WO2010118840A1 - Dispositif et procédé de mesure d'un système de lentilles, en particulier d'un oeil - Google Patents

Dispositif et procédé de mesure d'un système de lentilles, en particulier d'un oeil Download PDF

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Publication number
WO2010118840A1
WO2010118840A1 PCT/EP2010/002216 EP2010002216W WO2010118840A1 WO 2010118840 A1 WO2010118840 A1 WO 2010118840A1 EP 2010002216 W EP2010002216 W EP 2010002216W WO 2010118840 A1 WO2010118840 A1 WO 2010118840A1
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Prior art keywords
light
light beam
eye
measuring
doe
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PCT/EP2010/002216
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German (de)
English (en)
Inventor
Johannes Pfund
Mathias Beyerlein
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Optocraft Gmbh
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Publication of WO2010118840A1 publication Critical patent/WO2010118840A1/fr

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02015—Interferometers characterised by the beam path configuration
    • G01B9/02027—Two or more interferometric channels or interferometers
    • 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
    • A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B11/00—Measuring arrangements characterised by the use of optical techniques
    • G01B11/24—Measuring arrangements characterised by the use of optical techniques for measuring contours or curvatures
    • G01B11/2441—Measuring arrangements characterised by the use of optical techniques for measuring contours or curvatures using interferometry
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02001—Interferometers characterised by controlling or generating intrinsic radiation properties
    • G01B9/02007—Two or more frequencies or sources used for interferometric measurement
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02015—Interferometers characterised by the beam path configuration
    • G01B9/02029—Combination with non-interferometric systems, i.e. for measuring the object
    • G01B9/0203—With imaging systems
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02034—Interferometers characterised by particularly shaped beams or wavefronts
    • G01B9/02038—Shaping the wavefront, e.g. generating a spherical wavefront
    • G01B9/02039—Shaping the wavefront, e.g. generating a spherical wavefront by matching the wavefront with a particular object surface shape
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02041—Interferometers characterised by particular imaging or detection techniques
    • G01B9/02044—Imaging in the frequency domain, e.g. by using a spectrometer
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence

