WO2013017337A1 - Dispositif de prise de vues destiné à réaliser des photographies de la rétine de l'œil, procédé de prise de vues et produit programme d'ordinateur - Google Patents

Dispositif de prise de vues destiné à réaliser des photographies de la rétine de l'œil, procédé de prise de vues et produit programme d'ordinateur Download PDF

Info

Publication number
WO2013017337A1
WO2013017337A1 PCT/EP2012/062116 EP2012062116W WO2013017337A1 WO 2013017337 A1 WO2013017337 A1 WO 2013017337A1 EP 2012062116 W EP2012062116 W EP 2012062116W WO 2013017337 A1 WO2013017337 A1 WO 2013017337A1
Authority
WO
WIPO (PCT)
Prior art keywords
radiation
eye
retina
illumination
sensitive sensor
Prior art date
Application number
PCT/EP2012/062116
Other languages
German (de)
English (en)
Inventor
Andreas Dreher
Felix Margadant
Yves Robert
Original Assignee
Ophthametrics Ag
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Ophthametrics Ag filed Critical Ophthametrics Ag
Priority to CH01809/13A priority Critical patent/CH706603B1/de
Priority to DE212012000089U priority patent/DE212012000089U1/de
Publication of WO2013017337A1 publication Critical patent/WO2013017337A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A61B3/1241—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes specially adapted for observation of ocular blood flow, e.g. by fluorescein angiography

