EP2104448A2 - Système optique pour caméra d'observation - Google Patents

Système optique pour caméra d'observation

Info

Publication number
EP2104448A2
EP2104448A2 EP07856821A EP07856821A EP2104448A2 EP 2104448 A2 EP2104448 A2 EP 2104448A2 EP 07856821 A EP07856821 A EP 07856821A EP 07856821 A EP07856821 A EP 07856821A EP 2104448 A2 EP2104448 A2 EP 2104448A2
Authority
EP
European Patent Office
Prior art keywords
mirror
optical system
optical
imaging
image
Prior art date
Legal status (The legal status 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 status listed.)
Withdrawn
Application number
EP07856821A
Other languages
German (de)
English (en)
Inventor
Ingo Koschmieder
Manfred Dick
Detlef Biernat
Jan Buchheister
Lothar Müller
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Carl Zeiss Meditec AG
Original Assignee
Carl Zeiss Meditec 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 Carl Zeiss Meditec AG filed Critical Carl Zeiss Meditec AG
Publication of EP2104448A2 publication Critical patent/EP2104448A2/fr
Withdrawn legal-status Critical Current

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
    • A61B3/14—Arrangements specially adapted for eye photography
    • A61B3/15—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing
    • A61B3/156—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing for blocking
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B17/00—Systems with reflecting surfaces, with or without refracting elements
    • G02B17/02—Catoptric systems, e.g. image erecting and reversing system
    • G02B17/06—Catoptric systems, e.g. image erecting and reversing system using mirrors only, i.e. having only one curved mirror
    • G02B17/0605—Catoptric systems, e.g. image erecting and reversing system using mirrors only, i.e. having only one curved mirror using two curved mirrors
    • G02B17/0621—Catoptric systems, e.g. image erecting and reversing system using mirrors only, i.e. having only one curved mirror using two curved mirrors off-axis or unobscured systems in which not all of the mirrors share a common axis of rotational symmetry, e.g. at least one of the mirrors is warped, tilted or decentered with respect to the other elements
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B17/00—Systems with reflecting surfaces, with or without refracting elements
    • G02B17/08—Catadioptric systems
    • G02B17/0856—Catadioptric systems comprising a refractive element with a reflective surface, the reflection taking place inside the element, e.g. Mangin mirrors
    • G02B17/086—Catadioptric systems comprising a refractive element with a reflective surface, the reflection taking place inside the element, e.g. Mangin mirrors wherein the system is made of a single block of optical material, e.g. solid catadioptric systems

