the use of the reichert ocular response analyser to establish the relationship between ocular...
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Contact Lens & Anterior Eye 29 (2006) 257–262
The use of the Reichert ocular response analyser to establish the
relationship between ocular hysteresis, corneal resistance
factor and central corneal thickness in normal eyes
Sunil Shah a,b,c,*, Mohammed Laiquzzaman a, Ian Cunliffe a,b,c, Sanjay Mantry a,c
a Heart of England Foundation Trust, Solihull, UKb Ophthalmic Research Group Neurosciences Research Institute, Aston University, Birmingham, UK
c Birmingham and Midland Eye Centre, Birmingham, UK
Abstract
Purpose: The aim of this study was to measure ocular hysteresis and corneal resistance factor (CRF), novel methods of analysing ocular
rigidity/elasticity and to determine the relationship between central corneal thickness (CCT), hysteresis and CRF in normal subjects.
Design: Prospective, cross-sectional, clinical trial.
Participants: The study included 207 normal eyes.
Methods: Hysteresis and CRF were measured by the ocular response analyser. The CCTwas measured using a hand held ultrasonic pachymeter.
Main outcome measures: Ocular hysteresis and CRF in normal patients and their relationship with CCT.
Results: The mean hysteresis was 10.7 � 2.0 mmHg standard deviation (S.D.) (range 6.1–17.6 mmHg); the mean CRF was 10.3 � 2.0 (range
5.7–17.1 mmHg). The mean CCT was 545.0 � 36.4 mm (471–650 mm). The relationship between hysteresis and CCT; CRF and CCT; CRF
and hysteresis were significant ( p < 0.0001).
Conclusion: This study demonstrated that corneal hysteresis increased with increasing CCT, however, the correlation was moderate. It would
appear that CCT, hysteresis and CRF may measure different biomechanical aspects of ocular rigidity and are likely to be useful additional
measurement to CCT in the assessment of ocular rigidity when measuring intraocular pressure (IOP). This may be of particular importance
when trying to correct IOP measurements for increased or decreased ocular rigidity.
# 2006 British Contact Lens Association. Published by Elsevier Ltd. All rights reserved.
Keywords: Hysteresis; Central corneal thickness; Elasticity; Rigidity
1. Introduction
The cornea is a mechanically tough membrane that forms
a barrier between the eye and the external environment.
Several studies have been performed in the past to determine
the rigidity (elasticity) of the cornea [1–4]. Primarily these
were performed to study tonometry [5–7].
Various studies have argued that intraocular pressure
(IOP) measured by the applanation tonometer does not
* Corresponding author at: Heart of England Foundation Trust, Lode
Lane, Solihull, West Midlands B91 2JL, UK. Tel.: +44 121 424 4074;
fax: +44 121 424 5462.
E-mail addresses: [email protected],
[email protected] (S. Shah).
1367-0484/$ – see front matter # 2006 British Contact Lens Association. Publi
doi:10.1016/j.clae.2006.09.006
always give a true reading [8–12]. More recent studies have
demonstrated the importance of central corneal thickness
(CCT) measurements when trying to assess true IOP rather
than measured IOP [13]. However, these studies were
essentially using CCT as a measure of ocular rigidity and to-
date, CCT has been the most convenient measure of this
parameter [14]. Recently, Liu and Roberts [15] reported that
in their model, tonometry readings did not always reflect
true IOP values—they deviated when CCT, curvature or
biomechanical properties varied from normal values.
Previous studies that have tried to determine ocular
rigidity, have either been performed in vitro and/or involved
complicated mathematical calculations and thus are not
practical for clinicians. To-date, there has not been any easy
method reported to determine the biomechanical properties
shed by Elsevier Ltd. All rights reserved.
S. Shah et al. / Contact Lens & Anterior Eye 29 (2006) 257–262258
Fig. 1. Measurement of ocular hysteresis. 1, convex cornea; 2, flat cornea;
3, concave cornea; 4, flat cornea; 5, convex cornea. Reproduced with
permission from Reichert1.
of the cornea in vivo. Reichert ophthalmic instruments
(Buffalo, NY) have developed a new device: the ocular
response analyser (ORA) which is an adaptation of their
non-contact tonometer that allows measurement of IOP as
well as new measurements called hysteresis and corneal
resistance factor (CRF).
Hysteresis and CRF are determined by releasing an air
puff from the ORA that causes inward and then outward
corneal motion which in turn provides two applanation
measurements during a single measurement process (Fig. 1).
