oulu 2017 d 1432 university of oulu p.o. box 8000 fi-90014...
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UNIVERSITY OF OULU P .O. Box 8000 F I -90014 UNIVERSITY OF OULU FINLAND
A C T A U N I V E R S I T A T I S O U L U E N S I S
University Lecturer Tuomo Glumoff
University Lecturer Santeri Palviainen
Postdoctoral research fellow Sanna Taskila
Professor Olli Vuolteenaho
University Lecturer Veli-Matti Ulvinen
Planning Director Pertti Tikkanen
Professor Jari Juga
University Lecturer Anu Soikkeli
Professor Olli Vuolteenaho
Publications Editor Kirsti Nurkkala
ISBN 978-952-62-1672-0 (Paperback)ISBN 978-952-62-1673-7 (PDF)ISSN 0355-3221 (Print)ISSN 1796-2234 (Online)
U N I V E R S I TAT I S O U L U E N S I S
MEDICA
ACTAD
D 1432
AC
TAK
yösti Vihanninjoki
OULU 2017
D 1432
Kyösti Vihanninjoki
THE HEIDELBERG RETINA TOMOGRAPH IN THE DIAGNOSIS OF GLAUCOMA
UNIVERSITY OF OULU GRADUATE SCHOOL;UNIVERSITY OF OULU,FACULTY OF MEDICINE;OULU UNIVERSITY HOSPITAL
ACTA UNIVERS ITAT I S OULUENS I SD M e d i c a 1 4 3 2
KYÖSTI VIHANNINJOKI
THE HEIDELBERG RETINA TOMOGRAPH IN THE DIAGNOSISOF GLAUCOMA
Academic dissertation to be presented with the assentof the Doctoral Training Committee of Health andBiosciences of the University of Oulu for public defencein Auditorium 5 of Oulu University Hospital, on 13October 2017, at 12 noon
UNIVERSITY OF OULU, OULU 2017
Copyright © 2017Acta Univ. Oul. D 1432, 2017
Supervised byDocent Ville SaarelaProfessor P. Juhani Airaksinen
Reviewed byDocent Mika HarjuDocent Marko Määttä
ISBN 978-952-62-1672-0 (Paperback)ISBN 978-952-62-1673-7 (PDF)
ISSN 0355-3221 (Printed)ISSN 1796-2234 (Online)
Cover DesignRaimo Ahonen
JUVENES PRINTTAMPERE 2017
OpponentProfessor Hannu Uusitalo
Vihanninjoki, Kyösti, The Heidelberg Retina Tomograph in the diagnosis ofglaucoma University of Oulu Graduate School; University of Oulu, Faculty of Medicine; Oulu UniversityHospitalActa Univ. Oul. D 1432, 2017University of Oulu, P.O. Box 8000, FI-90014 University of Oulu, Finland
Abstract
Glaucoma is a group of eye diseases characterized by a chronic, progressive optic neuropathy.During the disease process, the axon damage of the retinal ganglion cells leads to changes in theretinal nerve fiber layer, causing optic nerve head, and visual field defects typical of glaucoma.
The Heidelberg Retina Tomograph (HRT) is a confocal scanning laser imaging deviceacquiring and analysing three-dimensional data of the ocular fundus wit good accuracy andreproducibility..
Conventional planimetric measurements were compared to those taken with the HRT in a pilotstudy of 12 eyes with early glaucomatous optic disc, retinal nerve fiber layer and/or visual fieldabnormalities. The neuroretinal rim area measurements and cup-to-disc area ratio did not differstatistically from each other when using these two different methods.
The effect of four different reference levels on the HRT parameter measurement values wastested in two separate studies. In the first study there were 67 eyes, 40 of the eyes were healthy and27 eyes had glaucoma of different stages. Then, 279 eyes, 180 of which were non-glaucomatousand 99 glaucoma eyes, were included in another study. The flexible reference level gave the mostreliable HRT parameter measurement values in both non-glaucomatous and glaucomatous eyes.
The ability of the HRT parameters to separate between non-glaucomatous and glaucomatouseyes was tested in 77 eyes, 40 of the eyes were non-glaucomatous, 10 ocular hypertensives and 27eyes had different stages of glaucoma. The reference level dependent HRT parameters cup-to-discarea ratio, vertical linear cup-to-disc ratio, mean retinal nerve fiber layer thickness (RNFLt) andrim volume as well as the reference level non-dependent HRT parameter, cup shape measure(CSM), separated best between the clinical groups.
The best combination of the HRT and other structural and functional parameters in separatingbetween non-glaucomatous and glaucomatous eyes was studied in 55 eyes. There were 32 non-glaucomatous eyes and 23 eyes with ocular hypertension or glaucoma. CSM, RNFLt, togetherwith age- and lens coloration-corrected mean deviation of the B/Y perimetry showed gooddiscrimination (ROC area 0.91) between non-glaucomatous and glaucomatous eyes.
Keywords: confocal scanning laser ophthalmoscope, glaucoma, optic nerve head, retinalnerve fiber layer, visual field
Vihanninjoki, Kyösti, The Heidelberg Retina Tomograph glaukooman diagnostiikassaOulun yliopiston tutkijakoulu; Oulun yliopisto, Lääketieteellinen tiedekunta; Oulunyliopistollinen sairaalaActa Univ. Oul. D 1432, 2017Oulun yliopisto, PL 8000, 90014 Oulun yliopisto
Tiivistelmä
Glaukooma koostuu joukosta hitaasti eteneviä näköhermon rappeumasairauksia. Sairausproses-sin aikana verkkokalvon gangliosolujen aksonivaurio johtaa muutoksiin verkkokalvon hermo-säiekerroksessa ja näköhermon päässä aiheuttaen glaukoomalle tyypillisiä näkökenttämuutoksia.
The Heidelberg Retina Tomograph (HRT) on konfokaali laserskanneritekniikkaan perustuvakuvantamislaite, joka tuottaa ja analysoi silmänpohjasta saatua kolmiulotteista mittaustietoa tar-kasti ja toistettavasti.
Tavanomaisen planimetrian antamia mittaustuloksia verrattiin HRT:n antamiin tuloksiin12:ssa silmässä, joissa oli todettu varhaisia glaukoomamuutoksia. Näköhermon pään hermoreu-nan (rim) pinta-ala ja keskuskuopan suhde papillan läpimittaan eivät poikenneet tilastollisestitoisistaan näitä kahta menetelmää käytettäessä.
Neljän eri referenssitason vaikutusta HRT-parametrien mittausarvoihin testattiin kahdessa eritutkimuksessa. Ensimmäisen tutkimusaineisto koostui yhteensä 67:stä silmästä, joista 40 oli ter-veitä ja 27:ssä eriasteisia glaukoomamuutoksia. Toisessa tutkimuksessa oli yhteensä 279 silmää,joista 180 oli terveitä ja 99:llä oli glaukooma. Papillomakulaarisäikeisiin tukeutuva, fleksiibelireferenssitaso antoi luotettavimmat HRT-parametrien mittaustulokset sekä terveissä että glau-koomasilmissä.
HRT-parametrien kykyä erottaa terveet silmät glaukomatoottisista testattiin yhteensä 77:ssäsilmässä, joista 40 oli terveitä, 10 oli korkeapaineisia ilman glaukoomamuutoksia, ja 27:ssä oliglaukoomamuutoksia. Referenssitasosta riippuvaiset HRT-parametrit, keskuskuopan suhdepapillan läpimittaan, vertikaali-lineaarinen keskuskuopan suhde papillan läpimittaan, keskimää-räinen verkkokalvon hermosäiekerroksen paksuus (RNFLt) ja `rim´:in tilavuus samoin kuinreferenssitasosta riippumaton keskuskuopan ´vinous´-mitta (CSM) erottelivat parhaiten nämäkliiniset ryhmät toisistaan.
Terveitä ja glaukoomasilmiä erottelevaa HRT:n ja muiden rakenteellisten ja toiminnallistenparametrien kombinaatiota etsittiin 55:n silmän aineistosta. Silmistä 32 oli terveitä ja 23 korkea-paineisia ja/tai glaukoomavaurioisia. CSM ja RNFLt, yhdessä iän ja mykiövärjäytymisen suh-teen korjatun sinikeltaperimetrian keskipoikkeaman kanssa osoittivat hyvää erottelukykyä (ROCarea 0.91) terveiden ja glaukoomasilmien välillä.
Asiasanat: glaukooma, konfokaali laserskanneri oftalmoskooppi, näköhermon pää,näkökenttä, verkkokalvon hermosäiekerros
To Professor P. Juhani Airaksinen (in mem.)
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Acknowledgements
The studies for this thesis were carried out in the Department of Ophthalmology,
University of Oulu, and in the Department of Ophthalmology, University of
Heidelberg, during the years 1994-2002. The writing process of this doctoral
dissertation was performed under two supervisors.
First of all, I am deeply grateful to my first supervisor, Professor P. Juhani
Airaksinen, M.D., Ph.D. (†), for his enthusiastic and encouraging attitude in glaucoma
research. His wide experience in scientific field and extensive knowledge of glaucoma
was admirable. It has been an unique priviledge to be one of his numerous co-workers
in ophthalmologic research worldwide. He suggested the subject of this study to me
and showed great helpfulness through these studies up until his retirement, and even
after that.
The writing process of this compilation dissertation would not have been
accomplished without my second supervisor, Ville Saarela, M.D., PH.D., who picked
me up to finish this thesis. I will never forget about his absolute will to bring this work
to a conclusion. I wish to express my warmest gratitude to him for his patience and
ability to painstakingly inspire and support me during these years.
I wish to thank Professor Anja Tuulonen, M.D., Ph.D., my teacher and co-writer in
these studies, for her invaluable help and advice in writing scientific papers. Her energy
and exemplary organizational ability have guided me through numerous problem
situations.
I am very grateful to Professor Reinhard O.W. Burk, M.D., Ph.D., my co-writer,
particularly for his help in Study III, for providing knowledge and study material of
critical importance. Co-operation with his research group in the Department of
Ophthalmology, University of Heidelberg, has been essential.
I want to thank Professor Pait Teesalu, M.D., Ph.D., also my co-writer, for fruitful
and pleasant co-operation in preparing these studies. His study period and
accomplishment of academic thesis in our clinic was memorable.
I acknowledge Docent Mika Harju, M.D., Ph.D., and Docent Marko Määttä, M.D.,
Ph.D., for their careful review and advisable criticism of this dissertation manuscript.
I also want to thank Aura Falck, M.D., Ph.D., member of the follow-up group of
this study, for her valuable comments and all the support she has kindly addressed to
me and to my work. She receives all my admiration. Thanks go to Pasi Hägg, M.D.,
Ph.D., another member of the follow-up group, too.
Mr. Esa Läärä, M.Sc., is acknowledged for his special advice on the statistical
analyses as well as Anna Vuolteenaho, M.A., for revising the English of this thesis.
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Mr. Heikki Nieminen (†), talented photographer in our Department of
Ophthalmology in 1980´s and 1990´s, deserves special thanks for his pioneering work
within glaucoma research. Thanks to his photographing skills numerous glaucoma
studies have been carried out.
I am very grateful to all my colleagues and all the staff in the Eye Clinic of the
Oulu University Hospital for their compassion and patience during these years. They
have made an important contribution to enable this work. They deserve everlasting
respect. My special thanks go to Professor Leila Laatikainen, M.D., Ph.D., Eila
Mustonen, M.D., Ph.D., Rauno Miettinen, M.D., Ph.D., Pentti Koskela, M.D., Ph.D.,
Jussi Kärnä, M.D., Ph.D., Kai von Dickhoff, M.D., Ph.D., Hannu Alanko, M.D., Pekka
Virtanen, M.D., Heli Hirvelä, M.D., Ph.D., Seppo Siik, M.D., Ph.D., Jouko Mattila,
M.D., Risto Salmi, M.D., Minna Virtanen, M.D., Juha Välimäki, M.D., Ph.D., Petri
Oksman, M.D., Harri Koskela, M.D., Ulla Lahtela, M.D. Sirje Ess, M.D., Tapani
Palosaari, M.D., Nina Hautala, M.D., Ph.D. and Pauli Hyytinen for all the support and
co-operation.
I acknowledge the personnel of Opti-Aika Järvelä, Kemin Silmälasi Oy, Näkötiimi
Oy and Opti-Silmä Oy for their patience and friendly co-operation when accomplishing
this thesis.
My sincerest thanks go to all my relatives and friends for their support and
encouragement during these years of the study.
I wish to express my deepest gratitude to my parents Paavo (†) and Mailis for their
care and love. They have showed unending sacrifices for all their children.
I want to express my warmest and loving thanks to my excellent sons Pyry and
Vesa, for making my life meaningful and bringing me plenty of happiness. They are the
joy of my life.
Finally, my loving thanks go to my dear companion, Tarja, my ´Honeysuckle´.
With love and unselfish care she has guided me back to real life from the ´Research
Wonderland´. Together with her I want to celebrate as well as to live our everyday life.
This study was financially supported by grants from Orbis Sensorius Oulu, Sigrid
Juselius Foundation, the Eye Foundation, the Eye and Tissue Bank Foundation, the De
Blindas Vänner – Sokeain Ystävät Foundation, Oulun Diakonissalaitos, the
Instrumentarium Science Foundation, Glaukooma Tukisäätiö Lux Foundation, EVO
funding of Oulu University Hospital and MSD (travel grant).
Oulu, at harvest time, 2017 KyöstiVihanninjoki
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Abbreviations
AF autofluorescence
ANOVA analysis of variance
B/Y blue-on-yellow (visual field) CA cup area
CCT central corneal thickness
C/D cup-to-disc ratio
CDR cup-to-disc area ratio
CDRVer vertical linear cup-to-disc ratio
CDVer vertical cup diameter
CSM cup shape measure (Mom3)
CV cup volume (volume below reference plane)
DA disc area
dB decibel
FDT frequency doubling technology
GDx scanning laser polarimetry
GPS glaucoma probability score
HPeak minimum relative z coordinate of corrected contour line
HRT Heidelberg Retina Tomograph
HRTCALC HRT calculation program
HVar height variation along contour line
IOP intraocular pressure
LTI lens transmission index
MD mean deviation
MHC mean height contour
MRA Moorfields regression analysis
Mom3 third moment
OCT optical coherence tomography
OHT ocular hypertension
ONH optic nerve head
POAG primary open angle glaucoma
PSD pattern standard deviation
RA rim area
REFf HRT software 1.11 standard reference level (the flexible
reference level, SRP)
REFd HRT software 1.09 standard reference level
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REFi individually determined reference level
REFm papillo-macular reference level
REFs curved surface reference level
RGC retinal ganglion cells
ROC receiver operator characteristics
RNFL retinal nerve fiber layer
RNFLc retinal nerve fiber layer cross section area
RNFLt mean retinal nerve fiber layer thickness
RV rim volume (volume above reference plane)
SAP standardized automated perimetry
SRP standard reference plane
SWAP short-wavelength automated perimetry
VF visual field
W/W white-on-white (visual field)
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List of original publications
This thesis is based on the following original articles, which are referred to in the
text by their Roman numerals:
I Vihanninjoki K, Tuulonen A, Burk ROW & Airaksinen PJ (1997) Comparison of optic disc measurements by Heidelberg Retina Tomograph and manual planimetric techniques. Acta Ophthalmol Scand 75: 512-515.
II Vihanninjoki K, Burk ROW, Teesalu P, Tuulonen A & Airaksinen PJ (2002) Optic Disc Biomorphometry with the Heidelberg Retina Tomograph at Different Reference Levels. Acta Ophthalmol Scand 80: 47-53.
III Burk ROW, Vihanninjoki K, Bartke T, Tuulonen A, Airaksinen PJ, Völcker H-E & König JM (2000) Development of the Standard Reference Plane for the Heidelberg Retina Tomograph (HRT). Graefe’s Arch Clin Exp Ophthalmol 238: 375-384.
IV Vihanninjoki K, Burk ROW, Teesalu P, Tuulonen A & Airaksinen PJ Identification of Non-glaucomatous and Glaucomatous Optic Discs with the Heidelberg Retina Tomograph. Manuscript.