Definitions

  • the invention relates to a device for measuring a lens system, in particular a (human or animal) eye. More particularly, the invention relates to a device for measuring the optical thickness and at least one further property of the lens system, in particular the surface topography and the wave aberration.
  • LASIK procedure For surgical procedures on the human eye, such as the correction of the refractive error of the eye, the ablation of corneous tissue (LASIK procedure) by means of an excimer laser has been increasingly used recently.
  • an upper layer (English flap) of the cornea (cornea) is cut open and folded to the side. Then a suitable amount of tissue is ablated on the exposed corneal tissue and then the comea flap replicated again.
  • Accurate and comprehensive measurement of the various optical elements of the eye is crucial to the success of the treatment on the one hand, and can be used, on the other hand, to examine exclusion criteria that speak against the treatment of an eye. In this sense, in particular a precise knowledge of the corneal thickness, the surface topography of the cornea and the wave aberration of the eye is required.
  • a similar density of information is also required for other surgical or therapeutic treatments on the human eye, in particular for replacement of the crystalline lens by an artificial implant (cataract surgery) and for coronary transplantation.
  • the corneal thickness, corneal topography and wave aberration of the eye are usually measured separately. This often results in discrepancies between the two measurements carried out in chronological order. tions due to the instability of the eye as a biological object on the one hand and on the other hand due to the numerous adjustment degrees of freedom of the eye relative to the measuring device. When used in optical medicine, such a measurement discrepancy may particularly affect the success of eye surgery or other medical correction procedure. To avoid such discrepancies, therefore, a joint measurement of corneal strength, topography and wave aberration is desirable.
  • a device for the common measurement of the topography and wave aberration of the eye is known from DE 103 42 175 A1.
  • two optical measuring systems are provided with a common beam path area.
  • a first measuring system which serves for topography measurement comprises a light source for emitting a first light beam of a first wavelength.
  • the second measuring system which is used to measure the wave aberration, comprises a light source for emitting a second light beam of a second wavelength.
  • a diffractive optical element is arranged in a common beam path region of the first measuring system and the second measuring system, which adjusts the respective wavefront profile of the first light beam and the second light beam wavelength-selective.
  • OCT optical coherence tomography
  • the invention has for its object to provide a device for measuring a lens system, in particular an eye, the simultaneous measurement of the corneal thickness and / or eye length and at least one other property of the lens system, in particular the (surface) topography and / or the wave aberration allows.
  • a lens system in particular an eye
  • the simultaneous measurement of the corneal thickness and / or eye length and at least one other property of the lens system, in particular the (surface) topography and / or the wave aberration allows is to be understood as meaning that all measurements are carried out either simultaneously and in parallel be, or briefly in a row in a common measurement process, in particular without having to replace the meter or to have to dislocate with respect to the lens system to be measured.
  • the device comprises an OCT measuring system with a light source for emitting a first light beam of a first wavelength range, and at least one further optical measuring system with a light source for emitting a second light beam of a second wavelength range.
  • a diffractive optical element DOE is arranged in a common beam path region of both measuring systems, which deflects the first and second light bundles at least predominantly into different diffraction orders.
  • the use of the DOE advantageously enables a "decoupling" of the OCT measurement beam, ie the first light beam from the second light bundle of the second measurement system, thus enabling the simultaneous use of both measurement systems without impairing the quality of the OCT measurement in that the OCT measuring beam can be focused on the sample by means of the DOE in such a way that the reflected or scattered light is effectively collected again and directed back into the measuring system This ensures, among other things, that the light intensity irradiated onto the sample can be kept low with sufficient recording quality.
  • the second measuring system is preferably set up for measuring the (surface) topography or for measuring the wave aberration.
  • the (surface) topography is the three-dimensional shape of the lens surface. in the In the case of the eye, this lens surface is the surface of the cornea, ie the transparent cornea.
  • the term wave aberration generally refers to the deviation of the optical imaging properties of the real lens system to be tested from the imaging properties of a corresponding ideal lens system. In the case of the eye, the wave aberration includes first order aberrations such as myopia, hyperopia or astigmatism as well as higher order aberrations.
  • the second measuring system is preferably constructed in the manner of the respective measuring system described in DE 103 42 175 A1.
  • the device may also contain a plurality of further measuring systems, in particular a measuring system for the topography measurement and a further measuring system for the wave aberration measurement.
