EP1988816A2 - Appareil ophtalmologique - Google Patents

Appareil ophtalmologique

Info

Publication number
EP1988816A2
EP1988816A2 EP07722902A EP07722902A EP1988816A2 EP 1988816 A2 EP1988816 A2 EP 1988816A2 EP 07722902 A EP07722902 A EP 07722902A EP 07722902 A EP07722902 A EP 07722902A EP 1988816 A2 EP1988816 A2 EP 1988816A2
Authority
EP
European Patent Office
Prior art keywords
ophthalmological
illumination
eye
unit
radiation
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Withdrawn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
EP07722902A
Other languages
German (de)
English (en)
Inventor
Egon Luther
Ingo Koschmieder
Joachim Winter
Uwe Mohrholz
Manfred Dick
Thomas Mohr
Daniel Bublitz
Enrico Geissler
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 EP1988816A2 publication Critical patent/EP1988816A2/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Withdrawn legal-status Critical Current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
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
    • G02B27/0927—Systems for changing the beam intensity distribution, e.g. Gaussian to top-hat
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
    • G02B27/0938—Using specific optical elements
    • G02B27/095—Refractive optical elements
    • G02B27/0955—Lenses
    • G02B27/0961—Lens arrays
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
    • G02B27/0938—Using specific optical elements
    • G02B27/0994—Fibers, light pipes