V Vihanninjoki K, Teesalu P, Burk ROW, Läärä E, Tuulonen A & Airaksinen PJ (2000) Search for an Optimal Combination of Structural and Functional Parameters for the Diagnosis of Glaucoma. Multivariate Analysis of Confocal Scanning Laser Tomograph, Blue-on-yellow Visual Field and Retinal Nerve Fiber Layer Data. Graefe`s Arch Clin Exp Ophthalmol 238: 477-481.
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Contents
Abstract
Tiivistelmä
Acknowledgements 9 Abbreviations 11 List of original publications 13 Contents 15 1 Introduction 17 2 Review of the literature 19
2.1 Development of eye fundus observation and imaging ............................ 19 2.1.1 Ophthalmoscopy and biomicroscopy ........................................... 19 2.1.2 Eye fundus photography and photogrammetry............................. 19 2.1.3 Emerging eye fundus imaging devices in the 1990s ..................... 22 2.1.4 Measuring the optic disc and the RNFL ....................................... 23
2.2 Non-glaucomatous eye ............................................................................ 24 2.2.1 Structure of the non-glaucomatous optic nerve head and
the RNFL ...................................................................................... 24 2.2.2 Visual field in non-glaucomatous eye .......................................... 26
2.3 Glaucomatous eye ................................................................................... 27 2.3.1 Glaucoma...................................................................................... 27 2.3.2 Glaucomatous optic disc changes ................................................. 27 2.3.3 Glaucomatous RNFL changes ...................................................... 29 2.3.4 Glaucomatous visual field defects ................................................ 30
2.4 The confocal scanning laser tomographer ............................................... 32 2.4.1 General aspects of confocal scanning laser technology................ 32 2.4.2 Principles of use and technical characteristics of the HRT ........... 32 2.4.3 Definitions related to measurements with the HRT ...................... 39 2.4.4 Accuracy and reproducibility of the HRT .................................... 42
2.2 Earlier studies with the Heidelberg Retina Tomograph ........................... 43 2.2.1 Accuracy and reproducibility studies ........................................... 43 2.2.2 The HRT in separating healthy and glaucomatous eyes ............... 45
3 Purpose of the study 47 4 Material and methods 49
4.1 Subjects ................................................................................................... 49 4.2 The planimetric techniques ..................................................................... 50 4.3 HRT study protocol ................................................................................. 53
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4.4 Automated perimetry .............................................................................. 60 4.5 Study protocol ......................................................................................... 60 4.6 Statistical methods .................................................................................. 61
5 Results of the study 63 5.1 Comparison of optic nerve head measurements using planimetric
techniques and the HRT (I) ..................................................................... 63 5.2 The influence of different reference levels on the HRT
measurement values (II) .......................................................................... 64 5.3 The development of the contour line based standard reference
plane (III) ................................................................................................ 66 5.4 The ability to separate clinical groups with the HRT (IV) ...................... 67 5.5 Logistic multivariate regression analysis of confocal scanning
laser tomograph, blue-on-yellow visual field and retinal nerve
fiber layer data (V) .................................................................................. 69 6 Discussion 73
6.1 Early glaucomatous optic disc, RNFL and visual field changes ............. 73 6.2 Accuracy, reproducibility and agreement between optic disc and
RNFL observation and evaluation methods ............................................ 74 6.3 The significance of the definition of the HRT reference level ................ 75 6.4 The significance of the HRT global parameters in optic disc
evaluation ................................................................................................ 77 6.5 Sensitivity and specificity of glaucoma imaging methods ...................... 77 6.6 Diagnostic accuracy of the HRT in screening studies ............................. 78 6.7 Clinical implications ............................................................................... 79 6.8 Further developments in the HRT ........................................................... 80
7 Summary and conclusions 83 References 85 Original publications 105
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1 Introduction
The definition of glaucoma refers to a progressive optic neuropathy causing
characteristic structural changes of the optic disc and the retinal nerve fiber layer
(RNFL) resulting in visual field defects, pathognomonic for glaucoma (Airaksinen
& Alanko 1983, Airaksinen et al. 1984, Jonas et al. 1989a, Jonas et al. 1989b,
Tuulonen & Airaksinen 1991, Airaksinen et al. 1992, Varma et al. 1992, Quigley
1999, Terminology and Guidelines of Glaucoma EGS 2014, AAO Glaucoma Panel
2016). Glaucoma is the second most common reason for blindness in the world
(Quigley & Broman 2006) and in Finland it is the second most common cause of
visual impairment in the age group of over 65 years (Finnish Register of Visual
Impairment 2014). Other most common causes for visual impairment worldvide
are age-related macular degeneration, corneal opacities, diabetic retinopathy and
congenital blindness, and in Finland age-related macular degeneration, inherited
retinopathies, diseases of visual pathways and diabetic retinopathy. There were
1271 patients with glaucoma diagnosis in the Finnish Register of Visual
Impairment in 2014. The early detectable glaucomatous optic disc and RNFL
abnormalities often precede the typical glaucomatous visual field defects
(Airaksinen et al. 1985a, Airaksinen et al. 1985b, Quigley et al. 1989, Sommer et al. 1991, Tuulonen & Airaksinen 1991, Quigley et al. 1992). However, any of these
three parameters may present the first clinical sign of glaucoma (Artes & Chauhan
2005, Strouthidis et al. 2006a, Strouthidis et al. 2006b). “Structure-function
dissociation” has been found in large glaucoma studies, too (Miglior et al. 2005b,
Heijl et al. 2009).
In earlier studies, with conventional optic disc and RNFL photography,
changes of the neuroretinal rim area (RA) (Airaksinen et al. 1985b, Airaksinen et al. 1992), the RNFL (Airaksinen & Drance 1985, Airaksinen & Nieminen 1985)
and the peripapillary RNFL contour line (Tuulonen et al. 1996) have been able to
separate between non-glaucomatous and glaucomatous eyes. However, the
qualitative and subjective nature of these assessing methods has shown the need for
more quantitative, accurate and reproducible methods (Lichter 1976, Varma et al. 1992, Caprioli et al. 1996, Coleman et al. 1996, Margo et al. 2002, Parrish et al. 2005). The eye fundus imaging devices emerging in the early 1990s have offered
the possibility to fulfill this deficiency, enabling the three-dimensional
measurements of the ONH.
As in manual planimetric techniques, the inner edge of the scleral ring, the
Elschnig’s ring, has been used as a reference level for manual optic disc
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measurements in conventional optic disc stereophotogrammetry (Elschnig 1907,
Sommer et al. 1979a, Balaszi et al. 1984, Britton et al. 1987, Jonas et al. 1988b,
Jonas et al. 1988c, Jonas et al. 1988d, Gross & Drance 1995). This is because the
scleral ring forms a reference plane, which most probably does not change with
progressive glaucomatous damage (Airaksinen et al. 1992, Jonas et al. 1993). The
preservation of the papillo-macular bundles during the glaucomatous RNFL
atrophy suggests a favorable region for the definition of a stable reference plane for
the HRT measurements (Airaksinen & Drance 1985, Airaksinen & Nieminen 1985).
Confocal scanning laser tomographers, such as the HRT, have been reported as
instruments with accurate and reproducible three-dimensional measurements of the
optic nerve head (ONH) and central retina (Zinser et al. 1989, Burk et al. 1990,
Weinreb & Dreher (1990), Burk et al. 1991, Burk et al. 1992, Burk et al. 1993a,
Burk et al. 1993b, Weinreb 1993a, Chauhan et al. 1994, Rohrschneider et al. 1994,
Chauhan & Macdonald 1995, Chauhan & McCormick 1995, Vihanninjoki et al. 1995, Bartz-Schmidt et al. 1996a). However, depending on the definition of the
reference level, variation in the optic disc values measured with HRT at different
stages of glaucomatous damage has been published (Tuulonen et al. 1994). That is
why a well defined and stable reference level as well as a choice of clinically
meaningful HRT parameters are of utmost importance for the HRT, to become a
clinically useful tool in glaucoma diagnostics and follow-up (Zangwill et al. 1995,
Dichtl et al. 1996, Wollstein et al. 2000, Kesen et al. 2002, Correnti et al. 2003).
Static automated perimetry has been the standard for evaluating visual fields
in the diagnosis and follow-up of glaucoma (Enger & Sommer 1987, Heijl et al. 1987, Heijl et al. 1989, Drance 1991, Anderson et al. 2001, Viswanathan et al. 2003). However, it has been proposed that short-wavelength automated perimetry
(SWAP) may reveal visual field defects earlier (Johnson et al. 1993b, Sample et al. 1993b) and larger in extent than W/W perimetry (Sample et al. 1986, Sample &
Weinreb 1990, Sample & Weinreb 1992, Wild 2001). The predictability of
glaucoma with B/Y perimetry has been poor, however (van der Schoot et al. 2010).
Frequency-doubling technology (FDT) discriminates glaucomatous and non-
glaucomatous eyes with high sensitivity and specificity, too (Johnson & Samuels
1997, Burnstein et al. 2000).
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2 Review of the literature
2.1 Development of eye fundus observation and imaging
2.1.1 Ophthalmoscopy and biomicroscopy
In 1851, Hermann von Helmholtz presented the first usable direct ophthalmoscope,
Augenspiegel, in his monograph on ophthalmoscopy (von Helmholtz 1851).
Jacobson was the first to report of glaucomatous optic disc cup in 1853 (Duke-
Elder 1958), whereas von Graefe and Jaeger mistakenly described ONH swelling
in glaucoma (von Graefe 1855, Jaeger 1858). Direct ophthalmoscopy has been used
in glaucoma diagnostics, both in optic disc and RNFL assessment. Later, binocular
ophthalmoscopy allowed stereopsis and green light ophthalmoscopy improved the
RNFL evaluation (Vogt 1930). In 1916, Zeiss developed the slit-lamp
biomicroscope, an important invention in ophthalmology (Koeppe 1918). It was
perfected with a contact lens by Goldmann in 1938 and with a non-contact lens by
Hruby in 1942 (Goldmann 1938, Hruby 1942). Regardless of various classification
systems for glaucomatous changes, all these techniques are subjective methods
with high interobserver variation and without documentation of the findings.
2.1.2 Eye fundus photography and photogrammetry
In 1886, Jackman and Webster published the first photographs of a living human
eye fundus (Jackman & Webster 1886), and the first accurate, high-quality eye
fundus photographs were introduced in 1907 by Dimmer (Dimmer 1907). In 1929
Bedell published the first stereo atlas of fundus photographs (Bedell 1929).
Difficulty in obtaining high-quality images and magnification errors in the
measurements of eye fundus structures limited the clinical use of fundus
photography. Several attempts to resolve these photogrammetry problems were
introduced, first in model eyes. Johnson et al. noted that the poor reproducibility of
the cup volume (CV) measurements was partially a result of the difficulty in
specifying the top of the optic cup, because the topography of the rim varies
considerably about its circumference (Johnson 1994). A chart with concentric
circles for optic disc comparison was presented in 1960 by Colenbrander
(Colenbrander 1976) and in 1964 by Snydacker (Snydacker 1964). In 1967, Armaly
introduced the definition of cup-disc ratio in normal and glaucomatous eyes, a
20
method shown to be inaccurate (Leydhecker et al. 1979) with high interindividual
variation (Lichter 1976). Other two- or three-dimensional optic disc and RNFL
evaluation methods included flicker comparison method (Bengtsson & Krakau
1979), stereochronoscopy (Goldmann & Lotmar 1977), computerized image
processing methods (Nakatani & Suzuki 1981, Miszalok & Wollensack 1982),
photographic subtraction (Deininger 1970, Horiuchi 1971, Alanko et al. 1980,
Jaanio et al. 1980) and video-ophthalmograph in optic disc topographic
measurements (Mikelberg et al. 1984).
In their studies, Schwartz and Takamoto produced relative or absolute depth
and volume measurements of the optic cup, with an accuracy of 23 µm for depth
and 4 µm for horizontal and vertical measures (Schwartz & Takamoto 1978). They
calculated CVs based on the top surface of the ONH along the disc margin instead
of the cup margin, defining the space below this surface as the CV. Takamoto and
Schwartz also found that the shape of the volume profile curves is different in
normal eyes compared to glaucomatous eyes (Takamoto & Schwartz 1979). Cup
shape was quantified by calculating volume profile, which is a cross-sectional or
contour area extending from the top to the bottom of the optic disc. In 1970, Holm
and Krakau measured CVs by projecting illuminated multiple slits on the ONH
(Holm et al. 1972, Jönsas 1972).
Later, the development of eye fundus photography techniques made it possible
to achieve more accurate, reproducible and objective documentation of the optic
disc and the RNFL. The permanent recording of findings is of the utmost
importance in the follow-up of glaucoma progression. Stereophotogrammetrical
methods in medicine were introduced by Björn et al. (Björn et al. 1954). In 1964,
Donaldson presented simultaneous stereophotographs, showing better
reproducibility of cup depth measurements compared to the sequential techniques
used by Allen (Donaldson 1950, Allen 1964, Rosenthal et al. 1977). In 1969,
different stereoscopic photographic techniques were introduced: Crock and Parel
(stereoangiography), Forsius and Jönsas (Oulu project), Mikuni et al. (stereoscopic
contouring) and Tomlinson and Phillips (a prism stereoscope) (Jönsas 1972).
Portney measured the optic discs of normal and ocular hypertensive eyes by
stereophotogrammetry using sequential stereophotographs taken with the Zeiss
fundus stereocamera with the Allen stereoscopic separator and concluded that CV
asymmetry greater than 0.20 mm3 was a sign of glaucoma (Portney 1974). Using a
stereophotogrammetric technique, Carassa and associates quantitatively evaluated
and compared optic disc asymmetries between the two eyes of normal subjects and
between those of ocular hypertensive subjects. They found a significant asymmetry
21
in the normal and ocular hypertensive groups for cup area (CA) and CV (inferior
quadrant) (Carassa et al. 1995) Tomita et al. used stereophotogrammetry to
compute cup parameters in normal and open-angle glaucomatous eyes. There was
a significant difference in the parameters between normal and glaucomatous eyes
(Tomita et al. 1994). The techniques of optic disc stereophotographs and RNFL
photography were presented by Airaksinen and Nieminen (Airaksinen & Nieminen
1985). Flicker comparisons of serial disc photographs in the diagnosis of early
glaucoma were studied by Heijl & Bengtsson (Heijl & Bengtsson 1989).
In 1917, Vogt described the evaluation of the RNFL in red-free light. Green
light ophthalmoscopy made the nerve fiber bundles more visible (Vogt 1930). In
1965, Behrend and Wilson introduced monochromatic light into ophthalmic
photography: interference filters and black-and-white film made the RNFL visible
in greenblue/blue light at the wavelength of 549-477 nm (Behrend & Wilson 1965).
Blue light was reflected from the RNFL layer of the retina, discriminating normal
and degenerated areas. Monochromatic photography techniques were further
developed by Mizuno et al., Hoyt & Newman, Iwata et al. Delori & Gragoudas,
and Vannas et al. (Mizuno et al. 1968a, Mizuno et al. 1968b, Hoyt and Newman
1972, Iwata et al. 1975a, Iwata et al. 1975b, Delori & Gragoudas 1976, Vannas et al. 1977). The higher resolving power of low-sensitive black-and-white film in
contrast to that of color film was noticed by Durrey (Durrey et al. 1979) and Frisen
(Frisen 1980). A 30-degree angle fundus camera through a green filter and black-
and-white film was used by Airaksinen (Airaksinen et al. 1981a) and by Mustonen
and Nieminen (Mustonen & Nieminen 1982). A new wide-angle fundus camera
was used by Airaksinen (Airaksinen et al. 1982). Airaksinen et al. (Airaksinen et al. 1982) and Peli et al. (Peli et al. 1987) found it easier to detect RNFL defects
with a wide-angle fundus camera, using high-resolution, fine-grain, black-and-
white film with a blue narrow-band interference filter of 465 nm wavelength (a
Wratten #58). In 1983, Sommer et al. improved the RNFL visibility in photographs
by using a 566 nm short-pass cut-off filter (Sommer et al. 1983).