  • a further measuring system for the wave aberration measurement at least the light bundle associated with one of the further measuring systems and the OCT measuring beam from the DOE are preferably directed (i.e., completely or at least predominantly) into different diffraction orders.
  • the wavelength ranges of the first and second light bundles are preferably disjoint, ie spectrally overlap-free.
  • the wavelengths of the first and / or second light beam are preferably in the (non-visible) near-infrared region of the electromagnetic spectrum.
  • the DOE is designed such that it directs the first light bundle, ie the OCT measuring beam, at least predominantly into the zeroth diffraction order, and thus does not change, at least not substantially, the beam path of the first light bundle.
  • the second light beam is directed by the DOE at least predominantly in the first diffraction order.
  • the second measuring system is expediently designed for measuring the topography in this method variant.
  • the zeroth diffraction order of the second light bundle is preferably completely suppressed.
  • the OCT beam transmitted to the zeroth diffraction order is either parallel or co-efficient. guided axially to the optical axis of the system, or is deflected by a separate from the DOE optics such that it always falls approximately perpendicular to the surface of the lens system, in particular on the cornea surface.
  • a sub-variant of this embodiment is provided for the deflection of a DOE upstream - in particular refractive - optics, by the addition of the first light beam, i. the OCT beam, and the second light beam is approximately perpendicular to the surface of the lens system, ie in particular deflected to the corneal surface.
  • the DOE is expediently designed to be the first light beam, i. the OCT measuring beam, at least predominantly in the zeroth diffraction order directs, and thus the beam path of the OCT beam not, at least not significantly affected. For the measurement of the wave aberration, however, such convergent radiation guidance is unsuitable.
  • a wave aberrometry measuring beam forming here the second light bundle is therefore transmitted in this case at least predominantly into the first diffraction order by the DOE, wherein the DOE is tuned to the wavelength of the second light bundle such that the second light bundle after passage through the DOE becomes a light beam the wave aberration measurement has suitable, in particular approximately planar wavefront profile.
  • the diffractive optical element is designed to be the first light beam, i. the OCT measuring beam, at least predominantly in the first diffraction order directs, whereas it directs the second light beam through the DOE at least predominantly in the zeroth diffraction order.
  • the second measuring system is expediently designed for measuring the wave aberration in this method variant.
  • the diffractive optical element is preferably designed in such a way that it adapts the first light bundle predominantly directed in the first diffraction order with respect to its wavefront profile to the topography of the lens system.
  • This pre-adjustment is made such that the wavefront profile of the first light bundle in the region of the cornea one of these has approximately the same curvature, so that the OCT measuring beam everywhere approximately perpendicular to the comea surface impinges.
  • This pre-adaptation of the wavefront course to the corneal curvature ensures that the OCT measuring beam is reflected particularly effectively into the measuring system by substantially vertical reflection.
  • pre-adaptation of the Wei- lenfrontverlaufes is in other words the loss of light, for example, reduced by stray light.
  • the DOE is preferably configured such that the wavefront course of the first light bundle is matched to a standard medical model of the human eye, in particular Gullstrand's normal eye.
  • the DOE is preferably transparent so that the first and second light beams are thrown through the DOE onto the lens system.
  • the use of a reflective DOE within the scope of the invention is conceivable.
  • a surface-corrupted phase element is understood as a plate made of glass or a transparent plastic, in the surface of a relief-like diffraction grating is introduced.
  • a phase element can nowadays be manufactured comparatively inexpensively with extremely high precision.
  • the diffraction effect of the phase element can be highly flexibly adapted to the needs.
  • a surface grating with an extremely small grating period of the order of magnitude of a few hundred nanometers and thus a comparatively large deflection angle of the diffracted light can be achieved with a surface-coded phase element.
  • the DOE in another way, for example by means of a volume hologram or a reflective diffractive element.
  • LCD phase-shifting liquid crystal displays
  • a fixation target is an image that is offered for examination to a subject to be examined during the measurement.
  • the additional light beam used for the insertion of the fixation target has a further wavelength for which the DOE is preferably also ineffective.
  • the further wavelength is preferably different both from the first wavelength and from the second wavelength. In this way, it is ensured that this further light bundle does not affect the parallel measurements (pachymetry and topometry and / or wave aberration).
  • the wavelength of the light beam used for the insertion of the fixation target corresponds to the wavelength of one of the at least two measuring systems.
  • the measurement of the corneal strength by means of OCT, and the or each further measurement of the wave aberration, topography, etc. are preferably carried out at the same time.