It has been suggested by Reichert that hysteresis may be a
measurement which is the result of the damping of the
cornea because of its visco-elastic properties and is derived
from the difference of the two applanation measurements
during the applanation process. Thus the hysteresis is a
measure of visco-elasticity due to the combined effect of the
corneal thickness and rigidity etc [16]. The ORA also
provides a basis for an additional parameter: CRF. Reichert
believes that CRF is dominated by the elastic properties of
the cornea and appears to be an indicator of the overall
‘‘resistance’’ of the cornea.
This study was performed to measure ocular hysteresis
and CRF and to determine the relationship between CCT,
hysteresis and CRF in normal subjects.
Fig. 2. Histogram of hy
2. Materials and methods
A total of 207 normal eyes of volunteers (42 males and 63
females) were studied. The patients were recruited from the
staff and the relatives of the patients attending the
ophthalmology clinic in a teaching hospital in Birmingham,
UK. The mean age of the subjects was 62.1 � 18.1 years
standard deviation (S.D.) (range 18.0–87.0 years). All
patients had normal eyes on history and examination. None
of the patients were suffering from glaucoma or had suffered
any previous eye surgery/injury or eye infection. They were
not using any topical ocular medication. There was no
history of systemic disease affecting eye.
The study and data accumulation was performed with
approval from the Local Ethical Committee and informed
consent was obtained from each subject participating in
this study.
Hysteresis and CRF were measured while the subject
was sitting comfortably in a chair using the ORA. The
patient was asked to fixate at the target (a red blinking
light) in the ORA, and the ORA was activated by pressing a
button attached to the computer. A non-contact probe
scanned the central area of the eye and released an air puff.
A signal was then sent to the ORA. The ORA then
displayed the IOP, hysteresis and CRF on the monitor of
the computer attached to the ORA (software version 3).
Hysteresis and CRF of both eyes was measured, only one
measurement was taken for each eye. The CCT was
measured using a hand held ultrasonic pachymeter (DGH-
550, DGH Technology Inc., Exton, PA). The patient was
seated in a chair and drop of topical anaesthetic
Proxymethacaine (Bausch & Lomb, Rochester, NY) was
instilled in both eyes prior to performing pachymetry. The
patient was asked to fixate at a target in order to minimise
any eye movement and to avoid damage to the corneal
epithelium. The pachymeter probe was gently placed onto
the mid-pupillary axis in a perpendicular orientation. Upon
contact with the corneal surface, the CCT value was
displayed on the monitor attached to the probe. Three
readings were taken and the mean value was used as
the CCT.
steresis and CRF.
S. Shah et al. / Contact Lens & Anterior Eye 29 (2006) 257–262 259
Fig. 3. Histogram of CCT. Fig. 5. Scatter plot of relationship between hysteresis and CCT.
3. Statistical analysis of data
Several computer packages were used to analyse and
present the data obtained. These included Excel (Microsoft
Corporation, Redmond, WA) and Medcalc (Med Calc
Software, Mariakerke, Belgium).
For general statistical reporting, the mean values
from each data set were calculated along with the S.D.
The distribution of values within each data set were
evaluated graphically. The level of statistical significance
was chosen at p < 0.05. All graphs were constructed using
Medcalc.
4. Results
The mean CCT for all eyes was 545.0 � 36.4 mm S.D.
(range 471–650 mm), hysteresis was 10.7 � 2.0 mmHg S.D.
(range 6.1–17.6 mmHg) and CRF was 10.3 � 2.0 mmHg
S.D. (range 5.7–17.1 mmHg).
Fig. 4. Scatter plot of relationship between CRF and hysteresis.
Figs. 2 and 3 show the frequency of distribution of CCT
and hysteresis and CRF. Fig. 4 is the scatter plot
demonstrating the relationship between CRF and hysteresis.
The correlation coefficient was strong (r = 0.8) and the
relationship was significant ( p < 0.0001). The regression
equation for Fig. 4 is:
CRF ¼ 1:294þ 0:846 hysteresis:
Figs. 5 and 6 are scatter plots demonstrating the
relationship between hysteresis and CCT; CCT and CRF,
respectively.
Regression equations for Figs. 5 and 6 are:
Hysteresis ¼ 0:023� 1:776 CCT
CRF ¼ 0:025� 3:499CCT:
The correlation coefficients were moderate (r = 0.426
and 0.467, respectively) but the relationship was significant
( p < 0.0001) between the three parameters.