Cup shape can be estimated by calculating volume profile, which is a cross-
sectional or contour area extending from the top to the bottom of the optic disc.
Takamoto and Schwartz found that the shape of the volume profile curves of normal
eyes was different from that of glaucomatous eyes: the glaucomatous eyes had
larger cup areas and deeper cup depths when compared to normal eyes. The volume
profiles of ocular hypertensive eyes in the same study were between those of
normal and glaucomatous eyes (Takamoto & Schwartz 1979).
22
Ophthalmoscopy using a Goldmann contact lens and a slit lamp, with
magnification correcting formulas, was found to be a clinically practicable method
in measuring optic disc dimensions, diameters and areas, compared with planimetry
on photographs (Jonas & Papastathopoulos 1995). The simple ophthalmoscopic
estimation of the ONH and the neuroretinal rim size in glaucomatous patients
compared well with the more laborious planimetric techniques (Littmann 1988).
As planimetry is a two-dimensional method, it involves measuring the area of
a structure, as opposed to depth which is measured in photogrammetry, a three-
dimensional method. Typical planimetric parameters are cup diameter, disc
diameter, cup, disc and neuroretinal RA, thinnest portion of the neuroretinal rim
and cup-to-disc ratio. Planimetric measurement values are given in ‘machine units’,
which makes it difficult to compare the results given by different planimetric
methods (Sommer et al. 1979a, Sommer et al. 1979b, Balaszi et al. 1984, Britton et al. 1987, Jonas et al. 1988a). These methods showed significant interexamination,
intra- and interobserver variation because of interpretation problems in defining the
cup margin (Lichter 1976, Varma et al. 1992, Caprioli et al. 1996, Coleman et al. 1996, Margo et al. 2002, Parrish et al. 2005).
2.1.3 Emerging eye fundus imaging devices in the 1990s
The technical development of optical imaging devices has made it possible to
enhance the clinical examination and the ‘golden standard’ of optic disc and RNFL
photographs. These are subjective and qualitative methods with descriptive
documentation, sensitive to small pupil size and media opacities. In contrast, the
new, real-time, computerized, accurate and reproducible instruments produce
quantitative, three-dimensional information.
In the 1990s, several emerging optical imaging instruments were introduced:
confocal scanning laser ophthalmoscope (the HRT), scanning laser polarimetry (the
GDx) and optical coherence tomography (the OCT). Scanning retinal thickness
analyzer (the RTA) and raster tomography (the Glaucoma-Scope) were also
available. Each of them has different principles of function, with strengths and
limitations (Gundersen et al. 2000, Konno et al. 2001, Zangwill et al. 2001, Asrani et al. 2003).
The Heidelberg Retina Tomograph (HRT) uses a diode laser of 670 nm wavelength
to scan the eye fundus in the x and y directions at multiple focal planes. A three-
dimensional, color-coded topographic image is calculated from a series of optical
image sections. Three topographic images are combined and automatically aligned,
23
giving a single mean topography for detailed analysis (Wollstein et al. 1998, Iester et al. 1999).
The GDx Nerve Fiber Analyzer (GDx) techniques are based on the change in
polarization occurring when light illuminates birefringent tissue, such as the RNFL.
In the GDx a polarization modulated laser beam, 780 nm in wavelength, passes
through the RNFL, which changes the state of polarization (retardation). The
polarizing ability of the cornea and the lens is compensated in either fixed (GDx
FCC), variable corneal compensation (GDx VCC) or enhanced cornea
compensation (GDx ECC) (Weinreb et al. 2002, Greenfield et al. 2003, Brusini et al. 2005,). The change in polarization is measured, and the thicker the birefringent
structure, the greater the retardation of transmitted light.
In the OCT, a low coherence infrared light beam of 840 nm wavelength is used
in interferometry principles: a measurement beam is reflected from intraocular
tissues according to their distance, thickness and reflectivity, and the interference
information with the reference beam is presented in bi-dimensional images after
longitudinal scanning in transverse direction (Huang et al. 1991, Guedes et al. 2003). The modern spectral-domain OCT is faster in image acquisition and has
better resolution and reproducibility compared with the older time-domain OCT
devices (Huang et al. 1991, Chang et al. 2008).
2.1.4 Measuring the optic disc and the RNFL
The classic, ‘golden standard’ methods of the assessment of the ONH and the RNFL
have been ophthalmoscopy and eye fundus photography, stereophotography of
optic discs and RNFL photography. All of these techniques remain subjective in
nature, showing inter-observer and inter-examination variation (Lichter 1976,
Varma et al. 1992, Tuulonen et al. 1996, Azuara-Blanco et al. 2003). Both
planimetry and stereophotogrammetry have problems with reproducibility and
accuracy due to variation in interpretation and with correcting algorithms (Sommer et al. 1979a, Balaszi et al. 1984, Britton et al. 1987, Jonas et al. 1988a, Jonas et al. 1989a).
The technical progress of eye fundus imaging devices in the late 1980s and
during the 1990s made it possible to acquire precise three-dimensional data of the
optic disc in vivo. However, standardization of these emerging methods that would
allow clinically reasonable measurement results has been challenging (Frohn et al. 1990, Zinser et al. 1990, Tuulonen et al. 1994).
24
2.2 Non-glaucomatous eye
2.2.1 Structure of the non-glaucomatous optic nerve head and the RNFL
The optic disc or ONH is formed of the internal surface of the posterior scleral
opening through which the retinal ganglion cell axons leave the eye (Figure 1). The
peripapillary scleral ring of Elschnig forms the wall of the optic disc, separating the
intrapapillary from the parapapillary region. The clinically visible optic disc margin
may be formed of the innermost opening in Bruch´s membrane, Bruch´s membrane
opening (BMO), or of the dense connective tissue of Elschnig, Elschnig´s ring, or
of the combination of both. The clinical appearance depends on the pigmentation
of BMO and on the structure of the border tissue of Elschnig, joining the sclera to
Bruch´s membrane (Jonas et al. 1988d, Strouthidis et al. 2009). The exact borders
of BMO can be verified with the OCT. (Strouthidis et al. 2010).
The optic disc and the surface of the RNFL are visible in the assessment of the
eye fundus (ophthalmoscopy, slit-lamp biomicroscopy, photography) (Snydacker
1964). The prelamina and lamina cribrosa of the optic nerve consists of glial and
connective tissue and are typically injured in glaucoma. The ONH glial astrocytes
translate ONH stress into axon damage (Hernandez 2000). Morphologically the
retina consists of several cell layers. The retinal ganglion cells (RGC) receive the
visual information originating from photoreceptor cells via amacrine and bipolar
cells and transfer it to the optic nerve. The retinal ganglion cell axons form the
RNFL on the retinal surface. The retinal nerve fiber bundles are topographically
regularly arranged: temporally originating arcuate fibers, perifoveally originating
papillo-macular fibers and nasally originating radial fibers (Radius & Anderson
1979a). All of them enter the ONH, where the axons rotate 90 degrees through the
opening of the sclera. The width of the neuroretinal rim and the size of the optic
disc cup are dependent on the size of the optic disc itself and on the number of
nerve fibers passing through the scleral canal. (Radius & Anderson 1979b, Jonas et al. 1988b, Jonas et al. 1988c).
25
Fig. 1. Schematic presentation of the structure of the ONH (A), the RNFL (B) and VF (C)
with glaucomatous defect.
Clinically important optic disc features include optic disc size, optic disc form,
neuroretinal rim size and form, optic cup size and form, cup-to-disc ratio, optic disc
hemorrhages, and parapapillary atrophy (Radius & Andersson 1979b, Jonas et al. 1981, Jonas et al. 1988a). In non-glaucomatic eyes, the ONH neuroretinal rim has
a characteristic shape described by the ISNT rule: the rim is widest at the inferior
disc sector, followed by the superior, nasal, and the temporal region, where the rim
is narrowest (Jonas et al. 1988d).
Jonas et al. measured these optic disc dimensions in 457 normal eyes, using
Littmann’s method for correcting the magnification errors of photographs of the
central eye fundus. They found the following measures: mean optic disc diameter
horizontally 0.91-2.61 mm and vertically 0.96-2.91, mean optic disc surface 0.80-
5.54 mm², optic cup area 0-3.41 mm², mean horizontal cup diameter 0-2.08 mm
and vertical cup diameter 0-2.13 mm, neuroretinal RA (0.80-4.66 mm², the
narrowing of the neuroretinal rim followed the ISNT rule, horizontal cup-to-disc
ratio 0-0.87, vertical cup-to-disc ratio 0-0.85, the horizontal cup-to-disc ratio was
larger in 93.2% of the optic discs compared to the vertical cup-to-disc ratio (Jonas et al. 1988d).
The ONH is the internal surface of the posterior scleral foramen through which
the retinal ganglion cell axons leave the eye. This posterior scleral opening forms
a truncated cone with a narrow neck internally with a diameter of 1.5 to 2.0 mm
and a broad base externally with a diameter of 3.5 mm. The optic disc is divided
26
into the intrapapillary region containing the optic cup and the neuroretinal rim, and
the parapapillary region. The intrapapillary region is separated from the
parapapillary region by the peripapillary scleral ring of Elschnig forming the wall
of the optic disc (Radius & Anderson 1979b).
2.2.2 Visual field in non-glaucomatous eye
The normal VF ranges 90º-100º temporally, 60º nasally, 50º-60º superiorly and 70º-
75º inferiorly when the eye is fixed in a target. This is called the periferic VF. The
VF within 30º from fixation is called the central VF. The blind spot, corresponding
the ONH, locates 13º-18º temporally and 1º inferiorly from fixation. The light
sensitivity of the retina decreases from the fovea towards the periphery (Goldmann
1945).
The visual fields can be examined by conventional kinetic perimetry, such as
Goldmann perimetry, or static profile perimetry, such as Standardized Automated
Perimetry (SAP) or function-specific perimetry, such as short-wavelength
automated perimetry (SWAP) and frequency doubling perimetry (FDT). In
Goldmann perimetry, size III Goldmann stimulus is usually used within the 30º
central visual field. In automated perimetry VF data is summarized in global
summary indices: mean deviation (MD) represents the difference between observed
and expected mean sensitivity, pattern standard deviation (PSD) the standard
deviation of threshold’s distribution, and visual field index VFI expresses the
amount of VF capacity in percentages (Flammer 1986, Heijl et al. 1987, Bengtsson
& Heijl 2008). Variability of the static perimeter threshold is known to increase
with distance from fixation.
In the conventional W/W perimetry the deviation of the threshold values is
corrected for age. In B/Y perimetry, however, the lens-induced absorption of the
blue light may show large variability in subjects of similar age. We have previously
presented a procedure that provides an estimate of the absorption of blue light in
an individual lens by measuring the autofluorescence (AF) of the crystalline lens
(Siik et al. 1991, Siik et al. 1993). We have previously shown that the reference
level for correcting B/Y perimetry results can be determined more precisely using
fluorometry of the lens than with age alone. However, it was evident that the
variability was further decreased when both variables, LTI and age, were used
(Teesalu 1997a).
Static automated perimetry has been the standard for evaluating visual fields
in the diagnosis and follow-up of glaucoma (Enger & Sommer 1987, Heijl et al.
27
1987, Heijl et al. 1989a, Drance 1991, Anderson et al. 2001, Viswanathan et al. 2003). However, it has been proposed that short-wavelength automated perimetry
(SWAP) may reveal visual field defects earlier (Sample et al. 1993b, Johnson et al. 1993a, Johnson et al. 1993b) and larger in extent than W/W perimetry (Sample et al. 1986, Sample & Weinreb 1990, Sample & Weinreb 1992, Wild 2001). Also
frequency-doubling technology (FDT) discriminates glaucomatous and non-
glaucomatous eyes with high sensitivity and specificity (Johnson & Samuels 1997,
Burnstein et al. 2000).
2.3 Glaucomatous eye
2.3.1 Glaucoma
Glaucoma is a group of eye diseases characterized by a chronic, progressive optic
neuropathy. The degeneration of the RNFL and the optic disc results from the axon
damage of the RGC, causing RGC death. The reasons for glaucomatous process
are multifactorial: raised IOP causing mechanical or ischaemic injury, vascular,
systemic hypotension/vasospasm, immunological and inflammatory changes, as
well as blockage of neurotrophins have been presented as an etiology (Lichter &
Henderson 1977, Weinreb & Khaw 2004). This morphological damage may lead
to irreversible visual impairment and blindness if not treated. Based on anatomic
differences of the anterior segment of the eye, primary glaucomas are classified as
open angle glaucoma (OAG) and angle closure glaucoma. The known risk factors
for glaucoma are raised IOP, age, race, family history of glaucoma, exfoliation of
the lens, myopia, thin central cornea thickness (CCT) and type II diabetes (Armaly et al. 1980, Sommer et al. 1991, Mitchell 1996, Quigley et al. 1999, Kass et al. 2002, Burr et al. 2007, European Glaucoma Society 2008).
2.3.2 Glaucomatous optic disc changes
Glaucoma is not a “red disease”: no single test is able to define abnormality.
Glaucoma diagnosis is based on pre-test probability (risk-mapping and clinical
examination) fulfilled by post-test probability (glaucoma test for structure and
function (Garway-Heath & Friedman 2006). The recommendation for glaucoma
tests consists of measurement of IOP, gonioscopy, visual fields and imaging of the
eye fundus structures, photography and/or computerized imaging of the optic disc
28
and the RNFL) (Tuulonen et al. 2015). Glaucomatous findings in any one of the
diagnostic tests, changes of the ONH or the RNFL or defect in the VF may be the
first sign of the glaucomatous process (Artes & Chauhan 2005, Miglior et al. 2005b,
Strouthidis et al. 2006b). Therefore, a normal optic disc appearance and a normal
visual field do not rule out glaucoma (Tuulonen et al. 1993).
Open angle glaucoma is a chronic optic neuropathy that produces characteristic
visual field defects and ONH changes. It is generally thought that changes at the
ONH can be detected before the appearance of the earliest localized visual field
defects plotted with standard perimetry (Figure 2). In addition to the ONH, the
atrophy of ganglion cell axons can also be observed in the RNFL. In fact, a defect
in the RNFL may be the earliest sign of glaucoma, preceding changes in the ONH
configuration and the visual field (Hart et al. 1978, Sommer et al. 1991, Funk et al. 1993, Weinreb et al. 1995).
Some of early glaucomatous optic disc changes, such as the neuroretinal rim
losses, can be found both with conventional stereoscopic ONH photography (Hoyt et al. 1972, Cher & Robinson 1973, Hitchings & Spaeth 1976, Sommer et al. 1977,
Quigley et al. 1980, Airaksinen et al. 1981a, Jonas et al. 1981, Tuulonen &
Airaksinen 1991, Airaksinen et al. 1992, Caprioli 1994, Gordon & Kass 1999,
Leske et al. 1999) and with modern automated eye fundus imaging devices, such
as the HRT, the GDx and the OCT, based on different techniques (Mikelberg et al. 1995, Dichtl et al. 1996, Gundersen et al. 2000, Konno et al. 2001, Zangwill et al. 2001, Asrani et al. 2003, Miglior et al. 2005a). Some of the glaucomatous changes,
like optic disc hemorrhages, positional changes of blood vessel, optic disc pallor
and parapapillary atrophy are only found in ONH photographs (Drance et al. 1977,
Airaksinen et al. 1981a, Caprioli et al. 1989, Jonas et al. 1989d, Teng et al. 2010,
Hollands et al. 2013). Three-dimensional ONH parameters with glaucomatous
changes, such as rim volume (RV), CV, cup shape and RNFL thickness, are only
achieved with modern imaging techniques (Weinreb et al. 1989, Burk et al. 1990,
Burk et al. 1991, Burk et al. 1993a, Burk et al. 1993b). The qualitative nature of
ONH photography, with inter- and intra-observer variability in assessing the ONH
and the RNFL despite a variety of standardizing methods, weakens its diagnostic
and follow-up capability (Tielsch et al. 1988, Varma et al. 1992, Azuara-Blanco et al. 2003, Zeyen et al. 2003, Reus et al. 2010). The accuracy and reproducibility of
the automated imaging methods improves the observer independency in the studies
(Kruse et al. 1989, Dreher et al. 1991, Dreher & Weinreb 1991, Lusky et al. 1993,
Mikelberg et al. 1993, Chauhan et al. 1994, Owen et al. 2006).