  • a time sequential, i. a (in particular at a very short distance) staggered measurement is still provided as in terms of a simplified process implementation advantageous embodiment of the invention. This is particularly useful when using a common detector for more than one measuring system for better separation of the measuring signals of these measuring systems.
  • the measurements are preferably carried out at a time interval which is shorter than the reaction time of the eye, so that the measurements take place quasi-simultaneously with respect to the eye.
  • FIG. 1 shows a schematic representation of a device for measuring a human eye with a measuring system for measuring the topography, a measuring system for measuring the wave aberration and an OCT measuring system for measuring the cornea thickness and with a arranged in a common beam path range of the three measuring systems diffractive optical element (DOE),
  • DOE diffractive optical element
  • FIG. 2 is a schematic representation of an OCT unit of the OCT measuring system according to FIG. 1,
  • FIG. 3 is an enlarged detail view of a variant of the device according to FIG. 1, FIG.
  • FIG. 4 shows a further variant of the device according to FIG. 1 with a modified beam path of the OCT measuring system, according to FIG. 3, FIG.
  • FIG. 5 shows a representation according to FIG. 3 of a further variant of the device according to FIG. 1, FIG.
  • FIG. 6 is a representation according to FIG. 1 of a second embodiment of the device
  • FIG. 7 in illustration of FIG. 3 is an enlarged detail of the device of FIG. 5, and
  • FIG. 8 in illustration of FIG. 1, a third embodiment of the device.
  • FIG. 1 shows a schematic sketch of a device 1 for measuring the cornea strength, the comea topography and wave aberration of a human eye 2.
  • the (surface) topography is the three-dimensional shape of the lens surface.
  • this lens surface is the surface of the cornea 4, ie the transparent cornea of the eye.
  • the lens system of the eye 2 further comprises in known manner the eye lens 5 and the glass body 6.
  • the retina 7 (or retina) is arranged in a known manner.
  • wave aberration generally refers to the deviation of the optical imaging properties of the real lens system to be tested from the imaging properties of a corresponding ideal lens system.
  • the wave aberration includes first order aberrations such as myopia, hyperopia or astigmatism as well as higher order aberrations.
  • the device 1 To measure the topography of the cornea 4 (topometry), the device 1 is provided with a (topometry) measuring system 8.
  • the measuring system 8 comprises a light source 10, in particular a laser.
  • the light source 10 generates a light beam 11 of a wavelength ⁇ 1.
  • the light bundle 11 is first collimated along the beam path of the measuring system 8 in a collimator lens 12, widened via a Kepler telescope 17, and irradiated by means of a wavelength-selective beam splitter 13 into a common beam path region 14 of the measuring systems 8 and 9.
  • the light bundle 11 passes through a diffractive optical element immediately preceding the eye 2, hereinafter referred to as DOE 18 for short.
  • the light bundle 11 is collimated in the direction of the eye 2 by means of the DOE 18 described in more detail below in its mode of operation.
  • a portion of the light beam 11 incident on the eye 2 (hereinafter referred to simply as reflected light beam 11 ') is reflected on the surface 3 of the cornea 4 and reflected back against the direction of incidence by the DOE 18, the beam splitter 13 and the Kepler telescope 17.
  • the reflected light beam 11 ' is coupled out of the incident light beam 11 and directed onto a wavefront detector 20.
  • the Kepler telescope 17 is designed such that the cornea 4 is sharply imaged on the wavefront detector 20.
  • the wavefront detector 20 is optionally designed as a Shack-Hartmann sensor, as described for example in US 2003/0038921 A1.
  • the wavefront detector 20 may also be designed as an interferometer, in particular a shearing interferometer.
  • the device 1 comprises an (aberrometry) measuring system 9.
  • the measuring system 9 comprises a further light source 21.
  • the light beam 22 is collimated in a collimator lens 12 and irradiated by another Kepler telescope 17 and the wavelength-selective beam splitter 13 in the common beam path region 14.
  • the beam splitter 13 is transparent to the wavelength ⁇ 2, thus ineffective.
  • a beam splitter 13 with such wavelength selectivity can be produced by conventional technology, for example by a dielectric mirror.
  • the light beam 22 passes through the DOE 18 on the eye 2.
  • the light beam 22 passes through the DOE 18 quasi unmodified and falls as a further fine light beam through the cornea 4 and the eye lens 5 on the retina 7.
  • the light beam 22nd is scattered back diffusely at the retina 7.
  • This scattered light hereinafter referred to as backscattered light beam 22 ', falls back through the eye lens 5, the cornea 4, the DOE 18, the Kepler telescope 17 and the transparent for the wavelength ⁇ 2 beam splitter 13 against its direction of incidence.
  • the backscattered light beam 22' is coupled out and thrown onto a wavefront detector 24 of the measuring system 9.
  • the wavefront detector 24 is in turn optionally designed as a Shack-Hartmann sensor or as an interferometer.
  • the beam splitters 13 and 23, a precompensation unit 25 is optionally interposed.
  • This pre-compensation unit 25 contains a (not shown in detail) conventional optical zoom system or a lens arrangement with which the defocus and astigmatism components, ie, the short- or hyperopia and the astigmatism, can be compensated.
  • the pre-compensation unit 25 is also reversed to image the incident light beam 22 sharply on the retina 7.