Definitions

  • the present invention relates to a device for observing, documenting and / or diagnosing the eye, in particular the anterior segment of the eye, the iris, the lens, the vitreous body and the fundus of the eye.
  • conventional white light sources are used for illumination in conventional ophthalmological devices for examining the eye, in order to produce the most natural possible image of the interior of the eye for the observer.
  • appropriate spectral filters are used in the beam path after the white light source.
  • halogen lamps have a relatively long warm-up phase.
  • the light of the halogen lamp is parallelized with a condenser lens and then illuminates a gap that is adjustable in width. The light that passes through the gap is then imaged by an optical system sharp into the anterior chamber of the eye to be examined. The light backscattered by the eye is imaged on a camera with a second detection optics and / or allows the visual observation of the eye.
  • the illumination beam path is angled in front of the eye by a prism.
  • This deflecting prism is located approximately in the pupil plane in front of the eye. Since all illumination beams must transmit through the prism exit surface, this deflection prism limits the light conductance of the illumination source. It is important that the light passing through the slit in the illumination source is as homogeneous as possible, since this homogeneity is transmitted through the image into the eye as far as the focal plane of the slit lamp.
  • the gap is in the pupil plane of the incandescent filament of the halogen lamp, so that the homogeneity in the cleavage plane thus corresponds to the intensity homogeneity in the angular spectrum of the incandescent filament of the halogen lamp.
  • the document EP 1 114 608 B1 describes an ophthalmic irradiation system which uses illumination based on LEDs in a subcomponent of the overall system. det.
  • the device essentially serves to emit certain quantities of red, green and blue light in order to generate substantially white light.
  • the individual light regulation serves to maintain the color shade when the protective filter is swiveled in and out.
  • the document EP 1 114 608 B1 thus describes in a special sub-construction an illumination system based on LEDs, which serves to maintain the color neutrality in combination with an optical protection filter.
  • Document EP 1 602 323 A1 describes the use of a white LED as illumination source in a classic slit lamp.
  • the homogeneity in the cleavage plane corresponds to the intensity homogeneity in the angular spectrum of the chip area of the LED.
  • this also has negative effects on the achievable homogeneity.
  • an incandescent filament emits approximately a spherical wave with homogeneous intensity in the angular spectrum due to the curved shape of the filament, a lambertian angle spectrum is emitted to a good approximation by an LED chip functioning as a surface radiator.
  • the present invention has for its object to provide a solution to an energetically economical and applicatively improved lighting device for an ophthalmological device, which in particular by a spectrally selective, very homogeneous, multi-channel light generation with short switching times and high spectral stability in the switch-on and short-term Emission is marked.
  • a particularly advantageous applicative property of this novel illumination device is, for example, the possibility of providing high spectrally selective intensities in the UV-near range> 400 nm.
  • the ocular media have the highest scattering power in the visible range and can make the most sensitive diagnoses.
  • Figure 1 an arrangement for homogenizing the light of the radiation sources on the basis of a microlens array
  • FIG. 2 shows an arrangement for homogenizing the light of the radiation sources on the basis of a hollow integrator.
  • the ophthalmic apparatus with homogeneous illumination for observing and / or documenting an eye, comprising an illumination device with an illumination source, a homogenization unit and a projection device, one or more, spectrally selectively emitting radiation sources on an organic or inorganic basis are used as the illumination source.
  • these radiation sources generate continuous and / or pulsed spatial illumination in order to enable a correspondingly adapted visual and / or digital observation, recording or output of the examined regions of the eye via a digital camera unit.
  • LEDs, SLDs, lasers or O-LEDs are used singly or in combination as spectrally selectively emitting radiation sources on an organic or inorganic basis.
  • the illumination source preferably has a plurality of spectrally selectively emitting beams. sources with equal and / or different intensity distributions as a function of their wavelength.
  • the intensity distribution of the radiation sources are broadband, narrowband or monochromatic or are formed by combinations thereof.
  • radiation sources in the visible spectral range predominantly have a broadband intensity distribution
  • the illumination device has for emitting a broadband spectrum of preferably 400 to 700 nm via one or more radiation sources, which preferably emit a monochromatic (blue) spectrum of 400 to 490 nm and are coated with a luminescent dye for color conversion. This ensures that the vast majority of the emitted white spectrum is in the blue region.
  • a radiation source which preferably emit a monochromatic (blue) spectrum of 400 to 490 nm and are coated with a luminescent dye for color conversion.
  • Such LEDs which emit light in the blue region of the white spectrum, have the advantage that in the shorter wavelength range, a higher scattering occurs on the media of the eye, which enables an improved diagnosis.
  • an LED which emits a monochromatic spectrum in the UV range ( ⁇ 400 nm) and is coated with a luminescence dye for color conversion.
  • a luminescence dye for color conversion.
  • Such an LED has the advantage that no emission of the excitation wavelength ( ⁇ 400 nm) takes place in the visible range (400-750 nm).
  • the color conversion luminescent dye may preferably be designed so that the resulting
  • Narrow-band illumination allows diagnosis in special spectral ranges.