29
The glaucomatous changes in the ONH and the RNFL can be verified
morphologically (Radius & Anderson 1979a, Jonas 1988a, Jonas et al. 1991,
Tuulonen et al. 2015). The loss of ganglion cell axons causes a decrease in the
amount of the neural rim structure, and this results in an increase in the optic CV
and changes in the optic cup and neural rim shape. The glaucomatous optic disc
changes reported in a wide variety of studies include: cupping of the optic disc
(Fuchs 1892, Elschnig 1907, Elliot 1922, Pickard 1923, Fingeret et al. 2005),
asymmetry between the patient’s two optic cups (Armaly 1967, Richardson 1968,
Fishman 1970), vertical ovality of the optic cup (Begg et al. 1972, Kirsch &
Andersson 1973, Read & Spaeth 1974), narrowing of the neural rim (Hoskins &
Gelber 1975, Chan et al. 1976), notching of the rim (Kirsch & Anderson 1973,
Spaeth et al. 1976, Hitchings & Spaeth 1976, Quigley 1982), diffuse loss of optic
nerve fibers (Spaeth et al. 1976, Hitchings & Spaeth 1976), pallor of the neural
tissue (Elliot 1922, Schwartz 1973), changes in the cup shape and blood vessel
position (Takamoto & Schwartz 1979, Varma et al. 1987) and optic disc
hemorrhages (Drance & Begg 1970, Airaksinen et al. 1981b, Airaksinen & Heijl
1983). Cup-to-disc ratio measurements from disc photographs were a weak
structural parameter to discriminate between non-glaucomatous and glaucomatous
eyes (Airaksinen et al. 1985b, Caprioli 1992, Bartz-Schmidt et al. 1996b, Feuer et al. 2002).
Airaksinen (Airaksinen et al. 1985b), Caprioli & Miller (Caprioli & Miller
1988) and Jonas et al. (Jonas et al. 1988b) showed in their studies that the neural
RA is diminished in glaucoma progression. Two different kinds of neural rim loss
patterns were found: localized and diffuse, and one or both may be identified in one
glaucomatous eye (Airaksinen et al. 1984, Jonas et al. 1993, Tuulonen 1993). In
early glaucoma, diffuse loss of axons was found to predominate, but a mixed
pattern of diffuse and localized loss was more frequent in the late stages of
glaucoma (Tuulonen & Airaksinen 1991). Airaksinen et al. (Airaksinen et al. 1985b)
found that in glaucoma, the rate of RA loss, over time was significantly more than
the age-related decline in non-glaucomatous eyes.
2.3.3 Glaucomatous RNFL changes
In 1972 Hoyt and Newman were the first to report of RNFL defects in glaucoma
(Hoyt & Newman 1972). Later, Hoyt et al. presented in a detailed report that the
first visible changes were thin slit-like defects in the arcuate area of the RNFL,
progressing further to wedge-shaped localized defects (Hoyt et al. 1973). The
30
RNFL defects seemed to precede the visual field defects by several years (Sommer et al. 1977, Sommer et al. 1979a, Quigley et al. 1982, Sommer et al. 1991). In
glaucoma, optic disc changes often follow the corresponding RNFL changes (Iwata et al. 1981).
The first visible glaucomatous RNFL changes are thin, slit-like defects in the
arcuate area of the RNFL (Hoyt & Newman 1972). Later, these changes progress
to wedge-shaped localized defects. (Hoyt et al. 1973). Optic disc changes have
frequently been found following RNFL defects (Iwata et al. 1982). In several
studies, the RNFL findings preceded the first visual field defects even by several
years (Sommer et al. 1977, Sommer et al. 1979a, Quigley et al. 1982). The RNFL
is best visualized with red-free light, using ophthalmoscope with green light, or
RNFL photography using a wide-angle fundus camera with high-resolution black-
and-white film with a blue narrow-band interference filter (Airaksinen et al. 1982,
Sommer et al. 1983, Peli et al. 1987). In their study on nerve fiber layer and color
fundus photography and on 1,344 eyes with elevated intraocular pressures (IOP),
Sommer et al. found that clinically detectable nerve fiber atrophy precedes the
onset of glaucomatous field loss (Sommer et al. 1991). Examiner experience and
the severity of optic nerve damage influenced the results. This was verified by
Quigley in his study (Quigley et al. 1992). Also relative RNFL height and visual
field mean defect discriminated well between normal and glaucomatous eyes
(Caprioli 1992). Cup-to-disc ratio measurements from disc photographs have been
found to be weak structural parameters to discriminate between non-glaucomatous
and glaucomatous eyes (Airaksinen & Alanko 1983, Caprioli 1992).
Several grading systems have been proposed to quantify the RNFL
abnormalities: a semiquantitative scoring system (Airaksinen et al. 1984), a four-
level grading system with three features: brightness of the reflexes, the RNFL
texture and the obscuring degree of retinal blood vessels by the RNFL (Quigley et al. 1993), and a visually supported grading system (Niessen et al. 1995).
2.3.4 Glaucomatous visual field defects
Landesberg was the first to describe typical glaucomatous arcuate visual field
defects (Landesberg 1869), later verified as “the Bjerrum scotoma”, by Bjerrum
(Bjerrum 1890). Rønne was the first to describe an extension of arcuate nerve fiber
bundle defect, the glaucomatous “nasal step” in the visual field (Rønne 1909). It
was rediscovered later by several investigators (Aulhorn & Harms 1967, Armaly
1971, LeBlanc & Becker 1971). The most common visual field defect in early
31
glaucoma besides the ‘nasal step’ is the isolated paracentral scotoma, reported in
several studies (Aulhorn & Harms 1960, Aulhorn & Harms 1967, Drance et al. 1967, Armaly 1971, Heijl 1976, Motolko et al. 1982 & Heijl 1989). Glaucoma
suspect arcuate scotoma starts from a blind spot and extends as an arch above or
below fixation temporally (Dyster-Aas et al. 1980, Schmied 1980). It finally results
in a central absolute defect (Heijl et al. 1987).
Fig. 2. The temporal relation of progression of the glaucomatous changes in the optic
disc and visual field (Sommer et al. 1991, Quigley et al. 1992).
Manual kinetic perimetry is insufficient in detecting early glaucomatous VF defects
(Aulhorn et al. 1966). The standardized automatic perimetry (SAP) is the standard
visual field test for measuring central visual function in glaucoma (Fankhauser et al. 1972, Heijl & Krakau 1975, Flammer et al. 1983).
Computerized automatic perimeters (Heijl 1977, Bebie & Fankhauser 1980,
Gloor 1980, Heijl & Drance 1980, Greve 1982) and relevant computer programs
(Anton et al. 1997, Flammer et al. 1983) improved the sensitivity and specificity
of visual field defect detection. The Swedish Interactive Testing Algorithm (SITA)
was developed as a test time reducing but accuracy maintaining and clinically
useful perimetric testing strategy by Bengtsson and Heijl (Bengtsson et al. 1997).
Short-wavelength automated, or blue-on-yellow, perimetry (SWAP) is believed to
detect early visual field defects even 3 years prior to white-on-white visual field
loss, because it specifically tests only one cell type, the small bistratified, RGC,
32
responsible for the blue-yellow opponency (Johnson et al. 1989, Hart et al. 1990,
Johnson et al. 1993a, Johnson et al. 1993b, Sample et al. 1993a, Sample et al. 1996,
Teesalu et al. 1998).
2.4 The confocal scanning laser tomographer
2.4.1 General aspects of confocal scanning laser technology
While laser scanning ophthalmoscopes, which were first developed in Boston and
later in Heidelberg, served predominantly the purpose of imaging, laser scanning
tomography provides additionally the feature of 3-D measurements of ocular
structures with good reproducibility. The laser tomographic scanner (LTS) in 1988
was the predecessor of the HRT, providing the three-dimensional structure of the
optic disc, precisely quantified with the technique of laser scanning tomography
(Kruse et al. 1989, Mikelberg et al. 1993, Weinreb et al. 1993, Janknecht & Funk
1994, Rohrschneider et al. 1994, Dannheim et al. 1995).
The main characteristics of the confocal scanning laser tomography technique
are: 1) sequential point-by-point imaging by a scanning laser beam, generally
requiring a computer system to acquire and display the image and 2) high spatial
resolution in three dimensions due to the confocal optical arrangement, introducing
the third dimension as a quantitative parameter, thus enabling formation of two-
dimensional optical section images and complete three-dimensional images and
subsequent three-dimensional measurements.
2.4.2 Principles of use and technical characteristics of the HRT
The HRT is a confocal scanning laser microscope designed for three-dimensional
imaging and three-dimensional measurements of the posterior segment of the
human eye in vivo. The system consists of a laser scanning camera, mounted on a
standard ophthalmic stand with chin rest, an operation panel, and a personal
computer system (The Heidelberg Retina Tomograph Operation Manual 1993).
The principle of function of scanning laser tomography consists of two-
dimensional optical section images of the retina and its structures, image planes
parallel to the retinal surface, and series of such section images showed in Figure
3. These images which make up a three-dimensional image of the structure are
recorded, digitized and displayed on the computer monitor.
33
Fig. 3. The principle of the technique used in confocal scanning laser tomography.
Dilatation of the patient’s pupil is not required for recording of the image data. A
pupil diameter of 1 mm was found to be sufficient to receive useful data. However,
the amount of detected light and, therefore, the signal-to-noise ratio increase with
increasing pupil diameter (Zangwill et al. 1997). The maximum irradiance at the
retina (0.5 mW/cm2) is approximately one hundredth of the irradiance deposit with
the viewing lamp of a fundus camera. The HRT system is a Class I laser product
and does not emit radiation hazardous to the human eye (The Heidelberg Retina
Tomograph Operation Manual 1993).
The three-dimensional image recorded is stored and analyzed using a standard
micro-computer. The topography image of the region examined is calculated and
presented on the computer monitor. The topography is analyzed quantitatively with
regard to the three-dimensional shape of the examined structure. Additionally,
changes in the topography over time can be detected and quantified for follow-up
analysis.
In a confocal imaging system, the illuminating light source, a diode laser beam
at 670 nm wavelength, is focused to a single point of the structure under
examination. The laser beam is deflected periodically in two dimensions by means
of scanning mirrors, so that a two-dimensional field of the object is scanned in a
time sequence. The light which is reflected from each point of the object is
deflected to a detector and registered. The detector is point-like, similarly to the
light source, and positioned optically conjugate to the focal plane (point-like: the
size of the diffraction limited focus spot of the laser beam). Such light which is
34
reflected from object structures at the focal plane is focused to the detector
diaphragm, passes the diaphragm and is registered by the detector. However, light
reflected or scattered from those parts of the object located outside the focal plane
is not focused to the detector diaphragm and can be registered only partially.
Suppression of reflected light increases rapidly with increasing focal distance.
Therefore, confocal imaging produces high optical resolution not only
perpendicular, but also parallel to the optical axis.
In consequence, the confocal image of a three-dimensional object contains only
information from a small domain at the focal plane. It may be considered as an
optical section through the object at the actual location of the focal plane. If a series
of confocal optical section images is recorded sequentially and the location of the
focal plane is changed along the optical axis between the individual image planes,
a volume of the object is scanned and this confocal image series forms a three-
dimensional image of the object that is spatially resolved in three dimensions. This
section-wise recording of three-dimensional images is called confocal scanning
laser tomography.
The z-profile width describes the highest achievable optical resolution parallel
to the optical axis (into the depth) when imaging the fundus with a confocal system.
For topography measurements, however, it is assumed that all reflected light
originates at one spatially curved surface, and the Z location of this surface at each
point in the (x,y) plane has to be determined. This is performed by searching the
maximum locations of the z-profiles measured at each point (x,y). The accuracy of
that measurement of the Z location depends on the width of the z-profile, on the
number of confocal section images recorded, and on the signal-to-noise ratio in the
image data. The Z location measurement accuracy achievable at the fundus is
typically some tens of microns. When the maximum positions of the z-profiles are
determined at each location in the (x,y) plane, the result is a matrix of numbers
Z(x,y). Each number Z represents the measured position along the optical axis or
height of the surface of the structure examined at the corresponding location (x,y),
as shown in Figure 4.
35
Fig. 4. The maximum positions of z-profiles at each location in the (x,y) plane are
determined.
This matrix of height measurement results in a topographic map of the examined
structure. It can be visualized on a computer monitor as an image Z (x,y) simply by
using each number of the matrix as a picture element (pixel), and by translating the
numerical value into a specific color. This visualized matrix of height measurement
results is called a topography image. The topography image is the basis for the
analysis and quantification of the spatial shape properties of the structure examined.
This includes planimetric and stereometric measurements and analysis of
topographic changes.
From the tomographical image series two images are calculated: the extended
focus image (summation image, the reflectivity image) and the topographic image.
The extended focus image is calculated as a sum of all individual images of the 32
focal planes, resulting in an image with an increased depth of focus which
approximately equals the scan depth along the z-axis. The grey values obtained are
color-coded for better structure differentiation. The topographical image displays
the depth and height information in color coding. Prominent structures are
represented in dark red colors, deeper structures in light yellow to white (The
Heidelberg Retina Tomograph Operation Manual 1993).
Given the optical characteristics of the human eye, the depth resolution is about
300 µm (Campbell et al. 1966). By calculating the center of gravity of the intensity
36
profile of the reflected light in 32 focal planes along the optical axis, a
reproducibility of the depth localization of less than 50 µm is achieved for each
individual pixel of the (x,y) plane (Weinreb & Dreher 1990).
In HRT software release 1.11 the contour line is automatically corrected for
rotation and different magnification between the topography images. The
correction of the rotation leads to a higher reproducibility of the stereometric
measurements, while the magnification correction ensures that the proper scaling
is always used. The quality control for acquired image series in release 1.11 also
requests a change of the focal plane setting if the required change is more than ±
0.5 diopters (The Heidelberg Retina Tomograph Operation Manual 1993).
The basic physical principles of confocal laser tomographic scanning are as
follows: The light source used in the HRT is a diode laser operating at 670 nm
wavelength. Single two-dimensional section images are recorded within 0.032
seconds at a repetition rate of 20 Hz and digitized in a frame of 256 x 256 pixels.
The value of each picture element is the measured height of the examined structure
at the corresponding location. Therefore, the topography image contains a total of
65,536 results of individual height measurements. A three-dimensional image of an
object volume is scanned and recorded as a series of 32 section images at 32 equally
spaced focal planes as shown in Figure 5. Total acquisition time for the complete
series is 1.6 seconds. The location of the three-dimensional scanning field along
the optical axis is adjusted by moving the focal plane of the living image. The total
depth extension of the image series into depth (the distance between the first and
the 32nd section image) can be adjusted between 0.5 mm and 4.0 mm in increments
of 0.5 mm; the spacing between each two subsequent images of a series can
therefore be changed between approximately 16 microns and 130 microns. For
recording an image series used for three-dimensional image formation, the operator
defines the focal planes between which the tomography is to be carried out. In the
case of an optic disk recording, the first focal plane is defined directly above the
first reflections of the retinal vessels. The last focal plane is selected in the region
at the bottom of the excavation, below the position of the maximum reflectivity of
the excavation (The Heidelberg Retina Tomograph Operation Manual 1993, The
Heidelberg Retina Tomograph Operation Manual 1994). The printouts of the non-
glaucomatous and glaucomatous ONH acquired with the HRT are shown in Figure
6. and Figure 7.
37
Fig. 5. The summary image of the HRT confocal scanning laser tomograph.
The acquired three-dimensional image data (256 x 256 x 32 = 2,097,152 three-
dimensionally defined pixels, voxels, per image) are stored automatically in an
image database, together with all relevant patient data and image acquisition
parameters. The value of each picture element represents an independent
measurement of height at the corresponding location. The height measurements are
calibrated by using the properties of the individual eye examined. The mean
standard deviation of the height measurement at each pixel is approximately 30
microns. This accuracy may be further increased by averaging of either arrays of
pixels within the same topography image or by averaging multiple topography
images received from multiple examinations.