  • the DOE 18 shown in FIG. 1 is a so-called surface-corrupted phase element whose structure and mode of operation is described in more detail in connection with the measuring systems 8 and 9 in DE 103 42 175 A1.
  • the device 1 also comprises a further light source 26, through which a further light beam 27 of a wavelength ⁇ 3 is superimposed on the eye 2.
  • the third light bundle 27 is in turn collimated by a collimator lens 28 and aligned by means of a wavelength-selective beam splitter 29 on the eye 2.
  • the third light bundle 27 serves to offer the eye 2 a so-called fixation target. This is understood to mean a picture which the test person aims at during the measurement.
  • the fixation target By sighting the fixation target, on the one hand, the visual axis of the eye 2 is aligned along the optical axis of the common beam path region 14.
  • the refractive power of the eye lens 5 is fixed in a region in which the subject can detect the fixation target sharply.
  • the subject is often faked by the fixation target an image at infinity, so that the eye lens 5 is held in the relaxed state during the measurement.
  • the light beam 27 also passes through the - optionally existing - pre-compensation unit 25, in particular to compensate for any short-sightedness of the eye 2, and thus to give the subject the opportunity to target the fixation target sharply.
  • the device 1 For the measurement of comea strength (pachymetry), the device 1 comprises an OCT measuring system 30.
  • the OCT measuring system 30 comprises an OCT unit 31 (described in more detail below) which generates a light beam 32 in the form of a fine measuring beam.
  • the light beam 32 has a continuous spectral distribution within a spectral band of typically between 30nm and 100nm about a central wavelength ⁇ 4.
  • the light beam 32 is introduced via a further collimator lens 33 and a further beam splitter 34 into the common beam path region 14 and passes coaxially or parallel offset to the optical axis of the common beam path region 14 through the beam splitter 13 and the DOE 18.
  • the light- The bundle 32 strikes the cornea 4 approximately centrally, with the light bundle 32 being partially reflected on the corneal outer surface and on the corneal inner surface.
  • the reflected light beam 32 is returned via the beam splitter 34 and the collimator lens 33 in the OCT unit 31 and detected there.
  • the beam splitter 13 is designed with respect to the spectral distribution of the light beam 32 such that the light beam 32 or 32 ', the beam splitter 13 passes unhindered.
  • the OCT unit 31 is preferably a frequency-domain OCT measuring arrangement designed in the manner of a Michelson interferometer.
  • the OCT unit 31 then comprises a light source 35, in particular in the form of a so-called superluminescent diode.
  • the light emitted by this light is split by a beam splitter 36 into the light beam 32 and a reference beam 37.
  • the reference beam 37 is reflected at a mirror 38, wherein the reflected reference beam 37 'is thrown back onto the beam splitter 36.
  • the beam splitter 36 of the reflected reference beam 37 ' is superimposed with the reflected light beam 32' and thrown together with the latter on a detector 39 in the form of a spectrometer.
  • the Comea strength is calculated in a conventional manner.
  • OCT unit 31 As an alternative to the OCT unit 31 shown in FIG. 2, it is also possible to use other conventional OCT measuring arrangements within the scope of the device 1, in particular so-called time-domain measuring arrangements.
  • the wavelength ⁇ 1 of the light beam 11 is preferably set to 1064 nm.
  • the light beam 11 is thus in the (non-visible) infrared range of the electromagnetic spectrum, so that the topometry measurement of the eye 2 is imperceptible.
  • the DOE 18 is designed to match the wavelength ⁇ 1 so that the light beam 11 is completely deflected to the first diffraction order while the DOE 18 is the zeroth diffraction order of the light beam 11 completely, or at least almost completely suppressed (see also DE 103 42 175 A1).
  • the DOE 18 is further configured such that the diffracted light beam 11 in the region of the cornea 4 has a curved wavefront profile that corresponds to the average surface curvature of the human cornea. This average value is derived in particular from the standard eye model by Gullstrand.
  • the wavelength ⁇ 2 of the light beam 22, 22 ' is ideally set to 532 nm in optical terms.
  • the light beam 22, 22 ' is transmitted through the DOE 18 exclusively to the zeroth diffraction order.
  • the light beam 22 thus passes through the DOE 18 with at least virtually unchanged wavefront profile.
  • the wavelength ⁇ 2 is fixed to wavelengths in the range between 690 and 750 nm, and thus to the transition between the red and infrared spectral ranges. In the latter case, although the light beam 22 is not completely transmitted, but predominantly in the zeroth diffraction order of the DOE 18.
  • the wavelength ⁇ 3 of the light beam 27 must necessarily be in the visible spectral range and is preferably selected such that the DOE 18 does not exert a diffractive effect on the light beam 27.
  • the wavelength ⁇ 3 is preferably set to 635 nm (red).
  • the wavelength ⁇ 3 can also be selected to be equal to the wavelength ⁇ 2. In this case, the light beam 27 is temporarily hidden during the aberration measurement.
  • the wavelength ⁇ 3 may also be selected such that the DOE 18 suppresses the zeroth diffraction order of the light beam 27.
  • the central wavelength ⁇ 4 of the light bundle 32, 32 ' is selected in the embodiment according to FIG. 1 such that the DOE 18 at least predominantly transmits the light bundle 32 into the zeroth diffraction order, ie substantially unchanged.