  • the observation can take place in the visible range directly or with illumination in the non-visible range by means of an electronic camera and the conversion / transmission of information in the visible range, for example by means of false color representation on a display.
  • certain intensity values in the non-visible range can each be assigned colors in the range 400-700 nm and displayed on the display.
  • the selection of desired wavelengths can take place via the actuation of selected monochromatic radiation sources.
  • illumination devices for emitting a broadband spectrum are also suitable for a spectral range of preferably 700 to 1100 nm
  • a digital camera unit sensitive in this spectral range is to be used here.
  • wavelengths in the UV range starting at approximately 180 nm are suitable for documenting the fluorescence images excited by an excimer laser
  • wavelengths in the IR range up to approximately 2 ⁇ m are used for images with little scattering of the radiation in the tissue and even more adequately To document water absorption. From a wavelength greater than 2 ⁇ m, the penetration depth is only sufficient for the cornea and thus no longer suitable for imaging.
  • OSRAM SFH4230 LEDs are used which emit radiation in the range of 700 to 1100 nm, with a half-width of 40 nm and a peak wavelength of 850 nm, in a Gaussian distribution.
  • This embodiment variant is particularly advantageous because no or only very little irritation of the eye takes place here and no mydriatics is required, which results in a narrowing of the pupil.
  • diagnoses are in the IR range, by transmission / conversion of information the IR range in the visible range, for example by means of false color representation on the display, possible.
  • reliable diagnoses are possible.
  • a broadband radiation source and monochromatic radiation sources in order to generate special intensity distributions.
  • the combination of radiation sources which do not overlap in the spectrum can preferably be effected by means of dichroic mirrors, which are imaged onto a common aperture.
  • dichroic mirrors which are imaged onto a common aperture.
  • the combination of different radiation sources is to ensure that the beams generated by the individual radiation sources match at the coupling point to the ophthalmological examination device in aperture and aperture angle.
  • a plurality of laser sources are used for the illumination.
  • the colinear imaging of the individual laser beams can preferably be effected by means of an optical grating or a prism.
  • the narrow-band spectra with a typical half-value width of, for example, +/- 3 nm can be widened to a half-value width of +/- 20 nm using optical conversion signals.
  • fluorescent dyes can be used as optical conversion coatings.
  • the illumination device has a homogenization unit in the form of a light integrator or light mixer, which is arranged in front of the radiation sources.
  • a hollow integrator or microlens array is used here as the homogenization unit.
  • the homogenization unit With the homogenization unit, the light emitted by the radiation sources is homogenized in terms of intensity, color and angle spectrum. The light homogenization should take place by the adaptation of the light conductance of the radiation sources to the illumination optics with the highest possible light efficiency.
  • - 9 - 1 shows an arrangement for homogenizing the light of the radiation sources on the basis of a microlens array.
  • the light coming from the radiation sources 1 is collimated with a condenser lens 2 and imaged onto the microlens array 3.
  • the microlens array 3 consists of respective opposing spherical surfaces 3.1 (input plane) and 3.2 (output plane) with a distance 3.3 corresponding to the focal length of the microlenses.
  • the radiation source 1 consisting, for example, of individual LEDs, is imaged as far as possible into the imaging lens 5 arranged behind the microlens array 3.
  • a slit diaphragm can be arranged in the image plane 6 with which the slit illumination required for a slit lamp is generated.
  • the gap thus generated is projected via the projection device 7 and a deflecting prism 8 in the eye 9, wherein the angle of incidence of the illumination can be varied.
  • the homogenization of the illumination radiation achieved in this way can be illustrated as follows:
  • the pupil of the radiation sources 1 is located exactly in the input plane 3.1 of the microlens array 3, wherein the light distribution through the microlenses in exactly as many channels as there are microlenses.
  • the light of each channel is then imaged via the imaging lens 5 in the image plane 6 and superimposed there with the light of all other channels.
  • LEDs with Lambertian radiation profile as the radiation source 1
  • a cosinusoidal intensity distribution in the input plane 3.1 of the microlens array 3 can be observed.
  • the light of each microlens is imaged by the associated second microlens and the imaging lens 5 on the entire image field, an almost perfect homogenization in the image plane 6 can be achieved
  • the use of microlens arrays with honeycomb cross-sections of the individual lenses is provided. This is particularly advantageous for the generation of a slit illumination.
  • one or more white LEDs has the advantage that the illumination of the gap in the image plane and in the Forderhunt of the eye is substantially homogeneous than in classic "geköhlerten" lighting and has almost no edge drop more, which in particular for the realization of higher quality Measurements are crucial.
  • the measurement of the turbidity of the eye lens in cataracts called.
  • This also makes it possible, for example, for the adaptation of contact lenses, to use the brightness of a fluorescence contrast agent as a measure of the gap size between the eye and the contact lens.
  • LED arrays with an RGB structure Even greater improvements in illumination can be achieved by using LED arrays with an RGB structure.
  • FIG. 2 shows an arrangement for homogenizing the light of the radiation sources on the basis of a hollow integrator.
  • the light coming from the radiation sources 1 is collimated with a condenser lens 2 and imaged into the hollow integrator 4.
  • the light of the radiation sources 1 is homogenized and in the image plane 6 in which a slit diaphragm can also be arranged in order to produce the slit illumination required for a slit lamp.