38
Fig. 6. The printout of the ONH acquired with the HRT confocal scanning laser
tomograph (non-glaucomatous eye).
Fig. 7. The printout of the ONH acquired with the HRT confocal scanning laser
tomograph (glaucomatous eye).
39
2.4.3 Definitions related to measurements with the HRT
The contour line is defined as the outer limit of the optic disc. It is interactively
determined by the operator. For this, a contour line is created on the monitor
display using a trackball. The contour line is displayed simultaneously on the
extended focus and topographic image. The outer limit of the optic disk is the inner
edge of the Elschnig’s scleral ring (Jonas et al. 1988a). In case of doubt, the
topographical image on which the contour line is created simultaneously may be
taken for orientation purposes. In particular, the scleral ring of Elschnig is often
more distinctly recognizable in topographical images. Depending on the size of the
optic disk, the contour line consists of approximately 300 to 400 pixels. The
topography of the contour line is influenced by crossing blood vessels. Automatic
interpolation at the vascular crossing locations results in the topography of the
corrected contour line.
Topography and reflectivity image are shown in Figure 10. The determination
of a topography image is a two-step process. The originally acquired three-
dimensional image series, the 32 images of the series, are aligned to each other to
correct the shifts between the individual section images due to eye movements
during the acquisition time. Additionally, geometrical corrections are applied to the
images. The result of this first step is the processed image series, also referred to as
the aligned image series. In the second processing step, the topography of the
surface of the examined structure is determined from the processed image series.
The result of the second step is the topography image, which contains the
information on the three-dimensional shape of the structure examined and is used
for subsequent three-dimensional analysis. Along with the topography image, the
reflectivity image is always determined, which is the sum of the 32 two-
dimensional section images acquired. Its value at each picture element is the
maximal reflectivity of the examined structure at the corresponding location. The
topography image is a color-coded image in which the color codes height. The
reflectivity image is also a color-coded image, but in this case the color codes the
reflectivity at each point.
Mean topography images are typically determined from two or more individual
topography images received from multiple examinations of an eye during the same
day. They are useful for two reasons: to increase the accuracy of the height
measurements and to obtain an individual reproducibility measure. If n source
images are used to determine the mean topography, theoretically the accuracy of
the mean height at each location is a factor of √n better than the accuracy of the
40
individual height measurements. In practice, this is true for n≤3 and the increase in
accuracy is generally small for n>3 (Weinreb et al. 1993). Therefore, it is most
efficient to perform three examinations and determine the mean topography image
(The Heidelberg Retina Tomograph Operating Manual 1993, Chauhan et al. 1994).
During determination of the mean topography image out of a set of source
topography images, first the source images are aligned to each other with regard to
horizontal shift, vertical shift, rotation, tilt, and height offset, in order to normalize
the images and to compensate for different recording conditions. After the
alignment, at each location within the topography images (each picture element)
the mean and the standard deviation of the individual height measurements are
determined, resulting in two new images, the mean topography image and the
standard deviation image. The standard deviation image contains the
reproducibility of the height measurements at each location within the mean
topography image. It is an individual and spatially resolved reproducibility measure
for this set of examinations.
All stereometric measurements are done within a region of interest which is
enclosed by the contour line, i.e., the contour line provides the two-dimensional
boundary of the region of interest. To evaluate some stereometric parameters, e.g.
CV of the optic disc, also an upper limitation of the region of interest towards the
vitreous is required. It is derived from the height variation along the contour line.
For that purpose, the measured height along the contour line is first corrected for
artifacts due to crossing blood vessels which cause local elevations. The result is
the corrected contour line.
The curved surface is defined by the following conditions as shown in Figure
8:
1. the curved surface is bounded by the corrected contour line
2. the curved surface has the height of the corrected contour line in each point of
its boundary
3. the height in the center of the curved surface equals the mean height of the
corrected contour line
each section of the curved surface from its center to a boundary point is a
straight line
41
Fig. 8. The scheme of the curved surface used in the HRT images.
The measurement of the topography of an object is basically the measurement of
three spatial coordinates of individual points of this object. Since the spatial
coordinates have dimensions, the proper calibration of the measurement results
plays an important role. The measurement results which make up the topography
images of the HRT are absolutely scaled values. The laser scanning camera of the
HRT normally delivers a parallel laser beam. For absolute scaling, in ametropic
eyes the change of the laser beam divergence is translated into a shift of the focal
plane inside the individual eye examined. This translation depends on the refractive
system of the eye. The refractive system of an individual eye is determined mainly
by the curvature of the anterior surface of its cornea. In addition, a model for the
optical properties of the crystal lens is used. From these data, the focal length of
the eye is determined, which defines the exact translation from the change of the
laser beam divergence to the corresponding absolute shift of the focal plane inside
the eye. This is the absolute scaling of the height measurements. The absolute
scaling in all dimensions ensures that all measured spatial coordinate values are
independent from the refraction of the eye examined.
From the description of absolute scaling it is obvious that a measured change
of the absolute height at a certain location could be caused either by a real height
change of the examined structure at that location, or by a change in the refraction
of the eye (change of the focal length). In order not to depend on an independent,
precise refraction measurement, another approach can be used: If there is any
42
retinal structure with an absolute height location which can be assumed to be
constant over time, this structure can be used to cancel the influence of refraction
variations of the eye. This approach is used when two topography images recorded
at different times are compared to each other with the operation software of the
HRT. The mean height within a reference ring in both topography images is
determined. The outer diameter of the reference ring is 2.7 mm and its width is 0.15
mm. It is then assumed that the mean absolute height within the reference ring has
not changed between the two examinations. In consequence, any measured
difference of the mean height of the reference ring between the two examinations
is assumed to be caused by a change in the focal length (the refraction) of the
examined eye. The corresponding change of the refraction is determined and used
for the absolute scaling of the topography images. This procedure compensates for
any changes in the refraction of the examined eye over time, including those due to
accommodation of the eye during one or both of the examinations.
In the HRT Operation Software releases 1.08, 1.09 and 1.10 the standard
reference is located at the mean height of the peripapillary retinal surface (z= 0 in
the relative coordinate system). By default, a reference plane at a location 320 µm
posteriorly of the mean peripapillary retinal surface height is used. The HRT
operation software offers to use a reference plane either at a standard location
(standard reference) or at a user-defined location.
2.4.4 Accuracy and reproducibility of the HRT
The accuracy and reproducibility of confocal scanning laser tomography have been
determined in several studies by numerous investigators (Burk et al. 1990, Burk et al. 1991, Burk et al. 1992, Weinreb & Dreher 1990). Confocal scanning laser
tomography has been used to produce three-dimensional topographic
measurements of the optic disc structure with high reproducibility (Kruse et al. 1989, Burk 1993a, Burk 1993b, Weinreb et al. 1993b, Janknecht & Funk 1994,
Dannheim et al. 1995). The HRT (Heidelberg Engineering GmbH, Heidelberg,
Germany) has previously been reported as an instrument to obtain accurate and
reproducible measurements of the ONH (Mikelberg et al. 1993, Rohrschneider et al. 1994).
The range of standard deviations was found to be between 28.4 µm and 58.0
µm; the standard deviation over all measurements was 42.6 µm. The relative error
did not exceed 3.1% for the phakic model and was between 0.6 and 8.2% for the
aphakic model (model eye) (Weinreb & Dreher, 1990).
43
There are several factors decreasing the accuracy of laser scanning
tomographic results. Includid are improper eye adjustment, definition of scan
region and scan intensity, focusing, ametropy, height of the head, pupillary distance,
accommodation, transparency of the optical media, pupil width, fixation, palpebral
aperture and restlessness of head position (Owen et al. 2006). In young patients
there was no significant difference (p<0.01) in the measured ONH volume
parameters related to pupil dilation (Zangwill et al. 1997). However, slightly
inaccurate adjustment resulted in a coefficient of variation in volume data of 3.8%,
whereas an increased scanning range by a factor of three compared to the proper
scanning depth led to an increase of volume readings of 16% (Rohrschneider et al. 1990).
2.2 Earlier studies with the Heidelberg Retina Tomograph
2.2.1 Accuracy and reproducibility studies
The confocal scanning laser tomograph has been developed for obtaining accurate
and reproducible three-dimensional topographic measurements of the optic disc
and central eye fundus. The reproducibility of local height measurements in a mean
topography image of three topography images is about 20-30 µm for healthy and
glaucomatous eyes (Kruse et al. 1989, Weinreb et al. 1993, Janknecht et al. 1994,
Dannheim et al. 1995). The coefficients of variation of the stereometric parameters
are approximately 5% (Mikelberg et al. 1993, Rohrschneider et al. 1993,
Rohrschneider et al. 1994, Tomita et al. 1994). The data of reproducibility of local
height measurements and stereometric parameter values as well as of correlation of
the HRT stereometric parameters with visual field indices is presented in Table 1,
Table 2 and Table 3.
44
Table 1. Reproducibility of the HRT local height measurements (individual pixels).
Reference Software
version
Number of eyes SD (µm) of eyes
normal glaucoma normal glaucoma
Bathija et al. (1998) 2.01 49 50 16.8±6.4 20.8±7.5
Caprioli et al. (1998) 2.01 43 53 19 21
Zangwill et al. (1997) 1.1x 8 26
Chauhan et al. (1994) 1.1x 30 30 25.9 31.2
Rohrschneider et al. (1994) 1.0x 13 13 22±6 30±6
Lusky et al. (1993) 1.02 10 10 30.1±7.0 31.8±10.6
SD = standard deviation
Table 2. Reproducibility of the HRT stereometric parameter values.
Parameter SD of normal eyes SD of glaucoma eyes
Rim area (mm²) 0.04 0.06
Cup area (mm²) 0.04 0.06
Cup volume (mm³) 0.01 0.03
Max cup depth (mm) 0.03 0.04
Mean cup depth (mm) 0.01 0.02
Rohrschneider et al. (1994), Tomita et al. (1994)
45
Table 3. Correlation of stereometric parameters with visual field indices.
Reference Number of
subjects
Average MD Parameters Correlation
coefficient HRT Visual field
Brigatti & Caprioli (1995) 46 - 4.8 dB CSM MD -0.65
CSM CPSD 0.55
Eid et al. (1997) 125 -7.5 dB RNFLT MD 0.49
CDAR MD 0.41
Iester et al. (1997a) 294 -4.0 dB RA MD 0.44
RA CPSD -0.48
CSM MD -0.43
CSM CPSD 0.38
Iester et al. (1997b) 105 -3.9 dB infMHC supMD -0.53
infRV supMD 0.47
supCA infMD -0.44
supCSM infMD -0.46
Kono et al. (1997) 21 early supRA infMD 0.65
16 advanced tempRA MD 0.58
Lee et al. (1996) 81 RA MD 0.62
Teesalu et al. (1997c) 77 -3.5 dB CSM MD-B/Y, -W/W -0.65
RNFLT MD-W/W 0.62
Tsai et al. (1995) 34 -3.0 dB RA MD-B/Y 0.56
RA MD-W/W 0.47
supRNFLT MD-W/W 0.67
Caprioli et al. (1998) 53 -4.8 dB mean peri- MD -0.43
papillary
surface slope CPSD 0.43
MD = mean defect, CPSD = pattern standard deviation, W/W = white-on-white, B/Y = blue-on-yellow,
CSM = cup shape measure, RA = rim area, CA = cup area, CDAR = cup/disc area ratio, RV = rim volume,
RNFLT = retinal nerve fiber layer thickness, MHC = mean height contour, inf/sup = inferior/superior, temp
= temporal.
2.2.2 The HRT in separating healthy and glaucomatous eyes
A number of structural characteristics of the ONH and retina as well as
psychophysical functions were established by multiple regression analysis in a
study by Drance et al. (Drance et al. 1987). In another study by Drance et al. (Drance et al. 1991), a stepwise discriminant analysis found that the combination
of the vertical cup-disc-ratio, the diffuse nerve fiber layer score and the localized
nerve fiber layer score could correctly identify 98% of the normal and 84% of the
glaucoma patients.
46
Initial RA, change of RA per year in follow-up and standard deviation of the
mean defect of the initial visual field in the multivariate analysis model could
correctly classify 81% of the patients with 72% sensitivity and 87% specificity in
a study by Airaksinen et al. (Airaksinen et al. 1985a).
The sensitivity and specificity of direct ophthalmoscopic assessment of the
optic disc in screening of glaucoma was studied by Harper and Reeves in their
multivariate analysis (Harper & Reeves 2000). Several different linear regression
formulas were able to discriminate non-glaucomatous and glaucomatous eyes
(Larrosa et al. 2006). The precision of the diagnostic test is improved by using
linear discriminant functions taking into account several HRT stereometric ONH
parameters (Mikelberg et al. 1995, Iester et al. 1997a, Bathija et al. 1998, Mardin et al. 1999, Ferreras et al. 2008). Parameters that were useful in these tests included
CSM, volume above the reference level (RV), height variation along contour line,
mean RNFL thickness, RA and cup area.
47
3 Purpose of the study
The aim of the present study was to develop the HRT as a clinically practical tool
in glaucoma diagnostics: to compare the HRT results with a conventional ONH
assessment, the manual planimetric technique. The purpose was also to find the
most adequate reference level for the HRT parameter measurements, the most
useful HRT parameters and the best combination of all structural and functional
parameters to discriminate between different levels of glaucomatous damage.
In detail, the aim of the study was:
1. to compare the manual optic disc measurements to those taken with the
Heidelberg Retina Tomograph (I)
2. to assess the effect of different reference levels on the HRT topographic optic
disc measurement values (II and III)
3. to search for the best HRT parameters to separate healthy individuals from
patients with glaucoma (IV)
4. to evaluate, which of the selected HRT and other structural and functional
parameters, alone or in combination, separate best between non-glaucomatous
and glaucomatous eyes (V)
48
49
4 Material and methods
4.1 Subjects
For study I, 12 eyes of 12 patients (7 females and 5 males), with early glaucomatous
abnormalities, were selected, their ages ranging from 46 to 73 (mean 62) years. In
five eyes, typical early glaucomatous abnormalities in the optic disc, the RNFL and
the Humphrey 30-2 visual fields (MD < 5dB) were found. In four eyes the untreated
IOP was above 22 mmHg and in eight eyes below it.
Study II included one randomly chosen eye of each of the 67 healthy or
glaucomatous subjects (42 females and 25 males). The controls were 40 non-
glaucomatous subjects with a mean age of 57 (range 29 to 84) years. These subjects
had normal findings in the ocular examination with IOP ≤ 21 mmHg, normal optic
disc, normal RNFL, normal W/W visual field examined with the Humphrey 30-2
program. They had no family history of glaucoma, no ocular or neurologic disease,
no diabetes or other systemic diseases or medications that are known to have an
effect on visual field sensitivity or color vision. The eyes examined were not
excluded on the basis of visual acuity. Twenty-seven eyes of 27 patients with a
mean age of 62 (range 38 to 82) years were examined, in addition to the non-
glaucomatous group. There were 23 open angle glaucoma patients with elevated
IOP, glaucomatous optic disc damage and W/W visual field loss, not influenced by
other ocular or systemic disorders. Four patients had ocular hypertension (OHT)
with elevated IOP (IOP > 22 mmHg on three or more occasions), with normal W/W
visual fields, but abnormal RNFL and/or optic disc. They were added to the early
glaucoma group as “preperimetric” glaucoma patients (Horn et al 1997). The 27
glaucoma cases were divided into two groups for statistical analysis: early to
moderate glaucomas (n=19) and advanced glaucomas (n=8), by the Humphrey (30-
2) W/W visual fields, with MD better/same or worse than 10 dB, respectively.
In study III there were 180 normal eyes and 99 eyes with glaucoma examined
with ten-degree triple images in order to find the reference level for the HRT
measurements, taking into account interindividual variability and ensuring that the
automatic reference level determination for intrapapillary parameters remained
below the disc border height.
In study IV the material consisted of 77 eyes of 77 subjects (51 females and 26
males). There were 40 non-glaucomatous subjects with a mean age of 57 (range 29
to 84) years. The criteria for the normality of the eyes were the same as in study II.