  • the central wavelength ⁇ 4 is determined in particular on the outer edge of the red spectral range, in particular to a value of between 500 nm and 750 nm, in particular 532 nm.
  • the beam path of the light beam 32 is fixed with respect to its position with respect to the optical axis of the common beam region 14.
  • the light bundle 32 is thereby always directed in particular to the same point of the cornea 4, in particular to its center.
  • the beam path of the light beam 32 can be changed by means of a deflection device, not shown here, so that the surface of the cornea 4 can be scanned by displacement of the light beam 32.
  • the light beam 32 according to FIG. 3 can be displaced parallel to the optical axis of the common beam region 14.
  • the light beam 32 can alternatively be pivoted relative to the optical axis of the common beam region 14 in such a way that the light beam 32 impinges on the corneal surface approximately perpendicularly.
  • the embodiment variants of the device 1 according to FIGS. 3 and 4 are similar to the embodiment shown in FIG.
  • the light beam 32 is always transmitted by the DOE 18 predominantly in the zeroth diffraction order, and thus passes through the DOE 18 substantially without change of direction.
  • the light bundle 32 is in turn displaceable parallel to the optical axis of the common beam region 14, but is deflected by an optical system (not explicitly shown) upstream of the DOE 18 in such a way that it always passes through the optics approximately perpendicular to the corneal surface falls.
  • the optical system is preferably a refractive optical system, in particular in the form of a converging lens, which advantageously has a wavelength sensitivity which is low in comparison with a diffractive optical system. having, and thus for the precise alignment of the polychromatic light beam 32 is particularly well suited.
  • the optics in addition to the light bundle 32, the further light bundles 11, 22 and 27 are convergently aligned with the cornea 4.
  • the convergent beam guidance is also desirable for the light beam 11 used for the topography measurement.
  • the DOE 18 arranged between the refractive optics and the eye 2 is therefore designed in such a way that it transmits both light bundles 32 and 11 at least predominantly into the zeroth order of diffraction and thus allows them to pass largely uninfluenced.
  • the light bundle 22 used for the aberration measurement is at least predominantly transmitted by the DOE 18 into the first diffraction order.
  • the DOE 18 selectively removes the convergent refractive beam guidance selectively for the light bundle 22 by producing a collimated, in particular approximately planar wave front course for this light bundle 22 directly in front of the eye 2.
  • the light bundle 27 used to image the fixation target is also collimated by the DOE 18, ie aligned homogeneously parallel to the optical axis with regard to its beam direction.
  • the illustrated in Fig. 6 second embodiment of the device 1 differs from the embodiments described above, especially in that here the light beam 32, so the OCT measuring beam is generated in a spectral range in which the light beam 32 through the DOE 18 predominantly transmitted in the first diffraction order.
  • the light bundle 32 extending within the common beam area 14 parallel to its optical axis is thereby deflected towards the optical axis after passage through the DOE 18 and collimated onto the cornea 4.
  • the described embodiment of the DOE 18 pre-adjustment of the first-order diffracted wavefront profile to the average Comea curvature
  • the light beam 32 is thereby deflected so that it always impinges approximately perpendicular to the surface of the cornea 4 (see also Fig. 7).
  • the central wavelength ⁇ 4 of the light bundle 32 is preferably set to an amount equal or similar to the wavelength ⁇ 1.
  • the OCT measuring system 30 has a beam deflection device 40 (also: angle scanner), with which the light bundle 32 is moved by a variable solid angle from its original propagation direction transversely to the optical axis of the common beam region 14 is deflected.
  • a collimator lens 41 connected downstream of the beam deflection device 40, the light beam 32 is again aligned transversely to the optical axis of the common beam region 14.
  • the third embodiment of the device 1 shown in FIG. 8 essentially corresponds to the embodiment described in connection with FIGS. 6 and 7.
  • the light beam 32 is first faded into the beam path of the topometry measuring system 8.
  • the beam splitter 34 is arranged within the Kepler telescope 17 of the measuring system 8.
  • the light beam 32 is then aligned here together with the light beam 11 through the beam splitter 13 parallel to the optical axis of the common beam path region 14.
  • the wavelengths ⁇ 1 and ⁇ 4 are preferably selected with a small spectral distance from one another.
  • the wavelength ⁇ 1 is set to 1064nm
  • the wavelength ⁇ 4 is set to 930nm.
  • the beam splitters 13 in the case of the embodiment according to FIG. 5) and 34 (in the embodiment according to FIG. 8) are to be configured correspondingly narrowband in order to ensure a clean separation of the light beams 11, 11 'and 32 or 32'.
  • the light beams 11, 11 'and 32, 32' in the embodiment according to FIG. 8 can also be fixed to the same wavelength length amount, in particular to 1064 nm.
  • the beam splitter 34 is suspended movably in such a way that it can be pivoted into the beam path of the measuring system 8 for the pachymetry measurement, and swung out of the beam path of the measuring system 8 for the topometry measurement.
  • the pachymetry Measurement and the topometry measurement must be performed alternately with each other over time.
  • DOE diffractive optical element