Definitions

  • Receiving device for receiving a retina of an eye
  • the invention relates to a recording device, in particular fundus camera for recording a predefinable image area of a retina of an eye, a recording method for receiving a retina of an eye, and a computer program product for controlling a recording device and for performing a recording method by means of a recording device, in particular fundus camera for recording a predefinable image area of a retina of an eye, a recording method for receiving a retina of an eye, and a computer program product for controlling a recording device and for performing a recording method by means of a
  • fundus cameras For the imaging of the fundus (fundus oculi), so-called fundus cameras have long been known in the art
  • the illumination and imaging beam path is usually made coaxial, for example, the circular area of the pupil is divided into an outer annular area for illumination and a circular central area for recording.
  • this coaxial division of the available pupil opening requires that the eye with respect to the optical axis of the
  • Imaging device must be positioned very accurately. This is especially important if the image is to be taken without drug dilatation of the pupil, since then the pupil diameter e.g. less than 4mm. With a small pupil diameter, the
  • Lighting ring should be positioned exactly in the center of the pupil, otherwise only a part of the light will be in the eye and the recording will be faint or even unusable. This lateral offset also allows reflexes from the cornea to enter the camera and outshine the light from the fundus.
  • FIGS. 1 and 2 show a schematic representation of an eye 10 with inner
  • the inner blood vessels 21 in the eye 10 run almost parallel to the surface of the retina 1 1 1.
  • the inner blood vessels 21 are very clearly visible, as shown in FIG. 2, partially covered by the transparent nerve fiber layer 24, which in turn is covered by the inner nerve
  • Boundary membrane (membrana limitans interna "ILM") 23 is limited to the glass body 100.
  • the inner boundary membrane 23 is a few ⁇ m thick basal layer, which is the visible light of microscopically small
  • the inner boundary membrane 23 follows the cylindrical shape of the blood vessels 21 and forms a "back" on which irradiated light 60, as shown in FIG. 2, is reflected back speculatively and as the mid-vessel reflex 25 on most fundus images a well-known from the prior art fundus camera is visible.
  • the known fundus cameras are designed for maximum light output of the light reflected from the retina and therefore use polarizing filters which are arranged so that the specular reflex of the retina is maximally detected and at the same time the internal reflexes of the fundus camera are suppressed.
  • the central specular reflex 25 is disturbing because it outshines the actually measured, the desired information-carrying beam 26 from the interior of the blood vessel 21 and an evaluation, for example according to a Lambert-Behr model, makes impossible.
  • the object of the invention is therefore to provide a recording device, in particular a fundus camera and a measuring method available, in which the problems described above with the over-radiating central reflex are largely avoided. It's also one
  • Object of the invention to provide a computer program product for controlling a recording device and / or for performing a recording method and for the evaluation of measurements according to a recording method of the invention.
  • the invention thus relates to a receiving device, in particular
  • Fundus camera for recording a predefinable image area of a retina of an eye.
  • To form an illumination beam is a
  • Luminous radiation of a first wavelength and a second luminous body provided for a second luminous radiation of a second wavelength wherein the illumination source is configured and arranged such that the retina of the eye can be acted upon by the illumination beam via an object optics in the image area.
  • a sensor device with a first radiation-sensitive sensor and a second radiation-sensitive sensor is further provided.
  • an illumination polarizer in particular a linear illumination polarizer, is arranged between the
  • Illuminating beam as well as a polarizing beam splitter between the object optics and the sensor device provided in a beam path of the reflected return radiation, so that the first radiation-sensitive sensor and the second radiation-sensitive sensor with differently polarized return radiation can be acted upon.
  • the polarizing beam splitter has succeeded convincingly in separating the otherwise overshadowing central reflex from the image of the interior of the blood vessels of the retina, even if both image signals are not guided away from the eye.
  • the essence of the invention is that the two signals are separated via two different, preferably mutually largely orthogonally polarized signals, i. the beam splitter divides the return radiation into two sub-beams polarized perpendicular to one another and leads them to the first one
  • Illumination polarizer also a polarizer for generating circularly polarized luminous radiation, in particular visible light, or else, e.g. a polarizer for generating elliptically polarized
  • Luminescent radiation in particular visible light.
  • the polarizing beam splitter which may be a linearly polarizing beam splitter and / or a circularly polarizing beam splitter and / or also an elliptically polarizing beam splitter.
  • Essential for the invention is that the combination of
  • inventive effect namely the sufficient separation, ie a sufficient separation of the measurement information carrying radiation from the blood vessels and the otherwise all-overshadowing specular backscattered central reflex leads.
  • the first wavelength is particularly different than the second wavelength.