50
In addition to the non-glaucomatous group, 37 ocular hypertensive or
glaucomatous patients with a mean age of 60 (range 30 to 82) years were examined.
There were 10 ocular hypertensives, with elevated IOP (IOP > 22 mmHg on three
or more occasions) with normal optic discs, normal RNFL and normal W/W visual
fields. There were 23 open angle glaucoma patients; the criteria for glaucoma were
the same as in study II. For statistical analysis, the glaucomatous eyes were divided
into three groups: early, moderate and advanced glaucomas, based on the
Humphrey W/W visual fields (program 30-2). In these groups, MD was better than
5 dB (n=9), between 5 and 10 dB (n=6) and worse than 10 dB (n=8), respectively.
Four ocular hypertensive patients with normal W/W visual fields but abnormal
RNFL and/or optic discs were added to the early glaucoma group as ‘preperimetric’
glaucoma patients, as in study II.
Fifty-five subjects (36 females and 19 males) were selected for study V. There
were 32 non-glaucomatous subjects with a mean age of 54 (range 29 to 83) years,
and 23 patients with different stages of glaucoma with a mean age of 59 (range 39
to 82) years. As in studies II and IV, four ocular hypertensive patients were included
in the glaucoma group. The criteria for normal, hypertensive, ‘preperimetric’ and
glaucomatous eyes were the same as in studies II and IV. The number of subjects
in studies I – V, non-glaucomatous and glaucomatous with different stages of
glaucoma, are shown in table 4.
Table 4. The number of non-glaucomatous and glaucomatous subjects, with different
stages of glaucoma, in studies I – V.
Study Number of subjects Non-glaucomatous Glaucomatous
Ocular hypertensive Early Moderate Advanced
I 12 12*
II 67 40 19** 8
III 279 180 99***
IV 77 40 14 9 6 8
V 55 32 23***
*Early, **Ocular hypertensive, Early and Moderate, *** Early, Moderate and Advanced
4.2 The planimetric techniques
Planimetry expresses the areas (x- and y-axes) of a structure, leaving the third
dimension, depth (z-axis), to another technique, photogrammetry. In planimetry,
only one-dimensional and area measurements are provided. However, these may
be related to topography or pallor. Planimetric linear measurements include disc
51
diameter, cup diameter, cup-to-disc ratio, and the thinnest portion of the
neuroretinal rim. Area measurements include area of the cup, disc, and neuroretinal
rim (Airaksinen et al. 1985b, Jonas et al. 1988d).
Planimetry expresses results in ‘machine units’ and ignores any magnification
factors in either the fundus camera or the eye. Algorithms that correct for
magnification in the eye have been developed by Littmann (Littmann 1988). These
convert the machine units of planimetric analysis into absolute units (millimeters
or square millimeters), thus allowing both comparison among individuals and
extrapolation of results from normal distributions. However, there is inter-
individual and inter-examination variation in planimetric studies (Jonas et al. 1988a,
Sommer et al. 1979a, Balaszi et al. 1984). A pair of stereophotographs and a
photograph of the ONH used in the planimetric techniques are shown in Figure 9.
and Figure 10.
The correlation between actual measured dimensions of the scleral canal
relative to the photographic results is an important consideration. Quigley et al. have reported that histologic measurements of the disc, which may be altered by
fixation, range between 1.75 and 1.89 mm in diameter (Quigley et al. 1999). Most
photographic results tend to be lower than the histologic ones; Jonas et al., however,
reported a photographic measurement of 1.92 mm (Jonas et al. 1988d).
52
Fig. 9. A pair of stereophotographs of the ONH used in the planimetric techniques.
53
Fig. 10. A photograph of the ONH used in the planimetric techniques.
Comparison of planimetry with automated devices has demonstrated a high degree
of correlation. Comparing planimetry with photography, Airaksinen et al. showed
the correlation coefficients 0.61 for the neuroretinal RA, 0.77 for the cup area, and
0.76 for the disc area (DA) (Airaksinen et al. 1985b). Mikelberg et al. compared
the results obtained using the Rodenstock ONH analyzer with ones obtained by
planimetry; the correlation coefficients for each of the parameters were as follows:
vertical cup-disc ratio 0.67, horizontal cup-disc ratio 0.63, neuroretinal RA 0.72,
and DA 0.89 (Mikelberg et al. 1986). In a similar study, Varma et al. compared
planimetry with the Rodenstock video-ophthalmograph and the Topcon image
analyzer. The correlation coefficients between planimetry and the others were 0.56
and 0.46 for the DA, 0.78 and 0.79 for the RA, and 0.66 and 0.86 for the ratio of
RA to DA, respectively (Varma et al. 1992).
4.3 HRT study protocol
In this study (studies I and III-V) the HRT, (Heidelberg Engineering, Gmbh,
Heidelberg, Germany) with software versions 1.10 and 1.11 was used to acquire
and evaluate topographic measurements of the optic disc. Dilatation of the pupil
54
was not used for image acquisition (Zangwill et al. 1997). For the optic disc
structure measurements we used the mean image of three scans (Weinreb et al. 1993). In this study we used a 10-degree picture angle and the tilted, relative
coordinate system in all measurements (HRT Operation Software Release 1.08
1993, HRT Operation Software Release 1.11 1994). Optic disc contour line was
manually marked around the disc at the inner edge of the scleral ring (Elschnig’s
ring) by an experienced glaucoma specialist. The HRT global parameters used in
this study are defined in Table 5.
Table 5. The definitions of the HRT global parameters used in this study.
Parameter Abbreviation Definition
The disc area DA The total area of the parts within the contour line.
The cup area CA The total area of those parts within the contour line that are
located below the reference plane.
The rim area RA The difference between disc area and cup area.
The cup/disc area ratio CDR CA/DA, basis reference plane.
The vertical cup diameter CDVer The vertical cup diameter
The vertical linear cup/disc
area ratio
CDRVer The vertical CA/DA
The cup volume CV The total volume of those parts within the contour line that
are located below the reference plane.
The rim volume RV The total volume of those parts within the contour line that
are located above the reference plane.
The mean retinal nerve fiber
thickness
RNFLt Reference height minus the mean height of contour.
The retinal nerve fiber RNFLc The RNFLT times the length of the layer cross-section area
contour line.
The height variation along Hvar The difference between the most elevated and the the
contour line most depressed point of the corrected contour
line.
Cup shape measure CSM Third central moment (skewness) of thefrequency
distribution of depth values relative to the “curved surface”
of the parts located inside the contour line and within the
measured segment. Only structures located below “curved
surface” (positive depth values) contribute.
The parameter CSM describes the overall shape of the ONH. Values are typically
negative in normal eyes (flat cup where small depth values are most frequent) and
positive in glaucomatous eyes (high slopes at the cup boundary, deep cup, high
depth values most frequent).
55
Fig. 11. The HRT software version 1.09 standard reference level (REFd) in non-
glaucomatous and glaucomatous eye.
56
The reference levels used in the present study are defined as follows: The HRT
software version 1.09 standard reference level (REFd) is defined at location 0.320
mm posteriorly of the mean height of the retinal surface (at z= 0.320 mm in the
relative coordinate system) (Figure 11).
Fig. 12. The HRT individual reference level (REFi) in non-glaucomatous and
glaucomatous eye.
The individually determined reference level (REFi) is obtained by the following
method: the x-y cursor in the intensity image, with the best scleral ring (Elschnig’s
ring) appearance out of the 32 intensity images with the tilted and relative
coordinate system, is placed at the Elschnig’s ring. This is just outside the contour
line at the point where the line gives an artifact “notch”. The z coordinate of that
point gives the value of the reference level (Figure 12).
57
Fig. 13. The HRT papillo-macular reference level (REFm) in non-glaucomatous and
glaucomatous eye.
The papillo-macular reference level (REFm) is defined as the level parallel to the
reference ring (corresponding to the retinal surface) at the mean height of the
corrected contour line in the segment between 0 degrees and +1 degrees (Figure
13).
58
Fig. 14. The schema of the REFf reference level used in the HRT images in non-
glaucomatous (left) and in glaucomatous (right) eye.
59
Fig. 15. The HRT software version 1.11 standard reference level (REFf) in non-
glaucomatous and glaucomatous eye.
The HRT software version 1.11 standard reference level (REFf) is the level parallel
to the reference ring and located 50 µm posteriorly of the mean contour line height
in the segment between -10 and - 4 degrees (Figure 15).
60
4.4 Automated perimetry
Humphrey Field Analyzer (Model 610; Humphrey Instruments, San Leandro, CA)
was used to obtain both W/W and B/Y visual fields on a modified 30-2 program.
Details of the B/Y test procedure have been provided in several previous
publications (Hart et al. 1990, Sample et al. 1993b). B/Y perimetry was performed
with a 100 cd/m2 yellow background and a size V blue (440 nm) stimulus.
W/W visual field MD was obtained using the statistical package provided by
Humphrey Instruments. The calculation of B/Y visual field MD was based on
the results of non-glaucomatous subjects enrolled in this study. The 24-2 test data
was used to obtain precise model of the normal B/Y visual field. In non-
glaucomatous subjects, the W/W perimetry was carried out during the first visit. To
achieve data for program 24-2 test, we subtracted respective peripheral location
values from program 30-2 data.
4.5 Study protocol
The clinical protocol was the same for each subject included in this study: best
corrected visual acuity, slit lamp biomicroscopic examination, determination of the
refractive error and keratometric values, stereophotographs of the ONH, RNFL
photographs and ONH planimetry, as well as Humphrey 30-2 visual field
examination (Humphrey Field Analyzer, Model 610, Humphrey Instruments, San
Leandro, CA, USA). The AF of the lens was measured using our fluorometer. A
lens transmission index (LTI) was calculated from the ratio between the heights of
the posterior and anterior AF peaks.
By using red-free or green light it is possible to discriminate normal and
degenerated RNFL areas, because greenblue light is reflected from the RNFL layer
in the retina (Behrendt & Wilson 1965). A wide-angle fundus camera with a blue
narrow-band interference filter and high-resolution black-and-white film has been
used to acquire RNFL photographs (Airaksinen & Nieminen 1985). The semi
quantitative scoring method with the total localized score, the total diffuse score
and the total overall score were calculated (Airaksinen et al. 1984). The HRT
images were taken through undilated pupils.
The present study followed the tenets of the Declaration of Helsinki. An
informed consent was obtained from all subjects prior to their inclusion in the study.
This study was approved by the Ethical Committee of the Medical Faculty of the
University of Oulu.
61
4.6 Statistical methods
The HRTCALC Utility Version 1.05 (Heidelberg Engineering GmbH, Heidelberg,
Germany) was used to collect and calculate the HRT parameter values from the
mean image topographic measurements. HRTCALC is a DOS program that scans
the HRT database and automatically determines the stereometric parameters for the
topography images or mean images present. HRTCALC creates an ASCII data file
containing the results of the parameter determination. The data was analyzed as an
ASCII data file in the SPSS 6.1.3S for Windows (SPSS Inc., Chicago, Illinois,
USA).
The statistical analyses used in these studies are as follows. In study I,
Wilcoxon Signed-Rank test was used to test the means of the parameters, the level
of statistical significance was set at p� 0.05. In study II and study IV, one-way
ANOVA with Duncan’s multiple range test was used in the statistical analysis
between the HRT parameter values. The HRTCALC Utility Version 1.05 was used
to collect and calculate the HRT parameter values from the mean topography
images. In study III, two-sided t-test for unequal variances and two-sided
asymptotic U-test of Mann-Whitney-Wilcoxon was used to analyze the contour-
line segment height readings. Means of regression analysis was used to analyze the
relation between the average SD of the mean topography image and the variability
of the contour-line segment height. Spearman rank correlation coefficients were
determined to compare the height variability of the contour-line segment (-10º to -
4º) and the mean topography image SD, both in non-glaucomatous and
glaucomatous eyes. In study V, stepwise logistic regression analysis was used, with
the default criteria of the program for selecting covariates (P� 0.050 for entry and
P� 0.1 for removal) at each step. The area under the receiver operating
characteristics (ROC) curve was the summary measure of the discrimination power.
62
63
5 Results of the study
5.1 Comparison of optic nerve head measurements using planimetric techniques and the HRT (I)
No statistically significant differences were found between the mean neuroretinal
RA and cup-to-disc area ratio (CDR) with these two techniques. However, the mean
optic disc area measured larger values with manual (planimetric) techniques than
with the HRT (a statistically significant difference). The results of study I are
presented in detail in Table 6. In this study the appearance of the neuroretinal RA
as defined by HRT corresponded well to the clinical definitions as shown in Figure
16.
Table 6. Optic disc parameters measured with manual planimetric techniques and with
the Heidelberg Retina Tomograph (HRT) (mean ± SD).
Parameter Manual HRT P-value
Optic disc area (mm²): Mean±SD 2.10±0.56 1.97±0.57 <0.05
Range 1.23-3.07 0.99-3.05
Neuroretinal rim area (mm²): Mean±SD 1.43±0.46 1.33±0.41 NS*
Range 0.98-2.63 0.88-2.23
Cup/Disc area ratio: Mean±SD 0.31±0.14 0.31±0.13 NS*
Range 0.01-0.51 0.11-0.61
*NS = not significant
64
Fig. 16. The appearance of the ONH rim area as defined by the HRT (left) and by ONH
photograph (right).
5.2 The influence of different reference levels on the HRT measurement values (II)
The results of study II show the RNFL thickness values with the reference level
REFi and REFm to be statistically significantly smaller than with reference levels
REFd and REFf in the normals and in the early-to-moderate glaucoma groups. The
results of study II are presented in detail in Table 7. The RNFL thickness measured
with REFi level was statistically significantly smaller than that measured with the
REFm level, too (Figure 17 a and b). The same finding was observed with the RA
values, but the differences were not statistically significant, except between rim RA
values measured with reference levels REFi and REFf in the normals (Figure 17 d
and e).
In advanced glaucoma, RNFL thickness values with the reference level REFd were
statistically significantly larger compared to measurements with all other reference
levels. With the REFi level the HRT gave the smallest RNFL thickness values
(Figure 17 c). Similar findings could be seen with RA values, but the difference
was statistically significant only between reference levels REFd and REFi (Figure
17 f). Again, for RV measurements, we noticed the same kind of differences in all
clinical groups as were seen for RNFL thickness and RA values, but here the
differences of measurement values with the tested reference levels were not as
65
frequently statistically significant as with the RNFL thickness values (Figure 17 g,
h and i).
Fig. 17. Boxplot presentation of the RNFLt, RA and RV in non-glaucomatous eyes (A, D
and G) and in eyes with early and moderate (B, E and H) or advanced glaucoma (C,F
and I) using the reference levels REFd, REFi, REFm and REFf (median with 10th, 25th,
75th and 90th percentile). For abbreviations see Table 3 and Table 5.
66
Table 7. Mean ± standard deviation of three HRT reference level dependent optic disc
parameters (RNFL thickness, rim area and rim volume) with four different reference
levels (REFd1 , REFi2 , REFm3 and REFf4).
