy, resulting in lower CH. Both viscous and elastic responses contribute to CH, and different proportions can result in similar CH.4 This is likely the reason that CH is not different 1 year after crosslinking (CXL) the keratoconic cornea, despite evidence of stiffening in the infrared and pressure signals.5 Both the first and second applanation pressures increase after CXL, without a change in the difference between them, which is the formula for CH (Figure 1). The elastic changes that represent stiffening are masked by the viscous changes that are also induced with CXL.
Analysis of the pressure and infrared signals or waveform of the ORA provides additional important information regarding biomechanics of response, as illustrated with the CXL example. Custom signal analysis was first reported in comparing contralateral eyes after a refractive procedure, one of which was stable and one of which was unstable with evolving iatrogenic ectasia.6 Both eyes had similar CH, but the signal morphology was dramatically distinct, with the unstable eye having lower peaks with an appearance similar to keratoconus, as seen in Figure 2.
Investigators have reported that low CH is predictive of glaucomatous damage cross-sectionally and glaucomatous progression in longitudinal studies.7 However, an important question that arises with these associations is how a biomechanical parameter of the cornea is connected to damage at the optic nerve? It has been suggested that the biomechanical response of the cornea may be a surrogate for the biomechanics at the back of the eye. However, there is recent evidence that the sclera contributes to the measured corneal response. In a comparison of contralateral eyes of 18 subjects, where one eye received a scleral buckle to treat retinal detachment, it was reported that the treated eyes with much stiffer sclera, resulted in a significantly lower CH than the fellow eyes with no treatment.8 There was no statistically significant difference in IOP measured with Goldmann applanation tonometry between eyes. In analysis of the ORA waveform using custom software, it was found that 2 signal features were different, including a shorter Time2 indicating an abbreviated recovery, and smaller Full Width Half Max2 of the second peak indicating greater velocity in the recovery or unloading phase. Figure 3 shows the result of further analysis using the 38 waveform-derived parameters developed by the manufacturer.9 Of the 11 significantly different values between treated and untreated eyes, 3 were standard reported parameters that included both loading and unloading applanation pressures, and 8 were waveform parameters that were all associated with the second peak in the unloading phase. Specifically, a stiffer sclera resulted in increased aspect2, which is the second peak aspect ratio (height/width) and the length of this peak's perimeter (path2). The greater aspect ratio included a lower peak width (w2) and higher slopes of peak rise and fall (uslope2 and dslop2), all indicating rapid corneal movement, and lower area under the second peak (p2area). In other words, the stiffer sclera drove a faster recovery of the concavity to the natural convex shape.
The scleral influence on corneal response to an air puff is consistent with ex vivo and modeling studies, which demonstrate that a stiffer sclera will resist fluid displacement as the cornea becomes concave, thus limiting corneal deformation.10–12 This can be misinterpreted as a stiffer corneal response. Conversely, a more compliant sclera may allow greater deformation, which might be misinterpreted as a more compliant cornea. The scleral contribution will be greater as deformation increases, which explains why those components of the signal associated with unloading are the ones involved with interpreting scleral response. It is proposed that the sclera is the connection between CH and glaucomatous damage at the optic nerve.
These studies lead us to a new interpretation of CH that actually represents ocular hysteresis. The cornea is the point at which the load is applied and the response measured; however, the entire eye is involved in dissipating the energy and contributing to the reported parameters. This response is not confined to the cornea, and it is anticipated the specific involvement of the sclera will generate many additional clinical biomechanical studies with a focus on dissecting the components of the waveform that indicate specific ocular structures.
Unfortunately, Dave Luce passed away in 2017. It is unlikely that he could have realized the broad scope of his invention when the concept of corneal hysteresis was published in the first JCRS special issue on corneal biomechanics in 2005.13 In the current year of 2021, there is no end in sight as to how CH and other new biomechanical parameters may impact patient care and ultimately preserve vision.
Atieh Yousefi Koupaei, PhD, performed the statistical analysis of the ocular response waveform parameters in Figure 3.
1. Luce D. Determining in vivo biomechanical properties of the cornea with an ocular response analyzer. J Cataract Refract Surg 2005;31:156–162
2. Roberts CJ. Concepts and misconceptions in corneal biomechanics. J Cataract Refract Surg 2014;40:862–869
3. Kotecha A, Elsheikh A, Roberts C, Zhu HG, Garway-Heath DF. Corneal thickness- and age-related biomechanical properties of the cornea measured with the ocular response analyzer. Invest Ophthalmol Vis Sci 2006;47:5337–5347
4. Glass DH, Roberts CJ, Litsky AS, Weber PA. A viscoelastic biomechanical model of the cornea describing the effect of viscosity and elasticity on hysteresis. Invest Ophthalmol Vis Sci 2008;49:3919–3926
5. Vinciguerra P, Albé E, Mahmoud AM, Trazza S, Hafezi F, Roberts CJ. Intra- and postoperative variation in ocular response analyzer parameters in keratoconic eyes after corneal cross-linking. J Refract Surg 2010;28:1–8
6. Kérautret J, Colin J, Touboul D, Roberts C. Biomechanical characteristics of the ectatic cornea. J Cataract Refract Surg 2008;34:510–513
7. Zimprich L, Diedrich J, Bleeker A, Schweitzer JA. Corneal hysteresis as a biomarker of glaucoma: current insights. Clin Ophthalmol 2020;14:2255–2264
8. Taroni L, Bernabei F, Pellegrini M, Roda M, Toschi PG, Mahmoud AM, Schiavi C, Giannaccare G, Roberts CJ. Corneal biomechanical response alteration after scleral buckling surgery for rhegmatogenous retinal detachment. Am J Ophthalmol 2020;217:49–54
9. Luce D, Taylor D. Ocular response analyzer. In: Roberts CJ, Liu J, eds. Corneal Biomechanics: From Theory to Practice. Amsterdam, the Netherlands: Kugler Publications; 2016:67–86
10. Metzler K, Mahmoud AM, Liu J, Roberts CJ. Deformation response of paired donor corneas to an air puff: intact whole globe vs mounted corneoscleral rim. J Cataract Refract Surg 2014;40:888–896
11. Nguyen BA, Reilly MA, Roberts CJ. Biomechanical contribution of the sclera to dynamic corneal response in air-puff induced deformation in human donor eyes. Exp Eye Res 2020;191:107904
12. Nguyen BA, Roberts CJ, Reilly MA. Biomechanical impact of the sclera on corneal deformation response to an air-puff: a finite-element study. Front Bioeng Biotechnol 2019;6:210
13. Roberts CJ, Ed. Special issue: corneal biomechanics. J Cataract Refract Surg 2005;31