Definitions

  • the invention relates to an optical system for a fundus camera, which is used for observation and imaging of the fundus.
  • a fundus camera When imaging the fundus of the eye with such a camera, reflections on the cornea and on the surfaces of the imaging optical system generally occur, which have a disturbing effect on the quality of the images and their evaluation.
  • a fundus camera comprises a multi-stage optical system, wherein an ophthalmoscope lens generates an intermediate image which is imaged by a sequential system or main objective on a film, on a CCD matrix of a CCD camera or in an intermediate image for visual observation with an eyepiece.
  • the ophthalmoscope lens is also a component of the elements of the illumination system.
  • the reflections on the cornea and on the surfaces of the ophthalmoscope lens represent a particular problem in the observation and recording of the fundus, because the light reflected by the retina, which carries the actual information of interest, has a considerably lower intensity than before light reflected from the entrance into the eye.
  • Disturbing corneal reflexes are usually prevented by a division of the pupil of the eye.
  • the ophthalmoscope lens forms a lighting ring in the eye pupil.
  • DE 103 16 416 describes an optical system in which instead of the ophthalmoscope lens a multi-lens is provided whose lenses are tilted relative to one another so that the direct reflections at the boundary surfaces do not reach the aperture of the observation. There is a tilt in the X and Y direction for each pair of lenses available.
  • This optical system requires a considerable effort for the mechanical versions of the individual lenses of the lens.
  • transverse color and longitudinal chromatic aberrations are generated, which must be compensated with great effort in the secondary optical system both in the observation and in the illumination part of the beam path.
  • the high number of optical interfaces and the long glass path inside the lens are also detrimental. Even small impurities at the interfaces and in the Material of the optical components used can add up unfavorably and greatly reduce the intensity of the light and produce disturbing stray light.
  • a tilted lens assembly is also described in US 4,730,910.
  • fundus cameras which have mirror elements in place of the ophthalmoscope lens. These systems have simple mirror geometries, with which only a small observation or illumination field with a sufficient optical quality can be realized.
  • the invention is based on the object to provide an optical system for a fundus camera, in which by using less, especially reflective optical elements for imaging a free of disturbing reflections and largely free of color aberrations mapping of the fundus in a large field of observation and a long working distance is reached.
  • the object is achieved in a designed according to the features of the preamble of the first claim optical system with the in marked part of this claim.
  • the subclaims contain discloses some embodiments and details of the inventive optical system.
  • An advantageous system for realizing a largely reflex-free ophthalmoscopy results when a mirror system consisting of two free-form mirrors is provided, wherein the free-form mirrors are designed as symmetry-free free-form mirrors, between which the intermediate image is located at a suitable location in the room.
  • a distribution of the powers of refraction and small deflection angles which favorably affects the aberrations are realized.
  • the application of symmetry-free freeform surfaces realizes the compensation of the unbalanced aberrations particularly advantageous.
  • the mirror system is arranged in encapsulated construction in a housing which is closed on the side facing the patient and on the side facing the observer by a respective cover.
  • the cover plates themselves are to be designed in the execution of their surface shape so that any resulting disturbing reflections can not get into the observation aperture and color errors remain minimal.
  • the optical elements of the mirror system are arranged in a common holder or recording in a precisely defined position and position to each other in the housing. This holder is designed such that the mirrors have a fixed reference to each other and to each other, which allows the positioning of the mirror with the required accuracy in an assembly step without adjustment in the housing.
  • the mirror system consists of a monolithic body of optical material with a refractive index n> 1, on which the imaging reflective surfaces are provided at precisely defined positions and in a precisely predetermined surface shape and a Lichteintritts- and a light exit surface, wherein the Lichteintritts- and the light exit surface of this body, since they are refractive surfaces in this case, get such a surface shape that disturbing reflections are avoided and color errors are minimized. Due to the monolithic design eliminates a costly adjustment of the reflective surfaces of the mirror, so that this system is very easy to install.
  • the light entry and / or the light exit surface of the monolithic body are asymmetrically shaped.
  • At least one reflective, electronic structurally or adaptive optical element is provided. It is convenient to arrange the adaptive elements in the vicinity of the device pupil.
  • At least one of the optical elements of the mirror system is designed as a spectral color splitter.