Parameter/
reference levels
Normals
n=40
Early and moderate
glaucomas
n=19
Advanced
glaucomas
n=8
RNFL thickness (RNFLt) (mm)
REFd 0.25 ± 0.05 0.18 ± 0.05 0.17 ± 0.06
REFi 0.18 ± 0.06 0.10 ± 0.06 0.01 ± 0.06
REFm 0.21 ± 0.07 0.14 ± 0.06 0.04 ± 0.07
REFf 0.26 ± 0.07 0.18 ± 0.0 0.08 ± 0.06
ANOVA REFi < REFd,
REFm, REFf
REFi < REFd,
REFm, REFf
REFd < REFi,
REFm, REFf
REFm < REFd, REFf REFm < REFd, REFf REFi < REFf
Rim area (RA) (mm²)
REFd 1.43 ± 0.35 1.17 ± 0.43 0.83 ± 0.30
REFi 1.29 ± 0.31 0.91 ± 0.34 0.42 ± 0.28
REFm 1.37 ± 0.32 1.04 ± 0.38 0.52 ± 0.33
REFf 1.47 ± 0.33 1.18 ± 0.40 0.65 ± 0.29
ANOVA REFi < REFf NS REFi < REFd
Rim volume (RV) (mm3)
REFd 0.38 ± 0.13 0.24 ± 0.13 0.15 ± 0.08
REFi 0.28 ± 0.11 0.15 ± 0.10 0.05 ± 0.05
REFm 0.33 ± 0.13 0.19 ± 0.12 0.06 ± 0.07
REFf 0.40 ± 0.14 0.25 ± 0.14 0.08 ± 0.06
ANOVA REFi < REFd REFi < REFd, REFf REFi, REFm, REFf <
REFd REFi, REFm < REFf
ANOVA: p < 0.05 1 REFd = HRT software version 1.09 standard reference level 2 REFi = individual reference level 3 REFm = papillo-macular reference level 4 REFf = HRT software version 1.11 standard reference level
5.3 The development of the contour line based standard reference
plane (III)
The results in study III show that the average optic disc surface inclination angle
was -7° ± 3° below the horizontal meridian (0°). The 6° wide contour-line segment
for the “flexible” standard reference plane (SRP) was chosen according to the
67
average surface inclination angle (-10° to -4°). The reproducibility of the SRP-
segment height measurements was 16.0 ± 10.8 µm for normal eyes and 23.4 ± 18.0
µm for glaucoma eyes.
To assure that the automatic reference level determination for intrapapillary
parameters remains below the disc border height, the SRP level was defined at an
50 µm offset (> 2 SD of average segment height reproducibility in glaucoma) added
to the individual height position of the 6° contour line segment.
5.4 The ability to separate clinical groups with the HRT (IV)
In study IV we used independent sample t-test to separate between normal and
glaucomatous groups (i.e., groups 1, normals, and 3 – 5, early, moderate and
advanced, combined) in the preliminary observation of the HRT parameter values
(Table 7.). More detailed analysis with one-way ANOVA and Duncan’s multiple
range test was performed with variables showing a statistically highly significant
difference between normals and glaucomas.
For further analysis the following reference level independent HRT parameters
were selected: cup shape measure (CSM) and the height variation along contour
line (Hvar). The following reference level dependent variables were also included:
cup area (CA), rim area (RA), cup/disc ratio (CDR), vertical cup diameter (CDVer),
vertical linear cup/disc ratio (CDRVer), mean RNFL thickness (RNFLt), RNFL
cross section area (RNFLc), cup volume (CV) and rim volume (RV). The group
means and standard deviations of these selected HRT parameters and their
respective clinical groups are presented in Table 8. According to the presented HRT
measurement values the ANOVA showed that there was a statistically highly
significant difference among the clinical groups for all selected HRT variables.
Finally, we performed a more detailed analysis of the clinical group differences
with Duncan’s multiple range test. The HRT parameters CSM, CDR and CDRVer
gave the best overall separation: the advanced glaucoma group was statistically
significantly different from all the other clinical groups. The early and moderate
glaucoma groups showed statistically significant differences from the normals and
the ocular hypertensives, but not from other glaucomas. Based on the measurement
values of the variables RNFLt and RV, the normals were different from all the three
glaucoma groups, the ocular hypertensives from moderate and advanced glaucoma,
and advanced glaucoma from all other clinical groups. The measurement values of
the most useful HRT parameters (CSM, CDR, CDRVer, RNFLt and RV) in the
clinical groups are presented in box plot form in Figure 18.
68
In our study population, the glaucomatous eyes (clinical groups 3-5 combined)
showed larger size of the optic disc (2.05 ± 0.40 mm²) compared to that of the
normal controls (1.86 ± 0.42 mm²).
Table 8. Mean ± standard deviation (SD) of the HRT parameters in the clinical groups.
Parameter Normals
n=40
Ocular
hypertensives
n=10
Early
glaucomas
n=13
Moderate
glaucomas
n=6
Advanced
glaucomas
n=8
Reference level non-dependent
parameters:
Cup shape measure (CSM) -0,22 ± 0.07 -0.20 ± 0.05 -0.11 ± 0.06 -0.10 ± 0.08 0.01 ± 0.06*
Height variation along
contour line (mm) (HVar)
0.41 ± 0.08 0.42 ± 0.12 0.35 ± 0.08 0.31 ± 0.13 0.24 ± 0.09**
Reference level dependent
parameters: thickness
describing parameters
Mean retinal nerve fiber
layer thickness (mm)
(RNFLt)
0.26 ± 0.07 0.25 ± 0.08 0.20 ± 0.04 0.16 ± 0.08 0.08 ± 0.06*
Retinal nerve fiber layer
cross section area (mm²)
(RNFLc)
1.25 ± 0.30 1.21 ± 0.44 1.02 ± 0.26 0.80 ± 0.38 0.37 ± 0.27*
Area describing parameters:
Cup area(mm²) (CA) 0.39 ± 0.31 0.56 ± 0.40 0.95 ± 0.32 1.02 ± 0.59 1.19 ± 0.34*
Rim area (mm²) (RA) 1.47 ± 0.33 1.38 ± 0.33 1.18 ± 0.42 1.17 ± 0.40 0.65 ± 0.29*
Cup/disc area ratio (CDR) 0.19 ± 0.14 0.28 ± 0.17 0.45 ± 0.12 0.45 ± 0.23 0.65 ± 0.14*
Vertical linear cup/disc area
ratio (CDRVer)
0.31 ± 0.22 0.40 ± 0.19 0.64 ± 0.11 0.63 ± 0.26 0.85 ± 0.09*
Vertical cup diameter (mm)
(CDVer)
0.50 ± 0.36 0.65 ± 0.34 1.08 ± 0.19 1.08 ± 0.47 1.30 ± 0.21*
Volume describing parameters
Cup volume (mm³) (CV) 0.09 ± 0.11 0.14 ± 0.14 0.29 ± 0.20 0.24 ± 0.16 0.31 ± 0.15*
Rim volume (mm³) (RV) 0.40 ± 0.14 0.37 ± 0.14 0.25 ± 0.14 0.23 ± 0.14 0.08 ± 0.06*
* p<0.00001, ** p<0.0001
69
Fig. 18. Boxplot presentation of HRT parameters (CSM, CDR, CDRVer, RNFLt and RV)
that provide the best separation between the clinical groups (Nor, OHT, GE, GM, GA)
(median with 10th, 25th, 75th and 90th percentile).
5.5 Logistic multivariate regression analysis of confocal scanning laser tomograph, blue-on-yellow visual field and retinal nerve
fiber layer data (V)
In study V we performed logistic multiple regression analyses to compare the
separating value of selected diagnostic methods and to test the sensitivity and
specificity of the model to correctly identify non-glaucomatous eyes (n = 32) and
glaucomatous eyes (n = 23).
70
First we selected all the global HRT parameters, W/W and B/Y visual fields
(age- and lens-adjusted) with the RNFL total diffuse, total localized and total
overall score values as covariates in the logistic model. The RNFL total overall
score gave the best separation between non-glaucomatous and glaucomatous eyes
(ROC area 0.99) with these parameters in the model.
However, the RNFL scoring is a subjective method in optic disc and RNFL
assessment. That is why we left the RNFL total diffuse, total localized and total
overall score out of the regression model in order to see better the discriminatory
ability of the other parameters. The visual field parameters (W/W and B/Y) were
also left out of the model to avoid their influence on the results. With all the other
parameters in the model, by the first step, CDR was selected (ROC area 0.90 for
CDR only). In the next step, RNFLt was selected, improving discrimination
marginally (ROC area 0.92 for CDR and RNFLt jointly in the model).
Because some of the global HRT parameter values (e.g. CDR, CDVer, CDRVer,
CV) are dependent of the optic disc size, and at the same time in our study
population, the areas of non-glaucomatous discs are somewhat smaller than the
areas of glaucomatous discs, we wanted to remove the effect of different disc sizes.
That is why we performed logistic regression analysis in a subset of data (22 non-
glaucomatous and 22 glaucomatous eyes, the subjects being matched for disc area).
With these data and with the HRT and B/Y visual field parameters in the model, the
stepwise procedure did not choose CDR or other disc size dependent HRT
parameters to the logistic model, i.e., the disc size dependent HRT parameters could
not separate glaucomatous from non-glaucomatous subjects in this restricted subset.
The best discriminating single parameter was RV (ROC area 0.92), and adding B/Y
visual field improved the discrimination (ROC area 0.96) for RV together with B/Y
visual field MD (Figure 21).
Therefore, in the next phase, we performed logistic multiple regression
analysis again in the original study population (32 non-glaucomatous and 23
glaucomatous eyes) with all the other above-mentioned HRT and B/Y visual field
parameters in the regression model, but we excluded all the optic disc size
dependent HRT parameters as well as the RNFL total diffuse, total localized and
total overall score. At the first step, cup shape measure (CSM) was selected (ROC
area 0.88) (Figure 19). At the second step, the mean RNFL thickness (RNFLt) was
added to the model, and the discrimination was somewhat improved (ROC area
0.91) (Figure 20). At the third step, age- and lens-corrected B/Y visual field MD
was added to the model, but it did not improve the result further (ROC area 0.91)
71
(Figure 21). If CSM was dropped, the discrimination provided by RNFLt and age-
and lens-corrected B/Y visual field MD jointly was still high (ROC area 0.93).
Fig. 19. The ROC curve. The area under the curve was 0.88 for CSM.
Fig. 20. The ROC curve. The area under the curve was 0.91 for CSM and RNFLt.
72
Fig. 21. The ROC curve. The area under the curve was 0.91 for CSM, RNFLt and age-
and lens-corrected B/Y visual field MD.
73
6 Discussion
6.1 Early glaucomatous optic disc, RNFL and visual field changes
The diagnosis of glaucoma is quite logical if the following structural and functional
changes characteristic of glaucoma are present: progressive, diffuse and/or
localized, loss of the ONH neuroretinal rim, changes in the RNFL and
corresponding visual field defects. The glaucomatous loss of ganglion cell axons
causes morphologically detectable tissue damage in both ONH and the RNFL.
Depending on the structure examined, different techniques for observation give the
most feasible results. In the present study the difference between moderate and
advanced glaucoma was set at 10 dB MD. Patients with the VF defects only barely
separated by this limit may have very similar glaucomatous damage compared to
patients on the upper and lower regions of the limits.
In this study, the HRT measurements showed clinically meaningful results and
the appearance of the neuroretinal RA assessed with the HRT corresponded well to
the conventional techniques. No statistically significant differences between the
mean neuroretinal RA and cup-to-disc area ratio was found when comparing the
ONH measurements using planimetric techniques and the HRT. However, the mean
optic disc area measurement values were larger with planimetric techniques than
with the HRT (study I). Among the global HRT parameters, the reference level non-
dependent CSM and the reference level dependent CDR, CDRVer, RNFLt and RV
discriminated best between non-glaucomatous and glaucomatous eyes (study IV).
In study IV the glaucomatous eyes showed larger optic discs compared to normal
controls. However, the difference was statistically not significant, possibly due to
the limited sample size of the study. Depending on the study population different
HRT parameter values are accurate to diagnose glaucoma (Mikelberg et al. 1995,
Bathija et al. 1998). Using logistic regression analysis method in order to find the
best combination of parameters discriminating the clinical groups, the RNFL total
overall score separated best between non-glaucomatous and glaucomatous eyes
when all the structural and functional parameters were included in the model. When
subjective assessing methods were left out of the regression model, in the first step
CDR gave a ROC area of 0.90, and in the next step CDR and RNFLt jointly gave
a ROC area of 0.92. Furthermore, the regression model did not choose the optic
disc size dependent HRT parameters in the model. This would suggest that the size
of the optic disc is taken into account when diagnosing glaucomatous damage with
74
the HRT. When tested in a subset of data, subjects were matched for disc area. By
leaving these optic disc size dependent HRT parameters as well as the subjective
RNFL scoring parameters out of the regression model, but using all the other
parameters in the original study population, the stepwise procedure selected the
CSM with ROC area 0.90 in the first step. The RNFLt with a ROC area of 0.94 was
chosen in the second step, and finally, the age- and lens corrected B/Y visual field
MD with ROC area 0.95 in the third step, in the model. This would suggest that the
diagnostics of glaucoma is improved when the optic disc, the RNFL and visual
fields all are included in the diagnostic panel (Tuulonen et al. 2015).
6.2 Accuracy, reproducibility and agreement between optic disc and RNFL observation and evaluation methods
Optic disc photography is a reliable method for documenting glaucomatous optic
disc abnormalities and their progression (Airaksinen et al. 1984, Balazsi et al. 1984). Several planimetric techniques have been used in the evaluation of the ONH
(Littmann 1988, Britton et al. 1987, Jonas et al. 1989a, Sommer et al. 1979a,
Balaszi et al. 1984). These methods have shown interobserver variation caused by
differences in image interpretation and the use of various ‘machine units’ in
measurements, corrected by magnification algorithms. In their study among
European general ophthalmologists Reus et al. (Reus et al. 2010) found accuracy
of 80.5% for detecting glaucoma in stereoscopic ONH photographs. In the same
study, Finnish ophthalmologists showed specificity of 93.2% and sensitivity of 69.3%
for detecting glaucomatous damage.
In earlier studies, the reproducibility of the HRT optic disc topography
measurements has shown standard deviations of pixel height measurements of 20-
30 µm; variability was slightly higher in glaucomatous eyes compared to non-
glaucomatous eyes (Kruse et al. 1989, Weinreb et al. 1993b, Janknecht & Funk
1994, Dannheim et al. 1995). The coefficient of variation of the HRT stereometric
topographic parameters has been reported to be between 2 and 10% (Mikelberg et al. 1993, Rohrschneider et al. 1994, Zangwill et al. 2001). Interobserver agreement
in interpreting HRT printouts in order to separate non-glaucomatous and
glaucomatous eyes has been reported with kappas between 0.67 and 0.73 for
diagnostic agreement (Sanchez-Galeana 2001).
The inter- and intra-operator agreement in the RNFL measurements with the
GDxVCC has shown coefficient of variation between 3.5% and 10% in non-
glaucomatous and glaucomatous eyes (Greenfield 2003, Zangwill 2001).
75
Interobserver agreement in discriminating clinical groups by interpreting the GDx
Nerve Fiber Analyzer printouts has been reported with kappas between 0.55 and
0.66 (Sanchez-Galeana 2001), and kappas of 0.42 and 0.48 for non-glaucomatous
and glaucomatous eyes, respectively. Reproducibility studies of the RNFL
thickness measurements with the OCT have showed coefficients of variation of
approximately 10% (Blumenthal et al. 2000, Carpineto et al. 2003). The
interobserver reproducibility for separating non-glaucomatous and glaucomatous
eyes with the OCT printouts has been reported with kappas between 0.51 and 0.73
(Sanchez-Galeana 2001). Both with GDx and OCT, variability has been found in
the RNFL thickness measurements (Iacono et al. 2006, Vizzeri et al. 2009).
6.3 The significance of the definition of the HRT reference level
The values of the HRT stereometric parameters depend on the definition of
reference plane, the instability of which results in measurement variability (Poli et al. 2008). More than half of the variability of the important HRT parameters RA,
RV, and RNFL could be explained by the variation of the standard reference height
(Breusegem et al. 2008). The interobserver variability is minimized by choosing
the most stable and most easily predictable reference level for HRT measurements,
also in follow-up studies (Tan & Hitchings 2003, Tan et al. 2004, Strouthidis et al. 2005a).
The definition of the reference level is of fundamental importance for ONH
stereoscopic parameter measurements. An ideal reference level in optic disc
assessing should ensure the accuracy and reproducibility of measurements also in
follow-up, taking into account the variation in morphology of individual ONHs.
The reference level should be clinically relevant, easy to apply and it should keep
its stability over time. As the reference level definitions always remain arbitrary,
depending on defining the method and individual anatomy of the ONH, no
reference plane is capable of measuring the stereometric parameters exactly.
The ‘curved surface’ was the first reference plane tested for the quantitative
assessment of the HRT (software version 1.0) stereoscopic parameter values. The
curved surface represents the mean height of the corrected contour line in the center,
connected by straight lines to its boundary points in the corrected contour line.