  • the first wavelength can be used to illuminate the Au background, preferably a
  • long-wavelength light preferably a red light is used, since this is more pleasant for patients after prolonged irradiation.
  • a short-wave light is advantageously used in practice, which is then operated pulsed for the actual measurement.
  • Patients is particularly preferably a fixation mark provided and configured such that the image area in the region of a predetermined position, in particular in the region of the optic nerve head on the retina is selectable, to compensate for ametropia of the eye, an assembly along an optical axis of an objective lens is advantageously displaced.
  • the invention relates to a recording method for receiving a prescribable image area of a retina of an eye by means of a recording device of the present invention, wherein a
  • Lighting beam is formed by providing an illumination source with a first luminous body for a first luminous radiation of a first wavelength and a second luminous body for a second luminous radiation of a second wavelength.
  • the illumination source is designed and arranged such that the retina of the eye is exposed to the illumination beam via an object optics in the image area, and a reflected from the image area of the retina back radiation is detected by a sensor device with a first radiation-sensitive Sensor and a second radiation-sensitive sensor is provided.
  • an illumination polarizer preferably a linear illumination polarizer between the illumination source and the
  • Object optics in a beam path of the illumination beam as well as a polarizing beam splitter between the object optics and the
  • the first wavelength is preferably chosen to be different from the second wavelength, wherein the second luminous body is operated advantageously pulsed and in practice usually a
  • Fixation mark is provided and configured such that the
  • the reverberation is particularly preferably divided by the beam splitter into two sub-beams polarized perpendicular to one another, whereby a radiation intensity reflected specularly on the eye can be directed to more than 95%, in particular more than 95%, of the radiation-sensitive sensor.
  • a sum signal are generated, for example, corresponds to a retinal image and / or a measurement signal of the first radiation-sensitive sensor and a measurement signal of the second radiation-sensitive sensor can also be a difference signal which contains largely specular reflections of a surface of the retina.
  • a chemical and / or physical property of the eye, in particular of the retina and / or of the blood in the interior of the blood vessel is often determined with the aid of a Lambert-Beer method.
  • the absorbance ie the absorbance of a material for radiation of wavelength ⁇ when a light beam passes through a cuvette, e.g. through a
  • Ig is the decadic or natural logarithm
  • the intensity of the transmitted light l 0 the intensity of the incident (incident) light
  • c the concentration of the absorbing substance in the liquid
  • ⁇ ⁇ as the decadic extinction coefficient (often also as a spectral
  • Absorption coefficient at the wavelength ⁇ and d is the layer thickness of the irradiated body.
  • the invention relates to a
  • Computer program product for controlling a receiving device and for carrying out a purchase procedure.
  • Fig. 1 schematic representation of an eye with internal blood vessels
  • Fig. 2 blood vessel of the eye gem.
  • 3 shows an embodiment of an inventive arrangement. 4: spatial arrangement of the iris and pupil opening of the iris of the eye;
  • FIG. 5 shows the prior art technique of pupil separation by T. Weitzel et al .
  • FIG. 6 Reduction of the intensity of the corneal reflex according to FIG.
  • Imaging system proposed that largely eliminates the central reflex, so the specular reflex 25.
  • the illumination source 400 of the system comprises a first luminous element 40, which emits a first luminous radiation, preferably light of a first wavelength ⁇ , and a second luminous element 41 of a second
  • Luminous radiation preferably emitted light of a second wavelength ⁇ 2 .
  • the luminous bodies 40, 41 are designed as light-emitting power LEDs LED 40, 41.
  • the LED 40 (e.g., Philips Lumilex LXML-PD01 -0040 or similar) emits, for example, in the red wavelength region with a middle first one
  • Wavelength ⁇ 627 nm and is used to illuminate the
  • the LED 41 (Philips Lumiled LXML-PM01 -0100 or similar) emits preferentially but not necessarily in a different wavelength range, for example in the green wavelength range with a mean second wavelength ⁇ 2 of 530 nm and becomes the measurement recording in the specific embodiment according to FIG. 3 lightning-fast, so pulsed operated.
  • the green light with a wavelength of about 530 nm is particularly preferred because the main absorption line of the hemoglobin is about 530 nm, so that its measurement is of course particularly facilitated.
  • the luminous bodies 40, 41 may, of course, in principle be any suitable luminous bodies. Particularly advantageously, the luminous bodies 40, 41 can also be designed as a laser, for example.
  • the light emitted by the LEDs 40 and 41 light is combined by the dichroic beam splitter 42 into a common beam path and focused by means of lens 43 on the Einlenkapt 45, wherein on the mirror 45 an intermediate image of the two LED filament 40, 41 is formed.
  • the intermediate image of the LED filament 40, 41 is focused by the objective lens 46 by means of the illumination beam 50 on the cornea 13 of the examined eye 10, passes through the pupil 14 and lens 12 of the eye 10 and illuminates the retina 1 1 1 of the eye 10 in the image area. 1 1 .
  • a pinhole 47 thereby limits the illumination beam 50 and thus determines the size of the image area 11. Typically this will be for this application Image area 1 1 on the retina 1 1 1, for example, about 6 mm