Fig. 6. Scatter plot of relationship between CRF and CCT.
S. Shah et al. / Contact Lens & Anterior Eye 29 (2006) 257–262260
Fig. 7. Bland and Altman graph.
Fig. 7 is a Bland and Altman plot which demonstrates that
hysteresis and CRF are not measures of the same parameter.
The data was analysed separately for two eyes (right and
left eyes) and difference was not found to be statistically
significant (paired t-test).
5. Discussion
The corneal stroma constitutes 90% of the corneal
thickness and is a highly specialised tissue which is
responsible for its mechanical and refractive properties [17].
The specific architecture of the most anterior part of the
corneal stroma (100–120 mm) has been suggested to be
responsible for the stability of the corneal shape [18]. The
exact mechanism which maintains the corneal contour itself
is not known, but may be due to the passive distension of
corneal tissues by the IOP. It is the distensibility of the eye
that is maintained due to the corneal mass, the elastic
properties of corneal tissue and the mechanical force acting
on this tissue [1]. However, rigidity or elasticity per se of
corneas are known to vary greatly between individuals [14],
and these parameters have only recently been widely
accepted as important when measuring IOP.
Several studies in the past have been conducted to
investigate the elasticity of the human cornea. Elasticity of a
given tissue can be described as a relationship between stress
and strain [19]. Stress can be described as the force per unit
cross-section applied on a given tissue material. Strain
measures the stretch of a material and can be calculated as a
change in length of the tissue divided by its original length.
Previous studies have investigated the rigidity (elasticity)
of the cornea by pressure and indenter loading [2] but the
results were not found to be consistent. Edmund [1]
investigated rigidity (elasticity) of the cornea by measuring
the radius of the central corneal curvature, the coefficient of
radius variation, the CCT and the coefficient of thickness
variation. Others tried to describe ocular rigidity (elasticity)
using engineering terms for simplicity [20]. Friedenwald [5],
in 1937, devised a formula for ocular rigidity where KP (an
assumed constant scleral rigidity) = dP/dV (V is intraocular
volume and P is the IOP). Further studies found that K was
not constant; K was found to decrease with IOP in human
eyes [21]. It was therefore clear that this was a very
complicated subject.
Purslow and Karwatowski [20] went on to report on an
analysis of ocular rigidity (elasticity) in basic engineering
terms. They analysed various theories and formulae to
determine the ocular rigidity (elasticity). These formulae
were based on the assumption that the eye is perfectly
elastic, a spherical tissue and had a uniform wall thickness
and that the wall material was isotropic and homogenous.
The authors commented that the assumption of homogenous
mechanical properties between sclera and cornea was
‘inherently less defensible’ and that this was a major
problem with such a simplistic model. They suggested that
the engineering analysis only helps to separate the
mechanical properties of the ocular shell from the
morphological factors. They concluded that the phenom-
enon of ocular rigidity (elasticity) was complex, and even
with very simplifying assumptions, the analysis did not lead
to a simple result.
Brooks et al. [22] investigated ocular rigidity in the eyes
of 85 keratoconic patients and 20 normal subjects. They
calculated the ocular rigidity coefficient from a combination
of applanation tonometry and impression tonometry
(Schiotz) using the Friedenwald nomogram and the line
of best fit. Foster and Yamamoto [23] measured ocular
rigidity of the 80 normal human eyes using the Friedenwald
nomogram and reported the rigidity as 2.40 � 0.37 mm�3.
They were of opinion that the Friedenwald method of
calculating ocular rigidity is not accurate and does not
reflect the true visco-elastic properties of the keratoconic
eyes. Orssengo and Pye [4], more recently, determined the
modulus of corneal rigidity (elasticity) in vivo from the
corneal dimensions and applanation tonometry. Although
all these studies are very interesting and have tried to
establish ocular rigidity by different methods but they all
involve complicated mathematical calculations [1,19,22,23]
and are impractical for clinicians. They also report varying
results.
The ORA is a new device developed by Reichert which is
a non-contact tonometer that measures IOP as well as new
metrics; hysteresis and CRF. The ORA is an attempt to make
the measurement of rigidity and elasticity easily accessible
to clinicians for all patients.