  • the gap thus generated is projected via the projection device 7 and a deflecting prism 8 in the eye 9, wherein the angle of incidence of the illumination can be varied.
  • the result of this advantageous embodiment is an improved efficiency and the reduction of temperature-dependent effects.
  • the much more even light field also improves the variety of possible diagnoses and their reliability.
  • the control unit will control and monitor the timing, duration and intensity of the radiation sources individually, collectively or in groups to generate specific illumination spectra.
  • control of the one or more camera units can be tuned to the wavelengths of the light emitted by the lighting module and synchronized with their lighting duration.
  • At least one but preferably several images may be recorded in different colored lighting conditions with an exposure time of a few milliseconds. These monochromatic images can then be combined to form a colored image. Targeted differences in monochromatic images can also be evaluated.
  • An advantage of this embodiment is that no mechanically moving filters are required that different diagnoses can be carried out with only one device, that by temporal modulation of the radiation source and synchronous, assigned recording several monochromatic recordings can be realized, which evaluated defined or even to a chromatic Mixed image are summarized without thereby increasing the radiation exposure of the patient.
  • control unit determines, monitors and corrects the optical power and / or the geometry of the light emitted by the radiation sources to keep the radiation exposure of the eye as low as possible and within acceptable limits.
  • control unit should monitor important setting values of the ophthalmological device, such as, for example, currents and / or voltages for determining the radiation dose.
  • important setting values of the ophthalmological device such as, for example, currents and / or voltages for determining the radiation dose.
  • wavelength-specific hazards such as thermal and photochemical hazards to the eye.
  • control unit should have means for reducing or shutting off the supply of the radiation source.
  • such radiation sources are distinguished by a good dimming capability with an almost constant color temperature, with only a very slight color shift (of ⁇ 0.02) in the standard color chart, which substantially improves the reproducibility of diagnostic results given different radiation powers of the radiation source. Even a heating of the radiation sources leads only to a very small shift of the color locus (of, for example, 0.0002 / 0 C) or the peak wavelength (of, for example, 0.04 nm / ° C).
  • these radiation sources are also characterized by very short on and off times (from 0% to 100% of the rated current), which are in the range of ms or even ⁇ s.
  • a specific operating point eg a specific current value
  • a brightness control can be performed with an identical operating point. This results in a further possibility for stabilizing the color temperature and thus for a better reproduction of diagnostic results at different radiation powers of the beam source.
  • the radiation sources offer the possibility of a short-term overload without damage, with the amount of overload depends on their duration.
  • the duration of a 3-times rated current overload is in the ms range for LEDs.
  • the radiation sources have a comparatively long service life, which is more than 10,000 hours depending on the type.
  • device design can be developed for the overall ophthalmic device that does not provide for the replacement of the radiation source during operation.
  • optical filters offer the possibility, in particular in the UV and IR ranges, to limit the emitted spectra in a defined manner by means of edge filters.
  • the edge wavelengths of the optical filters are typically 380, 400 or 420 nm in the UV range or 700 nm in the IR range.
  • the radiation sources used In order to ensure sufficient light output, it must be ensured that the radiation sources used have an optical minimum power and emit the light locally evenly from the emitting surface. Furthermore, the intensity of the radiation source should be continuously adjustable over a wide range and the color temperature over the entire range of intensity should be largely constant.
  • powers of 10 to 20 W are achieved in the visible spectral range (400 to 700 nm), which corresponds to about 1 W of optical power.
  • the illumination device consisting of an illumination source and a projection device additionally has devices for geometrical and / or spectral manipulation of the emitted light, which are used selectively.
  • the radiation source of the radiation generation the device for manipulating the generation of geometric and / or spectral illumination patterns and the focusing optics of the projection of the illumination pattern on and / or in the eye.
  • the filter preferably have wavelength-selective properties, such as high, low or band pass filter.
  • a suitable technical solution is that a centrally arranged, vertical gap (slit prism) is used for the illumination and the observation preferably takes place laterally past it.
  • the control unit can either be integrated into the ophthalmological examination apparatus or designed as a separate unit connected via data lines and serves both to control the radiation sources and manipulation means for generating a continuous and / or pulsed structured illumination, as well as to control the digital camera unit for visual inspection.
  • a separately formed control unit preferably has a user interface with an operating unit, a keyboard, a display and a data output unit, with standard PC interfaces preferably being used as data lines.
  • the data output preferably takes place via printers or standardized interfaces.
  • printers or standardized interfaces Of course it is also possible to save the data on different data carriers, such as floppy disk, CD-ROM, DVD, various memory cards or the like.
  • the device for the generation and manipulation of illumination patterns can optionally be controlled electronically in order to simplify the communication to the control unit.