  • the location of the image area 11 is selected by the viewing direction of the patient's eye 10.
  • Externally or system internally provided from the prior art known per se fixation marks, for reasons of
  • Clarity in Fig. 3 are not shown, the viewing direction of the eye 10 of the patient in the desired position.
  • an image area 1 1 in the vicinity of the visual nerve head 20 is selected on the retina 1 1 1, from which the larger inner blood vessels 21 go out, so that a sufficiently high evaluable signal intensity is generated.
  • a portion of the backscattered by the retina 1 1 1 light is collected by the eye lens 12 and the cornea 13 and imaged by the objective lens 46 as an intermediate image of the retina 1 1 1 in the plane of the aperture 47.
  • the reticle interchangeable is again through the field lens 49 as
  • the internal assembly 35 of the system may be displaced relative to the objective lens 46 along its optical axis OA.
  • Retina 1 1 1 arises on the radiation-sensitive sensors 31 and 32 always exactly when the pinhole 47 in the plane of
  • Retina sunscreen lies.
  • the sensors may e.g. Digital camera systems known per se, such as e.g. CMOS cameras, CCD cameras, point or line photodetectors or any other suitable light sensitive detector.
  • Digital camera systems known per se, such as e.g. CMOS cameras, CCD cameras, point or line photodetectors or any other suitable light sensitive detector.
  • Illumination polarizer 44 the illumination beam 50 containing the of the two luminous bodies 40, 41 emitted light such that the polarization axis of the illumination beam 50 upon appearance on the
  • the human cornea 13 is a birefringent element, that is to say an optical element which splits a light bundle into two sub-beams polarized perpendicularly to one another, wherein its so-called slow axis averages approximately 5 degrees nasally,
  • the representation of the horizontally polarized light of the illumination beam 50 thus passes the cornea 13 almost parallel to the slow axis and remains largely linearly polarized after penetrating the cornea 13.
  • the linearly polarized light radiates through the eye lens 12 and strikes the retina 1 1 1. There, a first part 25 of the light 60 is speculatively reflected at the boundary membrane 23, and a second part 26 penetrates deeper
  • the specularly reflected light 25 essentially retains its linear polarization with a representation of the horizontal polarization direction, while the scattered light 26 is depolarized more or less.
  • the polarization-maintaining light 25 and the scattered light 26 are reflected back out of the eye 10 and, as previously described, imaged by the lenses 46 and 49 on the photosensitive sensors 31, 32 which are sensitive to light here.
  • a polarizing beam splitter 30 shares the received Reflection 60 in two Pola sationskomponenten, so that the specular reflected light 25 is imaged for example more than 95% on the sensor 32, and the depolarized light 26, for example, about 50% to 50%, ie approximately each half the sensors 31 and 32 are displayed.
  • an image of the retina 1 1 1 is generated on the sensor 31, which is largely free of disturbing central reflexes of the surfaces of the blood vessels 21 and thus can be used in a conventional manner for the analysis of blood levels, for example, but not necessary using a method according to Lambert-Beer.
  • a summation image of the two sensors 31, 32 can be created, which is a conventional one
  • Retinal image corresponds and is a measure of the total re-radiated light intensity. Also by means of known electronics and / or digital
  • Image processing can also be a difference image of the two sensors 31, 32 are created, the main, i. for the most part only speculative
  • Reflections of the surface of the retina 1 1 1 includes.
  • Image information can then be used to analyze materials, agents, contaminants, trace elements, etc. that are located between the retinal surface and the corneal surface, ie, in the vitreous body 100, eye lens 12, anterior and posterior chamber, or cornea 13.
  • FIG. 4 or FIG. 5 which in principle can likewise be used in combination with an arrangement according to the invention, wherein in an arrangement according to the invention However, particularly preferably an arrangement or a method according to FIG. 6 is used, as will be explained below.
  • FIG. 4 shows a possible relative spatial arrangement of the iris 15 of the eye 10, which has a pupil opening 14.
  • the illuminating beam is arranged annularly on the outer edge of the pupil, while the light 61 to be detected leaves the eye 10 in the center of the pupil.
  • FIG. 5 shows that of T. Weitzel et al. proposed method of
  • an illumination beam 52 is imaged as a point on the pupil plane of the eye 10.
  • the eye pupil is optically divided into two crescent-shaped areas, one of which is for the
  • Illumination beam 52 the other for the imaging beam 62 is responsible.
  • the spatially separated entrance and exit pupils are in the
  • Imaged imaging beam where then blocked with a suitable aperture of the corneal reflex.
  • imaged imaging beam where then blocked with a suitable aperture of the corneal reflex.
  • the Einlenktik 45 is mounted in a conjugate image plane to the corneal plane and thus simultaneously acts as a projected aperture 53 for the separation of the illumination beam 52 from
  • Imaging beam 63 the ratio of pupil area for the imaging beam to pupil area for the illumination beam is substantially greater than in the methods shown in FIGS. 4 and 5. This results in a correspondingly greater light output with the same pupil size.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Hematology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Eye Examination Apparatus (AREA)