Measuring corneal biomechanical properties by the
applanation of a force to the cornea requires a procedure
capable of separating the contributions of the corneal
resistance and the IOP because the corneal resistance and
true IOP are basically independent. The ORA releases a
precisely metered air pulse which causes the cornea to move
inwards. Thus the cornea passes through applanation
(inward applanation), and then to the past applanation phase
S. Shah et al. / Contact Lens & Anterior Eye 29 (2006) 257–262 261
where its shape becomes slightly concave. Milliseconds
after applanation, the air puff shuts off, resulting in a
pressure decrease in a symmetrical fashion. During this
phase, the cornea tries to regain its normal shape and the
cornea again passes through an applanation phase (outward
applanation). Theoretically, these two pressures should be
the same but this is not the case. This is described as the
dynamic corneal response which is said to be the resistance
to applanation manifested by the corneal tissue due to its
visco-elastic properties. The difference between the outward
and inward pressures is termed hysteresis and is measured in
mmHg. Hysteresis is said to be a measurement of viscous
properties whereas the CRF is dominated by elastic
properties of cornea and is an overall indicator of the
corneal resistance.
The cornea reacts to stress as a visco-elastic material, i.e.
for a given stress, the resultant corneal strain is time
dependent. The visco-elastic response consists of an
immediate deformation followed by a rather slow deforma-
tion [19]. The immediate elastic response of the ocular
tunics seems to reflect the immediate elastic properties of the
collagen fibres; the steady state elastic response reflects the
properties of the corneal matrix [19]. The two applanation
pressure readings – ‘inward’ and ‘outward applanation’ – are
perhaps the result of immediate elastic response and delayed
or steady state elastic response, respectively, of the corneal
tissue.
Luce [16] reported the first ever measure of corneal
hysteresis on the ORA. He reported corneal hysteresis in
normal, keratoconus, Fuchs’ dystrophy, and post-LASIK
patients from pooled data from a large number of users and
machines. He reported that hysteresis varied over a dynamic
range of 1.8–14.6 mmHg.
The results of this study on normal eyes performed on a
single instrument also demonstrated a wide range of
individual variation in hysteresis (6.1–17.6 mmHg). The
histogram (Fig. 2) shows the distribution of hysteresis and
CRF. The data was further analysed to assess the correlation
between CRF and hysteresis and the graph (Fig. 4) showed
the relationship was significant p < 0.0001 and correlation
coefficient strong (r = 0.8). However, the Bland and Altman
plot (Fig. 7) confirms that hysteresis and CRF are not the
same measured parameters.
A review by Mishima [24] proposed that CCT in man
averages 518 mm but Doughty and Zaman [8] found that in
recent years, higher value of CCT have been reported and
this, they suggest, may be due to the change in environ-
mental factors or other factors such as diet and living style. A
very wide range (450–600 mm) of values for CCT has been
reported for ‘normal’ corneas [8].
The results in this study also showed wide individual
variations of CCT (471–650 mm). The histogram (Fig. 3)
shows the distribution of CCT, the frequency of the CCT was
highest in the range between 521.0 and 540.0 mm. The
scatter plot (Fig. 5) shows the relationship between CCT and
hysteresis. The regression line shows hysteresis increasing
with increasing CCT (the slope was moderate and the
correlation coefficient r = 0.426 is moderate). This study
found a stronger relationship between these two parameters
than reported by Luce [16].
The scatter plot (Fig. 6) shows the relationship between
CCT and CRF. The graph showed CRF increased with
increasing CCT, the correlation was moderate (r = 0.467)
but the relationship was significant ( p < 0.0001). A
regression analysis reveals that the regression equations
for the relationship between CCT and hysteresis; CCT and
CRF were not the same.
In summary, the results of this study showed that
hysteresis and CRF measured by the ORA have a positive
but moderate correlation to CCT; the higher the CCT the
higher the hysteresis (visco-elasticity) and CRF (elasticity).
The results of this study suggest that hysteresis and CRF and
CCT are related but are not measurements of the same
physical/biomechanical parameter.
The ORA may be a measure of the corneal rigidity in
vivo. The measurement of hysteresis and CRF is easy and
can be performed by any trained technician. It may be
helpful in the future for long term monitoring of glaucoma
and other disease processes of the cornea, for eyes where
IOP measurement is important. It may provide additional
factors over and above CCT for cases in which corneal
biomechanics are important and help with the assessment of
the accuracy of IOP (in the manner that CCT has been found
to be in the ocular hypertension study) [25,26]. Further
studies need to be done to establish the relevance and
usefulness of these measures.
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