  • An advantageously configured embodiment of an inventive optical system results, for example, from the following coordinates for the position of mirrors 1 and 2 designed as free-form mirrors corresponding to one
  • Illuminated ring -51.2908710 39.1319540 30.6900040; and a surface shape defined by the following relationship for the mirrors 1 and 2 relating to the respective flat coordinate system Z (PS 2 + p y y2 + W ⁇ - Q + k y) p y - Q + ⁇ ⁇ y) p y]
  • one of the mirrors is designed as a spectral color splitter.
  • the excitation light in fluorescence applications can be placed very close to the application site become.
  • the structure of the entire optical system of the device considerably simplified because color splitters and other additional elements to correct the extended spectral bandwidth are not necessary.
  • the optical system for non-reflective ophthalmoscopy is advantageously used in devices for multi-color laser photocoagulation, for performing optical coherence tomography (OCT) and in devices for eye diagnosis and therapy with ultra-short pulse lasers.
  • the application in the case of hyper-spectral imaging or in multispectral imaging for the diagnosis of functions of the retina in fundus reflectometry is advantageous. Also advantageous is the use in fundus cameras based on a traditional temporally parallel color image generation or on the basis of a new temporally sequential color image generation or on the basis of a sequential multispectral fundus reflectometry with a monochrome chip.
  • the use of the free-form mirror optics in devices with OCT, confocal or line laser scanners or in devices and / or methods for imaging the retina may also be advantageous.
  • the application is advantageous in confocal laser scanners.
  • the size of the entire optical system can also be minimized by minimizing the distance of the patient's eye to be examined from the mirror adjacent to the patient.
  • the intermediate image can be positioned so that no optical surfaces are imaged onto the retinal image in the area in which most ophthalmic sight defects lie. Due to the additional degrees of freedom, which allow the free-form mirrors used, the image fidelity over an illumination field or over an observation field> 30 ° is guaranteed.
  • all components are arranged such that there is a free working distance of approximately 30 mm to 50 mm between the eye of the patient and a component, so that ergonomic aspects on the patient side are met and the physician obtains sufficient manipulation freedom.
  • the size of the entire optical system can also be minimized by minimizing the distance of the patient's eye to be examined from the mirror adjacent to the patient.
  • FIG. 1 shows an optical system with two free-form mirrors
  • FIG. 2 shows an optical system with two free-form mirrors
  • Fig. 3 shows a system of optical material with a refractive index n> 1.
  • FIG. 1 is an advantageous possible exemplary embodiment of an optical system for carrying out a flexflex ophthalmoscopy, in particular with a fundus camera, shown in a greatly simplified form, wherein only the optical elements, which comprises a substantially coaxial illumination and imaging or observation, or camera beam path, simplified without frames or other mechanical holding means are shown.
  • a mirror system which consists of two imaging, reflective, optical elements in the form of mirrors 1 and 2. At least one of these two mirrors 1 or 2 is designed as a so-called free-form mirror with an imaging, reflective free-form surface.
  • the mirrors 1 and 2 each have a free-form surface as an imaging surface with the design data listed below:
  • K x O. OO OO OO OE + 00
  • p mean curvatures of the surfaces at the coordinates x and y, K x the sagittal conical constant, K y the meridional conic constant and z the arrow height of points of the surfaces of the mirrors 1 and 2.
  • the origin of the coordinates is at the location of the eye pupil ,
  • the free-form surfaces are formed as symmetry-free surfaces, and they are not rotation surfaces, as e.g. is a sphere or a paraboloid surface.
  • the two mirrors 1 and 2 there are two areas in which, depending on the inclination of the mirror 1 and 2 to the optical axis 3 of the beam path, local regions of the mirror surfaces are sharply imaged on the fundus image (intermediate image). This is done in this case for the mirror 2 in the range of about -6.0 D to -5.0 D. In the range of about +8.0 D to +13 D, surface defects of the mirror 1 are sharply imaged on the fundus image. For eye defects, in which If the intermediate image is located on one of the two mirrors 1 or 2, contamination of the mirror surfaces can cause scattering effects in the imaging.
  • an intermediate image 4 is positioned between the mirrors 1 and 2 in such a way that no image of the mirror surfaces is imaged on the image in a range from -5.0 to +8.0 D, in which most eye defects are present the retina takes place. This prevents impurities, imperfections or production-related defects of the mirror surfaces from being imaged on the retinal image. For eye deficiency sight outside the specified diopter range, where the intermediate image 4 is located on one of the mirrors 1 or 2, impurities on the mirror surfaces can be excluded by digital image processing.
  • the mirrors 1 and 2 are arranged, for example, in a housing so that their reflective surfaces are not directed upwards.
  • the optical system of a fundus camera comprises an illumination path 5 with an illumination beam path 6 (shown dashed in FIG. 1) and with the imaging mirrors 1 and 2.