Abstract

L'invention concerne un dispositif<span lang=FR style='font-family:"Courier New"'> de prise de vues (1), en particulier une caméra pour fond de l'œil (1), destiné à photographier une zone prédéterminable (11) de la rétine (111) de l'œil (10). Afin de former un faisceau d'éclairement (50), une source d'éclairage (400) est dotée d'un premier luminaire (40) destiné à produire un premier rayonnement d'éclairement d'une première longueur d'onde (</span>λ1) et d'un deuxième luminaire (41) destiné à produire un deuxième rayonnement d'éclairement d'une deuxième longueur d'onde (λ2). La source d'éclairage (400) est conçue et disposée de manière la rétine (111) de l'œil (10) puisse être exposée au faisceau d'éclairement (50) dans la zone prédéterminable (11) grâce à une lentille objectif (410). Afin de détecter le rayonnement de retour (60) réfléchi par la zone prédéterminable (11) de la rétine (111), ledit dispositif comprend en outre un dispositif de détection (300) ayant un premier capteur photosensible (31) et un deuxième capteur photosensible (32). Selon la présente invention, il est prévu un polarisateur d'éclairage (44), en particulier un polarisateur d'éclairage linéaire (44), placé entre la source d'éclairage (400) et la lentille objectif (410) dans le trajet des rayons du faisceau d'éclairement (50), ainsi qu'un diviseur de faisceau polarisant (30) entre la lentille objectif (410) et le dispositif de détection (300) dans le trajet du rayonnement de retour (60), si bien que le premier capteur photosensible (31) et le deuxième capteur photosensible (32) reçoivent un rayonnement de retour (60) polarisé différemment. L'invention concerne en outre un procédé de prise de vues pour la prise de photographies de la rétine (111) de l'œil (10) ainsi qu'un produit programme d'ordinateur destiné à commander un dispositif de prise de vues (1) et de mise en œuvre du procédé de prise de vues.
PCT/EP2012/062116 2011-08-03 2012-06-22 Dispositif de prise de vues destiné à réaliser des photographies de la rétine de l'œil, procédé de prise de vues et produit programme d'ordinateur WO2013017337A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
CH01809/13A CH706603B1 (de) 2011-08-03 2012-06-22 Aufnahmevorrichtung zur Aufnahme einer Netzhaut eines Auges sowie Aufnahmeverfahren.
DE212012000089U DE212012000089U1 (de) 2011-08-03 2012-06-22 Aufnahmevorrichtung zur Aufnahme einer Netzhaut eines Auges sowie Computerprogrammprodukt

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201161514864P 2011-08-03 2011-08-03
US61/514,864 2011-08-03

Publications (1)

Publication Number Publication Date
WO2013017337A1 true WO2013017337A1 (fr) 2013-02-07

Family

ID=46397229

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2012/062116 WO2013017337A1 (fr) 2011-08-03 2012-06-22 Dispositif de prise de vues destiné à réaliser des photographies de la rétine de l'œil, procédé de prise de vues et produit programme d'ordinateur

Country Status (3)

Country Link
CH (1) CH706603B1 (fr)
DE (1) DE212012000089U1 (fr)
WO (1) WO2013017337A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018031690A1 (fr) 2016-08-09 2018-02-15 Seattle Genetics, Inc. Conjugués de médicaments avec des lieurs auto-stabilisants, aux propriétés physiochimiques améliorées

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1992019930A1 (fr) * 1991-04-29 1992-11-12 Massachusetts Institute Of Technology Procede et appareil d'imagerie optique et de mesure
EP0608516B1 (fr) 1993-01-28 1998-01-21 Yves Prof. Dr. Robert Ophtalmoscope
WO2007104165A1 (fr) 2006-03-13 2007-09-20 Ophthametrics Ag Dispositif d'enregistrement photographique du fond de l'œil
WO2008037090A1 (fr) * 2006-09-29 2008-04-03 Ottawa Health Research Institute Dispositif et procédé pour mesures optiques séparées d'une lumière spéculaire et d'une lumière diffuse
US20090225277A1 (en) * 2008-03-05 2009-09-10 Tamir Gil Snapshot Spectral Imaging of the Eye
US20100085537A1 (en) * 2008-10-06 2010-04-08 The Catholic University Of America Lenslet array for retinal oximetry
CH699479B1 (de) 2008-08-29 2011-02-15 Ophthametrics Ag Vorrichtung zur Unterstützung der Positionierung des Auges vor einem ophthalmologischen Gerät.

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1992019930A1 (fr) * 1991-04-29 1992-11-12 Massachusetts Institute Of Technology Procede et appareil d'imagerie optique et de mesure
EP0608516B1 (fr) 1993-01-28 1998-01-21 Yves Prof. Dr. Robert Ophtalmoscope
WO2007104165A1 (fr) 2006-03-13 2007-09-20 Ophthametrics Ag Dispositif d'enregistrement photographique du fond de l'œil
WO2008037090A1 (fr) * 2006-09-29 2008-04-03 Ottawa Health Research Institute Dispositif et procédé pour mesures optiques séparées d'une lumière spéculaire et d'une lumière diffuse
US20090225277A1 (en) * 2008-03-05 2009-09-10 Tamir Gil Snapshot Spectral Imaging of the Eye
CH699479B1 (de) 2008-08-29 2011-02-15 Ophthametrics Ag Vorrichtung zur Unterstützung der Positionierung des Auges vor einem ophthalmologischen Gerät.
US20100085537A1 (en) * 2008-10-06 2010-04-08 The Catholic University Of America Lenslet array for retinal oximetry