Unfortunately, it was unable to correctly separate between neuroretinal rim and
optic cup structures (Burk et al. 1990). The HRT (software version 1.08, 1.09 and
1.10) default ‘fixed 320 µm offset’ reference level (Burk et al. 1993a) is
independent of observer and automatically set in the image, but has the
76
disadvantage of measuring clinically inaccurate values in advanced glaucoma eyes.
This reference level was defined 320 µm posteriorly to the reference ring positioned
on the RNFL surface around the ONH. Erroneously high neuroretinal rim values
and optic CV measurements that are too low are obtained because the peripapillary
glaucomatous RNFL damage shifts the reference ring level (Tuulonen et al. 1994).
To avoid this inadequacy, the basis of reference level definition had to be more
individual and stable. In order to achieve these requirements, the inner border of
the scleral ring, the Elschnig’s ring, as well as the papillo-macular region of the
RNFL bundles were chosen as ‘landmarks’ for the more individually determined
reference level (Tuulonen et al. 1994, Vihanninjoki et al. 1994). This choice is
based on the findings of earlier studies showing that the scleral ring remains
constant and that the papillo-macular bundles are best preserved during glaucoma
progression (Airaksinen et al. 1984, Sommer et al. 1977, Sommer et al. 1979a,
Drance et al. 1977, Drance 1978, Drance et al. 1981). However, glaucomatous
changes may also affect the papillo-macular bundles (Chen et al. 2001). Another
arbitrary reference level, the papillo-macular 0-1º reference level, was proposed
based on the same assumptions (Airaksinen 1994a, Airaksinen 1994b, Airaksinen et al. 1995). Applying a wider contour-line segment, still respecting the most stable
region of the disc margin, and taking the interindividual variability of ONH
topography better into account, a flexible reference plane was established as the
SRP for the HRT (software version 1.11). The SRP is located 50 µm posteriorly of
the mean contour line height in the segment between -10 and -4 degrees. Further
studies were needed to show the validity of this reference plane.
An alternative reference plane, assisted with the OCT measurements, was
defined as being located posteriorly from the average height of the disc margin by
the amount of mean RNFL thickness measured with the OCT (Park & Caprioli
2002). This reference plane may be particularly useful in detecting early
glaucomatous changes in eyes with tilted discs, such as in myopic glaucoma.
Another, experimental reference plane, is positioned to ensure that it always lies
entirely below the circumference of the contour line. The distance of the reference
plane is beneath LOW5%, the lowest 5% region of the contour line, where RA
variability is the lowest (Tan & Hitchings 2003). This experimental reference plane
presented good correspondence between the appearance of the neuroretinal rim in
optic disc images and the rim defined by the reference plane (Tan et al. 2004).
The Moorfields reference plane is a combination of the SRP used in the
baseline images and the height difference between the SRP and the reference ring
of the 320 reference plane, which is kept constant (Poli et al. 2008). This reference
77
plane showed significantly lower variability and had better discrimination between
RA change and measurement variability in a longitudinal HRT image series (Poli et al. 2008).
6.4 The significance of the HRT global parameters in optic disc evaluation
The HRT has improved eye fundus assessment by moving from conventional,
subjective ophthalmoscopic and photographic methods to a more objective and
reproducible method. In addition, a more adequate interpretation of the results by
means of normative databases respecting racial variability, Moorfield regression
analysis (MRA) (Wollstein et al. 1998, Reus et al. 2007) and the glaucoma
probability score (GPS) (Swindale et al. 2000, Coops et al. 2006, Taibbi et al. 2009)
is achieved. The ability of the HRT stereometric parameters, both reference level
dependent and non-dependent, to discriminate between non-glaucomatous and
various stages of glaucomatous eyes has been shown in several studies (Brigatti &
Caprioli 1995, Zangwill et al. 1995, Dichtl et al. 1996, Uchida et al. 1996, Iester et al. 1997d, Wollstein et al. 1998). However, measurement accuracy and
reproducibility is imperative in the diagnosis as well as the follow-up of glaucoma.
The HRT techniques have enabled three-dimensional measurements,
determination of the volume of the neuroretinal rim and optic cup, as well as the
assessment of the optic cup shape, the parameter values optic disc which could
previously only be estimated with conventional photographic methods (Zinser et al. 1989, Burk et al. 1990, Burk et al. 1993a).
6.5 Sensitivity and specificity of glaucoma imaging methods
The sensitivity and specificity of direct ophthalmoscopic assessment of the optic
disc in the screening of glaucoma was studied by Harper and Reeves in their
multivariate analysis (Harper & Reeves 2000). The specificity for finding
glaucomatous damage in RNFL photographs has been between 83% and 97%
(Quigley et al. 1980, Airaksinen et al. 1984, Wang et al. 1994).
In their multivariate analysis study on 96 OHT patients with a minimum of 5
years of follow-up Airaksinen et al. found the factors best separating stable OHT
patients from the ones who developed glaucoma to be initial RA, change of the rim
area/year of follow-up and SD of the MD of the initial visual field. This model
correctly classified 81% of the patients with 72% sensitivity and 87% specificity.
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IOP variables, RNFL score and peripapillary atrophy were poor predictors
(Airaksinen et al. 1991).
Using the Rodenstock ONH analyzer, Damms and Dannheim, in terms of
separation characteristics of the different disc parameters, found the maximum and
vertical cup-to-disc ratio (C/D) to have the best diagnostic power (ROC area 0.97
and 0.96 respectively), followed by superior C/D (ROC area 0.92), vertical, total
and temporal RA (ROC area 0.86, 0.79 and 0.70, respectively) and cup CV (ROC
area 0.55) (Damm & Dannheim 1993). In a study with the scanning laser
ophthalmoscope of Rodenstock, Chihara et al. found the optic disc and cup area
smaller when obtained with the SLO than those in conventional photographs, the
coefficient of variation of the optic disc parameters ranging from 4.2% to 9.1%.
The correlation between the optic disc measures studied with the SLO and MD of
the visual field was statistically significant (Chihara et al. 1993).
In glaucoma studies the HRT has shown sensitivities of 63-85%, specificities
of 90% and ROC area of 0.86–0.96 (Bowd et al. 2002, Greaney et al. 2002,
Zangwill et al. 2001).
Glaucoma studies with the GDx have shown sensitivities of 32–89%,
specificities of 86–96% and ROC area of 0.84–0.94 (Bowd et al. 2001, Greaney et al. 2002, Medeiros & Susanna 2003, Yamada et al. 2000, Zangwill et al. 2001).
The ability to detect glaucoma with the OCT has shown specificities of 68–
88%, specificity of 71–96% and ROC area of 0.87–0.94 (Bowd et al. 2001,
Greaney et al. 2002, Guedes et al. 2003, Kanamori et al. 2003, Soliman et al. 2002b,
Zangwill et al. 2001).
6.6 Diagnostic accuracy of the HRT in screening studies
The conventional screening tests for POAG have consisted of ophthalmoscopy,
tonometry and perimetry. However, approximately 50% of persons over 40 years
of age with POAG were not detected with these screening methods in the United
Kingdom (Crick et al. 1994). Several studies have confirmed this problem
(Sommer et al. 1991, Wong et al. 2006).
Burk et al. found the scanning laser ophthalmoscopic measurement values of
the shape of the ONH to be similar to the measurements of computed
stereophotogrammetry (Burk et al. 1993b). In addition, in a study by Cooper et al., measurements of the RNFL produced by scanning laser ophthalmoscopy and red-
free photographs were comparable (Cooper et al. 1992). In several HRT studies
even one HRT parameter has been able to separate between non-glaucomatous and
79
glaucomatous eyes (Burk et al. 1991, Vihanninjoki et al. 1994, Dichtl et al. 1996,
Iester 1997d, Wollstein et al. 1998). However, a combination of HRT parameters
most often gives the best accuracy and reproducibility in diagnosing glaucoma
(Mikelberg et al. 1995, Broadway et al. 1998, Ferreras et al. 2008).
The HRT with MRA has been reported as a good screening method in the
diagnostics of glaucoma, even compared to SAP and frequency doubling perimetry
(Robin et al. 2005).
The effectiveness of the modern eye fundus imaging devices, including the
HRT, as screening methods has been only poorly investigated (Kass et al. 2000,
Polo et al. 2006, Burr et al. 2007, Tuulonen et al. 2015, Burr et al. 2012). The
results in the studies with modern, digitalized ONH assessing methods are quite
variable in diagnosing glaucoma (Caprioli et al. 1996, Polo et al. 2006, Coleman et al. 1996, Hadwin et al. 2013). Evidence-based recommendations in glaucoma
diagnosis and follow-up of progression emphasized the lack of randomized
multicenter studies of glaucoma screening and diagnostics. The high risk of
research bias of the published studies and the variability of the measurement values
in the assessment of eye structures and function, depending on the method, observer,
patient or the degree of disease indicate that there is a need for further evidence
(Tuulonen et al. 2015). Although the new eye fundus imaging devices can minimize
the inter- and intraobserver variability of the results, the interpretation of the digital
printouts and detection of artifacts is still challenging. The conventional
photographs of the ONH and the RNFL remain necessary (Chauhan et al. 2013).
6.7 Clinical implications
The criteria of glaucoma diagnosis have been debated for decades. The consistency
of the definition of glaucoma influences the estimation of the prevalence rates, risk
factors and strategies of treatment. In a literature review of 182 articles from the
American Journal of Ophthalmology, Ophthalmology and Archives of
Ophthalmology for the years 1980, 1985, 1990 and 1995, Bathija et al. found that
36% of the articles used both optic disc and visual field criteria for glaucoma, 13%
used optic disc or visual field criteria, 26% used only visual field criteria, 20% used
only IOP, and 5% used only optic disc criteria. In the 1990s, specific descriptions
of the optic disc (34% of articles) and visual field (34% of articles) were favored
(Bathija et al. 1998). This progress may have depended on the availability of the
glaucoma imaging techniques in the 1990s. Still, according to several public health
80
studies, approximately 50% of the POAG subjects are not detected (Sommer et al. 1991, Klein et al. 1992, Weih et al. 2001, Wong et al. 2004).
In a prospective, longitudinal study, Caprioli et al. (Caprioli et al. 1996)
evaluated change, progressive glaucomatous damage, in the optic nerve and nerve
fiber layer by four techniques: 1. qualitative evaluation of stereoscopic color optic
disk photographs, 2. qualitative evaluation of monochromatic nerve fiber layer
photographs, 3. manual stereoplanimetric measurements of disk RA, and 4.
computerized measurement of peripapillary nerve fiber layer height. Of the patients
followed up for 3.3±1.0 years, 15% progressed by qualitative optic disk evaluation,
7.2% by qualitative nerve fiber layer evaluation, 3.6% by stereoplanimetry, and
13.2% by measurement of nerve fiber layer height. Visual field deterioration was
detected in 5.2% and correlated best with qualitative optic disk and nerve fiber layer
evaluations. Evaluation by stereoplanimetry and nerve fiber layer height
measurement detected change in eyes with primarily diffuse structural damage, a
pattern not well detected by qualitative methods.
Based on the results of this thesis, SRP was developed to improve the
diagnostic accuracy of the HRT. However, the results of the multivariate analysis
show that the diagnosis of glaucoma should not be based on the results of the HRT
alone. Evaluating the structural and functional parameters gives the most reliable
basis for the diagnosis of glaucoma.
The clinical HRT studies have maintained the HRT flexible reference level,
introduced in the software version 1.11, as still appropriate in glaucoma diagnostics.
This applies despite though the increased variability in RA measurement with the
standard reference level compared to the 320 reference plane (Strouthidis et al. 2005a). However, in the follow-up of glaucomatous progression, the Moorfields
regression analysis (MRA), using the standard reference level in the baseline
studies and the 320 reference plane in follow-up, has shown its adaptability (Poli et al. 2008). The Glaucoma Probability Score (GPS), an automated HRT image
analyzing method independent of the contour line and the reference level, has
facilitated the interpretation of the HRT topography images especially in
progression studies (Swindale et al. 2000, Coops et al. 2006, Taibbi et al. 2009).
6.8 Further developments in the HRT
The progress from the HRT I to HRT II and III includes both technical
improvements with automated functions as well as development of the software
from the versions 1.0, 1.09 and 1.11 used in the HRT I. New features such as
81
averaging of the scans, serial scans, fine focus, scan depth, correction of scaling
errors and automated drawing of the contour line minimize the effect of the operator
on the measurement values (Strouthidis & Garway-Heath 2008). These methods
decrease the variability of HRT measurement and improve its repeatability. The
imaging head and light source of the HRT I was changed in the HRT II and III,
making these two later devices compatible with each other. Unlike the HRT III
software, the HRT II software cannot analyze the images acquired with the HRT I.
However, technical differences in image acquisition make the HRT I and HTRT III
image analyses uncomparable per se. Use of larger normative databases,
considering ethnicity, enables clinically reasonable analyses of the images acquired.
The development of image alignment techniques, such as applying a subpixel
method (Burk & Rendon 2001) or face recognition technique (Capel 2004), has
improved image quality and decreased measurement variability, manifesting as
lower topography standard deviation (TSD) (Bergin et al. 2008). The Moorfields
regression analysis (MRA) and Glaucoma Probability Score (GPS) as well as a
number of HRT RA progression strategies represent tools for clinical classification,
especially in the follow-up of glaucoma progression. The combination of HRT and
OCT techniques might provide more accurate parameters for discriminating non-
glaucomatous and glaucomatous eyes in follow-up studies as well.
Despite the development of HRT methodology the reference plane described
in article III still remains the SRP definition for the HRT in the diagnosis of
glaucoma.
82
83
7 Summary and conclusions
The main results and conclusions of this study:
1. In this study population, the measurements of the mean neuroretinal rim area
and cup-to-disc area ratio as defined by the HRT corresponded well to the
clinical definitions in the optic disc photographs.
2. As the HRT standard reference level was defined at a 50 µm offset (� 2 SD of
average segment height reproducibility in glaucoma) added to the individual
height position of the 6º contour line segment (-10º to -4º), the automatic
reference level determination for intrapapillary parameters remains below the
disc border height.
3. The HRT parameters CSM, CDR, CDRVer, RNFLt and RV were most
powerful in separating non-glaucomatous and glaucomatous eyes.
4. Multiple logistic regression analysis of the HRT, B/Y visual field and the RNFL
data gave the best result (ROC area 0.91) when CSM, RNFL thickness and the
age- and lens-corrected B/Y visual field MD were added to the model.
84
85
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Original publications
I Vihanninjoki K, Tuulonen A, Burk ROW & Airaksinen PJ (1997) Comparison of optic disc measurements by Heidelberg Retina Tomograph and manual planimetric techniques. Acta Ophthalmol Scand 75: 512-515.
II Vihanninjoki K, Burk ROW, Teesalu P, Tuulonen A & Airaksinen PJ (2002) Optic Disc Biomorphometry with the Heidelberg Retina Tomograph at Different Reference Levels. Acta Ophthalmol Scand 80: 47-53.
III Burk ROW, Vihanninjoki K, Bartke T, Tuulonen A, Airaksinen PJ, Völcker H-E & König JM (2000) Development of the Standard Reference Plane for the Heidelberg Retina Tomograph (HRT). Graefe’s Arch Clin Exp Ophthalmol 238: 375-384.
IV Vihanninjoki K, Burk ROW, Teesalu P, Tuulonen A & Airaksinen PJ Identification of Non-glaucomatous and Glaucomatous Optic Discs with the Heidelberg Retina Tomograph. Manuscript.
V Vihanninjoki K, Teesalu P, Burk ROW, Läärä E, Tuulonen A & Airaksinen PJ (2000) Search for an Optimal Combination of Structural and Functional Parameters for the Diagnosis of Glaucoma. Multivariate Analysis of Confocal Scanning Laser Tomograph, Blue-on-yellow Visual Field and Retinal Nerve Fiber Layer Data. Graefe`s Arch Clin Exp Ophthalmol 238: 477-481.
Reprinted with permission from John Wiley and Sons Ltd (I, II) and Springer (III,
V).
Original publications are not included in the electronic version of the dissertation.
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THE HEIDELBERG RETINA TOMOGRAPH IN THE DIAGNOSIS OF GLAUCOMA
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