  • the control unit controls the corresponding radiation sources via the switch-on time and duration, as well as current and voltage, so that the desired spectral illumination pattern is produced.
  • these can also be embodied as separate units, wherein the radiation is guided, for example via optical fibers, to the ophthalmological apparatus and coupled into its illumination beam path.
  • the advantage of such an embodiment is in addition to a very compact design of the ophthalmological device made possible by the possibility of a very individual adaptability of the lighting to the respective task to be solved.
  • the digital camera unit is designed so that it can be used as a device for visual observation, wherein the output of the image of the examined eye takes place on a display which is present on the camera or separately.
  • a contact glass can be used for increased observation.
  • the digital camera unit serves in particular to record and output these images.
  • the digital camera unit is controlled synchronously with the radiation sources used.
  • the digital camera unit consists of a commercially available consumer camera, which preferably stores the recordings digitally on a transportable storage medium, such as a compact flash card, SD card, memory stick or the like.
  • a transportable storage medium such as a compact flash card, SD card, memory stick or the like.
  • the control unit itself or a PC system connected via a data line serves to store the images of the examined eye, preferably in the form of a patient-related database.
  • the system should allow both data export and import of patient-related data using standardized file formats (eg DICOM), as well as post-processing and extraction of functional features from the digital camera recordings in order to obtain relevant information for optimal diagnostics.
  • the images evaluated in terms of quality and existing artifacts and optionally software in terms of image sharpness, contrast, pixel error, Marginal drop, distortion, color aberration, local offset or the like can be corrected.
  • the ophthalmological examination device has a device (eg, beam splitter) with which a preferably variably adjustable part of the radiation can be coupled out to an existing opto-electronic interface.
  • a device eg, beam splitter
  • Various applicators can be connected to this standardized interface. Furthermore, this electronic control and monitoring of the coupled applicator is present.
  • a flexible optical fiber configured as a stepped or gradient fiber for transmitting the optical radiation can then be connected to the standardized interface in order to provide a separate additional illumination.
  • the flexible light guide is used, for example, for scleral illumination, so that the eye can be "backlit” illuminated, in particular for observation / documentation of cornea, iris, lens, capsular bag or existing implants.
  • the or even more flexible light guide can also for a serve regrediente lighting.
  • a flexible light guide communicates with a lighting module, which is mounted on the head of the doctor.
  • the relatively high efficiency of the lighting unit also enables a time-limited, mobile operation.
  • the supply of the radiation sources takes place here by means of batteries.
  • an increase in the sharpness of the electronic images of the eye can be achieved by optical image stabilization, in
  • a mechanically movable, optical element is arranged, with which existing movements of the eye - especially at longer exposure times - can be compensated.
  • the same effect can be achieved if the electronic image sensor itself is mechanically movable.
  • An increase in the sharpness of the electronic images can also be achieved by using shorter exposure times in combination with higher light intensities of the radiation source and / or methods of electronic amplification or post-processing of the image data for image acquisition.
  • the electronic camera used as a visualization unit has several sensors.
  • each monochromatic radiation source of illumination is assigned a sensor in the observation beam path. The assignment can be made in the observation beam path z. Example by means of dichroic filters or a beam splitter filter combination. Thus, the exact same time recording of multiple monochromatic images is possible.
  • the illumination takes place in the form of very narrow gaps which lie in the range of 10 ⁇ m to 1 mm, for which purpose a laser source with a very low light conductance and above all with very small divergence is used.
  • This type of illumination is used in slit lamps, which can be used to examine details in the front of the eye. With adjustable magnification and special lateral illumination with the so-called light gap numerous diseases are recognizable.
  • the laser source sends a short pulse in the range of ⁇ s up to a few milliseconds into the eye.
  • This radiation which is scattered on the media of the eye, is recorded by an electronic camera, whereby optionally an optical filter can be used, which is transparent only for the excitation wavelength of the laser.
  • the special slit illumination described here combines the advantages of a very good signal-to-noise ratio and a very high depth of focus.
  • the proposed illumination device provides spectrally selective spectra of high intensities in the UV-near range> 400 nm. Since the ocular media have the greatest scattering power in this range, very accurate diagnoses can be made.
  • the irritation of the eye is very low. Due to the possibility of a diagnosis in the IR range, there is no narrowing of the pupil during the observation. The diagnostic options are significantly improved and the radiation exposure of the patient is reduced.
  • the selection of desired wavelengths via the operation of selected monochromatic radiation sources take place, so that mechanically moving optical filters are no longer necessary and simplifies the device structure.
  • the advantage compared to existing solution is that only the wavelength necessary for the diagnosis is emitted by the radiation source, which also minimizes the radiation exposure of the patient
  • the LEDs used have a much more uniform light field, better efficiency, lower temperature-dependent effects, a stable color temperature, improved efficiency, lower heat load and better reproducibility of diagnostic results at different radiant powers of the radiation source.