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
MASAHIRO MIURA ET AL: "Imaging polarimetry and retinal blood vessel quantification at the epiretinal membrane", JOURNAL OF THE OPTICAL SOCIETY OF AMERICA A, vol. 24, no. 5, 1 January 2007 (2007-01-01), pages 1431, XP055039029, ISSN: 1084-7529, DOI: 10.1364/JOSAA.24.001431 *

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018031690A1 (fr) 2016-08-09 2018-02-15 Seattle Genetics, Inc. Conjugués de médicaments avec des lieurs auto-stabilisants, aux propriétés physiochimiques améliorées

Also Published As

Publication number Publication date
CH706603B1 (de) 2016-08-31
DE212012000089U1 (de) 2013-12-12

Similar Documents

Publication Publication Date Title
EP0603658B1 (fr) Méthode pour déterminer in-vivo d&#39;une propriété optique du liquide de l&#39;humeur vitrée de l&#39;oeil
DE60309185T2 (de) Verfahren und anordnung zur durchführung von messungen der topographie einer oberfläche durch thermische emission von einer oberfläche
DE60121123T2 (de) Verfahren und vorrichtung zur messung von refraktiven fehlern eines auges
DE68911975T2 (de) Ophthalmoskopisches Diagnoseverfahren und Gerät.
DE60032528T2 (de) Wellenfrontsensor mit schrägeinfallender Beleuchtung
DE102017115105B4 (de) Optisches kohärenztomografie-system und -verfahren mit mehreren aperturen
DE3878572T2 (de) Geraet zur diagnostik in der augenheilkunde.
DE4222395A1 (de) Vorrichtung und Verfahren zur Messung der Augenrefraktion
HUE028034T2 (en) Eye image analysis for the diagnosis of neurodegenerative diseases
DE10304185B4 (de) Vorrichtung und Verfahren zum Anpassen einer Position eines Brillenglases relativ zur Position einer Pupille
DE102011088038A1 (de) Operationsmikroskopsystem für die Ophthalmologie und zugehörige Detektionseinheit
WO2013189591A1 (fr) Microscope pour chirurgie oculaire, présentant un dispositif de mesure de l&#39;amétropie
EP0136440B1 (fr) Appareil ophthalmique et dispositif de mesure pour l&#39;examen du fond de l&#39;oeil
DE3885341T2 (de) Gerät zur Diagnostik von Augenleiden.
DE68911974T2 (de) Ophthalmologisches Diagnose-Verfahren und Gerät.
WO2008077854A1 (fr) Appareil ophtalmologique et procédé de détermination de la position de l&#39;œil d&#39;un patient
DE102004017130A1 (de) Verfahren zur Messung des Gefäßdurchmessers optisch zugänglicher Blutgefäße
DE102005020911A1 (de) Verfahren zur Messung der Änderung des Polarisationszustands von polarisierter optischer Strahlung durch eine optisch aktive Schicht eines Körpers und/oder einer Konzentration eines optisch aktiven Stoffs in der Schicht und Vorrichtung zur Durchführung des Verfahrens
WO2013017337A1 (fr) Dispositif de prise de vues destiné à réaliser des photographies de la rétine de l&#39;œil, procédé de prise de vues et produit programme d&#39;ordinateur
DE4422071B4 (de) Netzhaut-Blutströmungsgeschwindigkeits-Meßeinrichtung
DE102008008732A1 (de) Verfahren und Anordnung zur Bestimmung von Hornhautradien
JP2520426B2 (ja) 眼科測定装置
DE4410690C1 (de) Anordnung zur spektrometrischen Untersuchung und deren Verwendungen
DE102005019471A1 (de) Verfahren und Anordnung zur nichtinvasiven Blutzuckermessung
DE3689757T2 (de) Gerät zur Messung der Brechkraft der Augen.

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 12730488

Country of ref document: EP

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 10201300001809

Country of ref document: CH

WWE Wipo information: entry into national phase

Ref document number: 2120120000895

Country of ref document: DE

Ref document number: 212012000089

Country of ref document: DE

122 Ep: pct application non-entry in european phase

Ref document number: 12730488

Country of ref document: EP

Kind code of ref document: A1