  • the light from a light source, not shown, is provided via a deflection mirror provided with an opening 7 8 and via the mirrors 1 and 2 for illuminating the fundus of an eye to be examined 9 passed into the eye.
  • a fundus image is then imaged through the eye lens 11 and the mirror 2 as an intermediate image 4 in an intermediate image plane.
  • This intermediate image 4 is then through the Mirror 1 through the opening 7 of the deflection mirror 8 through in a subordinate observation or recording path 12 on the receiver of a camera, not shown, or imaged in an image plane of observation optics for visual observation.
  • a cover plate is provided which must be designed and dimensioned such that reflections arising from it do not enter the observation or recording path 12 can and color errors remain minimal.
  • This cover can also have an asymmetrical surface shape.
  • a protection against contamination of the mirror 1 and 2 can also be achieved by a thin film, which is then tilted to avoid disturbing reflections to the optical axis 3.
  • FIG. 2 shows greatly simplified the elements of an encapsulated optical system with the mirrors 1 and 2 and advantageously, cover plates 13 and 14, wherein in the exemplary embodiment, the cover 13 on the patient side and the cover 14 on the Beobachtungst. Capture side the surrounding housing.
  • the surrounding housing has been omitted for the sake of simplicity.
  • the two cover plates 13 and 14 are designed and arranged in their execution so that resulting reflections can not get into the observation or recording path 12 and color errors are greatly minimized.
  • the two mirrors 1 and 2 it is advantageous to fix the two mirrors in a holder (not shown) after their adjustment, so that the position of the mirror can not change. Together with the holder then the mirrors 1 and 2 can be installed in an assembly step effectively without further adjustment in the device.
  • FIG. 1 A further advantageous embodiment of the optical system according to the invention for non-reflecting ophthalmoscopy and imaging of the fundus is shown in simplified form in FIG.
  • This system comprises a monolithic body 15 of optical material with a refractive index n> 1, on which the imaging reflective surfaces are arranged at precisely defined positions and in a precisely predetermined surface shape, as well as a light entry surface 16 and a light exit surface 17.
  • the light path in this embodiment proceeds as follows: refraction of the incoming light at the light entry surface 16, then reflection at a first reflective surface 18 of the body 15, then reflection at a second reflective surface 18 of the body 15 th reflective surface 19 of the body 15 and then exit of the light from the body 15 through the light exit surface 17 and refraction of the light at this surface.
  • the light entry surface 16 and a light exit surface 17 as refractive surfaces and must therefore be designed and profiled so that disturbing reflection can not get into the observation or recording path 12 and color errors remain minimal. This can be achieved, for example, by virtue of the fact that the light entry surface 16 and / or the light exit surface 17 have an asymmetrical or another suitable surface shape.
  • the monolithic design has u.a. the advantage that a costly adjustment during production and possibly Nachjus- days after prolonged use of the imaging mirror to each other omitted. This arrangement is also very easy to install.
  • the fundus camera such that a minimization of the distance between the patient's eye and the mirror 2 adjacent to the patient's eye is achieved. This also minimizes the size of the entire optical system. Minimizing this distance also results in an advantageous displacement of the region in which local regions of the mirror surfaces are not sharply imaged onto the fundus image and which is shifted toward higher myopic refractive errors, so that in accordance with the statistical frequency of the ocular vision also percentage more fundus images without interference from surface defects on mirrors 1 and 2.
  • An advantageous embodiment of the optical system according to the invention can also be designed so that it is possible to influence the field size and shape as well as the pupil size and shape. This can advantageously be achieved with at least one electronically structurable or adaptive optical element in the optical system.
  • such a structurable or adaptive element can be arranged instead of the deflecting mirror 8 (FIG. 1) or at another suitable location in the beam path of a fundus camera.
  • a structurable or adaptive element for example, in the illumination beam path of a fundus camera, asymmetries can be maintained, so that the requirements for the imaging system for non-reflecting ophthalmoscopy are reduced and a simpler production is achieved.
  • a simple adaptation of field size and pupil to different application tasks is possible.
  • adaptive elements can also be used to compensate for device-specific errors or even higher-order ocular errors, thus enabling an optimally corrected fundus image and, for example. gives the doctor advantages in a diagnosis.
  • the adaptive element is advantageously arranged in the vicinity of the device pupil.
  • the optical system for reflex ophthalmoscopy according to the invention proves to be particularly advantageous when a fundus camera with this system and laser applications for diagnosis and therapy are combined.