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Abstract

L'invention porte sur un dispositif (1) de mesure d'un système de lentilles, en particulier de l'œil (2). Le dispositif (1) comprend un système de mesure OCT (30), qui comprend une source de lumière (35) pour émission d'un premier faisceau lumineux (32) ayant une première plage de longueurs d'onde, et au moins un autre système de mesure optique (8, 9), qui comprend une source de lumière (10, 21) destinée à émettre un deuxième faisceau lumineux (11, 22) correspondant à une deuxième plage de longueurs d'onde (λ1, λ2). Dans une zone (14) de trajectoire commune des rayons de système de mesure (30, 8, 9), on a disposé un élément optique diffractif (18), qui dévie, au moins essentiellement dans différents ordres de diffraction, le premier et le deuxième faisceau lumineux (32,11, respectivement 32,22).
PCT/EP2010/002216 2009-04-15 2010-04-09 Dispositif et procédé de mesure d'un système de lentilles, en particulier d'un oeil WO2010118840A1 (fr)

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DE102009017144.4 2009-04-15
DE200910017144 DE102009017144A1 (de) 2009-04-15 2009-04-15 Vorrichtung und Verfahren zur Vermessung eines Linsensystems, insbesondere eines Auges

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012116807A1 (fr) 2011-03-03 2012-09-07 Optocraft Gmbh Procédé et dispositif de mesure de la topographie de l'oeil

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102012019469A1 (de) 2012-09-28 2014-04-03 Carl Zeiss Meditec Ag Verfahren zur Realisierung von OCT- und sonstigen Bildaufnahmen eines Auges
DE102015009642A1 (de) * 2015-07-24 2017-01-26 Carl Zeiss Meditec Ag Verfahren zur Bestimmung der Topografie der Kornea eines Auges

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030038921A1 (en) 2001-03-15 2003-02-27 Neal Daniel R. Tomographic wavefront analysis system and method of mapping an optical system
DE10342175A1 (de) 2003-09-12 2005-04-14 Optocraft Gmbh Vorrichtung und Verfahren zur Messung der Oberflächentopographie und Wellenaberrationen eines Linsensystems, insbesondere eines Auges
US20050203422A1 (en) * 2004-02-10 2005-09-15 Jay Wei Optical apparatus and methods for performing eye examinations

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030038921A1 (en) 2001-03-15 2003-02-27 Neal Daniel R. Tomographic wavefront analysis system and method of mapping an optical system
DE10342175A1 (de) 2003-09-12 2005-04-14 Optocraft Gmbh Vorrichtung und Verfahren zur Messung der Oberflächentopographie und Wellenaberrationen eines Linsensystems, insbesondere eines Auges
US20050203422A1 (en) * 2004-02-10 2005-09-15 Jay Wei Optical apparatus and methods for performing eye examinations

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012116807A1 (fr) 2011-03-03 2012-09-07 Optocraft Gmbh Procédé et dispositif de mesure de la topographie de l'oeil

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