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  • Physics & Mathematics (AREA)
  • General Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (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

La présente invention concerne une solution pour effectuer un examen, établir un dossier et/ou effectuer un diagnostic de l'oeil, en particulier de la partie antérieure de l'oeil, de l'iris, du cristallin, du corps vitré et du fond de l'oeil. L'appareil ophtalmologique à éclairage homogène selon l'invention est constitué d'un dispositif d'éclairage pourvu d'une source d'éclairage, d'une unité d'homogénéisation et d'un dispositif de projection, une ou plusieurs sources de rayonnement à base organique ou inorganique à émission à sélectivité spectrale étant utilisées comme source d'éclairage dans ledit appareil. L'éclairage ainsi produit permet, au moyen d'une unité de visualisation, un examen visuel et/ou numérique adapté, l'enregistrement ou la sortie des zones examinées de l'oeil. A des fins d'homogénéisation, la lumière provenant des sources de rayonnement (1) est collimatée au moyen d'une lentille de condenseur (2) et projetée sur le réseau de microlentilles (3) constitué de faces sphériques opposées (3.1) et (3.2) situées à une distance (3.3) l'une de l'autre qui correspond à la focale des microlentilles. Ledit appareil ophtalmologique permet d'effectuer un examen et/ou d'établir un dossier pour certaines zones d'un oeil, en particulier dans l'UV proche < 400 nm, dans lequel les milieux oculaires présentent le pouvoir de diffusion le plus élevé.
EP07722902A 2006-02-28 2007-02-22 Appareil ophtalmologique Withdrawn EP1988816A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006010105A DE102006010105A1 (de) 2006-02-28 2006-02-28 Ophthalmologisches Gerät
PCT/EP2007/001527 WO2007098882A2 (fr) 2006-02-28 2007-02-22 Appareil ophtalmologique

Publications (1)

Publication Number Publication Date
EP1988816A2 true EP1988816A2 (fr) 2008-11-12

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EP07722902A Withdrawn EP1988816A2 (fr) 2006-02-28 2007-02-22 Appareil ophtalmologique

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US (1) US7871164B2 (fr)
EP (1) EP1988816A2 (fr)
JP (1) JP5227811B2 (fr)
CN (1) CN101389263A (fr)
DE (1) DE102006010105A1 (fr)
WO (1) WO2007098882A2 (fr)

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JP5227811B2 (ja) 2013-07-03
DE102006010105A1 (de) 2007-08-30
CN101389263A (zh) 2009-03-18
WO2007098882A2 (fr) 2007-09-07
WO2007098882A3 (fr) 2007-12-21
US20090257024A1 (en) 2009-10-15

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