  • the freedom from color errors is particularly advantageous since the different wavelengths used have no shelves in the application plane.
  • the omission of false light paths (reflexes) facilitates registered, precisely controlled laser photocoagulation.
  • the small number of optical components results in fewer optical interfaces and very short paths in optical media.
  • OCT Optical Coherence Tomography
  • the absence of chromatic aberrations of the system is particularly advantageous since additional corrections for shortening the pulse widths can be omitted.
  • the absence of chromatic aberrations of the system is advantageous in that additional elements for correcting the extended spectral bandwidth can be omitted.
  • the application of the optical system according to the invention can be carried out both within fundus cameras based on a traditional temporally parallel color image generation (generation), as well as with a new, temporally sequential color image generation or with a sequential multispectral fundus reflectometry with a monochrome chip advantageously apply.
  • generation traditional temporally parallel color image generation
  • new, temporally sequential color image generation or with a sequential multispectral fundus reflectometry with a monochrome chip advantageously apply.
  • the desired spectral component is filtered out of the white flash by means of a color filter.
  • This solution is not energetically efficient.
  • a better solution here is the use of LED both in continuous, as well as in pulsed mode. LEDs of different emission wavelengths, eg red, green and blue are used for color recordings.
  • Monochrome techniques use one or more LEDs with appropriate wavelengths. Due to the almost delay-free switching on and off of the LED, sufficiently short exposure times can be achieved. The spectral characteristics of the LED are known with sufficient accuracy and can be energetically efficiently influenced by filters, which makes optimal color management easier to realize.
  • the image acquisition for red, green and blue takes place in a meaningful sequential manner, ie as image sensor, a black and white image sensor (high sensitivity) is used, and by pulsed LED, the respective color sub-image is sequentially fed .
  • Optimal modulation of the color partial images can be achieved by selecting the pulse lengths or pulse heights.
  • continuous illumination for the purpose of adjustment to the examination subject can be achieved by a suitable choice of the intensities of the used LED a meaningful, adapted to the object spectral light mixture can be achieved.
  • chromatic aberrations can be selectively influenced synchronously to the respective spectral light pulses. For example, with specific adjustments of a used adaptive element during an associated colored light pulse, an optimal correction can be achieved. A similar effect can be achieved with an optical element which is selectively changed in its position in the beam path, for example in the form of a shift lens. In this way, the optical design can be simplified in terms of chromatic corrections, since not all corrective measures must be applied simultaneously.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
  • Biomedical Technology (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biophysics (AREA)
  • Heart & Thoracic Surgery (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 système optique pour une caméra d'observation ophtalmoscopique sans reflet, ce système comportant une trajectoire de faisceau dans laquelle se trouvent des éléments optiques de réfraction et de réflexion utilisés sensiblement ensemble pour l'éclairage et l'observation ou la prise de vue. L'éclairage et l'imagerie du sujet d'observation sont réalisés au moyen d'un système de miroirs d'imagerie comprenant essentiellement plusieurs éléments optiques de réflexion sous forme de miroirs (1 et 2), au moins un élément optique, par exemple un miroir (2), étant un miroir de forme libre présentant une surface d'imagerie et de réflexion de forme libre. Selon l'invention, les éléments optiques sont disposés les uns par rapport aux autres en des positions précises dans un boîtier de manière à éviter, dans une zone de dioptrie éloignée des yeux (9) du patient à examiner, une reproduction des surfaces de réflexion des éléments optiques sur l'image de la rétine observée.
EP07856821A 2006-12-21 2007-12-18 Système optique pour caméra d'observation Withdrawn EP2104448A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006061933A DE102006061933A1 (de) 2006-12-21 2006-12-21 Optisches System für eine Funduskamera
PCT/EP2007/011089 WO2008077526A2 (fr) 2006-12-21 2007-12-18 Système optique pour caméra d'observation

Publications (1)

Publication Number Publication Date
EP2104448A2 true EP2104448A2 (fr) 2009-09-30

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Application Number Title Priority Date Filing Date
EP07856821A Withdrawn EP2104448A2 (fr) 2006-12-21 2007-12-18 Système optique pour caméra d'observation

Country Status (5)

Country Link
US (1) US8066374B2 (fr)
EP (1) EP2104448A2 (fr)
JP (1) JP5232165B2 (fr)
DE (1) DE102006061933A1 (fr)
WO (1) WO2008077526A2 (fr)

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JP2010512877A (ja) 2010-04-30
US20100014052A1 (en) 2010-01-21
WO2008077526A2 (fr) 2008-07-03
WO2008077526A8 (fr) 2008-12-11
DE102006061933A1 (de) 2008-06-26
JP5232165B2 (ja) 2013-07-10
US8066374B2 (en) 2011-11-29
WO2008077526A3 (fr) 2008-09-18

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