Optical coherence tomography assisted surgical apparatus

Abstract: Ophthalmologic surgical microscope which is combined internally with an optical coherence tomography ("OCT") apparatus wherein auto-focusing is provided by driving a motorized internal focusing lens of the ophthalmologic surgical microscope with a signal output from the OCT apparatus. An embodiment of the inventive ophthalmologic surgical microscope includes: (a) an optical coherence tomography ("OCT") apparatus; (b) a beamcombiner for internally coupling output from the OCT apparatus into the ophthalmologic surgical microscope; and (c) a motor for moving an internal focusing lens of the ophthalmologic surgical microscope in response to a signal from the OCT apparatus, whereby the ophthalmologic surgical microscope is auto-focused.

Description: Technical Field of the Invention The present invention relates to optical coherence tomography ("OCT") assisted surgical apparatus such as: an ophthalmologic surgical microscope which includes an OCT unit for auto-focusing on the posterior intraocular lens capsule for use, for example, in cataract surgery and for performing in-line corneal topography measurements for use, for example, in refractive surgery. Background of the Invention As is well known, cataract surgery is an ophthalmologic surgical procedure for removing an opaque intraocular lens from an eye. In accordance with this surgical procedure, after the intraocular lens is removed, an artificial intraocular lens needs to be implanted to recover the patient's vision. It is desirable for an ophthalmologic surgical microscope that is used during the surgical procedure to have a capability of auto-focusing on the intraocular lens capsule during the surgical procedure, which capability is especially important after a majority of the opaque intraocular lens has been removed. After a majority of the opaque intraocular lens has been removed, small amounts of cataract residue may remain on the optically transparent intraocular lens capsule --because the intraocular lens capsule is transparent, such residue is difficult to see. As is known, it is important to completely remove such residue because any residue left on the intraocular lens capsule will serve as a nucleus of a new cataract. Present apparatus for auto-focusing an ophthalmologic surgical microscope, such as a prior art apparatus disclosed in U.S. Patent No. 5,288,987 issued February 22, 1994, are based on detecting and measuring the intensity of light scattered from an object. However, such apparatus for auto-focusing are disadvantageous because it is difficult to focus on an optically transparent medium such as the posterior intraocular lens capsule since reflection therefrom is specular and weak. OCT apparatuses coupled to a biomicroscope or endoscope are described in "In vivo retinal imaging by optical coherence tomography" by E.A. Swanson et al., Optics Letters, vol. 18, no. 21, pages 1864-1866 and in WO 92/19930. In light of the above, there is a need in the art for an ophthalmologic surgical microscope which can auto-focus on the posterior intraocular lens capsule for use in cataract surgery. As is well known, refractive surgery is a surgical procedure that has, as its primary objective, correction of an ametropia by making incisions in a cornea to change the refractive power of the cornea. Surgical manipulation of corneal shape requires an accurate and precise method of measuring anterior corneal curvature from apex to limbus. At present, measurement of curvature of the center of the cornea is commonly made using a keratometer and, for more precise measurements of corneal topography, it is common to utilize photokeratoscopy or videokeratoscopy. Current corneal topography measurement apparatus are mostly Placido-disc-based videokeratoscopes. In such an apparatus, a series of concentric rings are configured on a cone-shaped housing so that an image reflected from the cornea is virtually flat in space. Then, the configuration of the rings is analyzed to determine the corneal topography. A prior art apparatus of this type has been described in an article entitled "New Equipment and Methods for Determining The Contour of the Human Cornea" by M. G. Townsley, Contacto , 11(4), 1967, pp. 72-81. Such videokeratoscopes have the following disadvantages: (a) due to the small radius of the cornea (~8 mm), a limited number of rings can be resolved on the cornea (normally, the contour which can be measured is restricted to an area which ranges from 0.8 to 11 mm in diameter on the cornea); (b) no information can be obtained between the rings; and (c) due to use of rings, in-line measurement is very difficult when used in conjunction with an ophthalmologic surgical microscope. An article entitled "Accuracy and Precision of Keratometry, Photokeratoscopy, and Corneal Modeling on Calibrated Steel; Balls" by S. B. Hannush, S. L. Crawford, G. O. Waring III, M. C. Gemmill, M. J. Lynn, and A. Nizam in Arch. Ophthalmol. , Vol. 107, Aug. 1989, pp. 1235-1239 provides a comparison of these prior art methods and apparatus. Another corneal topography measurement apparatus has been developed recently by PAR Microsystem Co. The apparatus utilizes raster photogrammetry to measure a corneal topography. In this apparatus, a grid pattern is projected onto the cornea. The grid pattern is then viewed and imaged from an offset angle. Finally, corneal elevation at each of the discrete points in the grid pattern are calculated using the image of the projected grid pattern, and information relating to its geometry, . This apparatus is described in an article entitled "Intraoperative raster photogrammetry - the PAR Corneal Topography System" by M. W. Berlin, J. Cataract Refract Surg , Vol. 19, Supplement, 1993, pp. 188-192. Corneal topography measurements suffer in this apparatus because only a limited number of points in the image of the projected grid pattern can be resolved by the image optics. As is further known, since a posterior corneal surface contributes about -14% of total corneal refractive power, in some cases, an anterior corneal topography, by itself, does not provide sufficient information for use in a refractive surgical procedure. For that reason, it becomes even more important to obtain corneal topography measurements with a precision that cannot be provided by current corneal topography measurement apparatus. In light of the above, there is a need in the art for an ophthalmologic surgical microscope which can perform in-line, corneal topography measurements for use in refractive surgical procedures. Recently, a new ophthalmic measurement apparatus, an optical coherence tomography ("OCT") apparatus, has been disclosed which has advantages over the above-described prior art ophthalmic measurement apparatus. An OCT apparatus uses a short coherence light source for range measurements based on the principle of white light interferometry. OCT has been proposed recently for use in several ophthalmologic applications. For example, such proposals have been made in a preprint of an article which has been submitted for publication entitled "Micron-Resolution Imaging of the Anterior Eye in Vivo with Optical Coherence Tomography" by J. A. Izatt, M. R. Hee, E. A. Swanson, C. P. Lin, D. Huang, J. S. Schuman, C. A. Puliafito, and J. G. Fujimoto, 1994, pp. 1-24. The preprint discloses an OCT apparatus which utilizes optical fiber technology and a superluminescent laser diode source, which OCT apparatus is interfaced with a slitlamp biomicroscope for imaging intraocular structures with a spatial resolution of 10-20 µm. The preprint discloses the use of the OCT apparatus to provide direct, micron-resolution measurements of (a) ocular profile dimensions, optical scattering, and structure in the cornea; (b) the anterior angle region; (c) the iris; and (d) the crystalline lens. The preprint further discloses the use of the OCT apparatus to measure: (a) anterior chamber depth, defined as a distance, along the visual axis, from the posterior corneal surface to the lens anterior capsule; (b) radius of curvature of the posterior and anterior surfaces of the cornea; (c) corneal refractive power; and (d) corneal dimensions such as thickness. The preprint still further discloses that the OCT apparatus, using an inexpensive diode laser source and a fiber optic implementation, is compatible with existing ophthalmic instrumentation. Finally, the preprint makes the following suggestions for potential clinical applications of OCT: (a) providing cross-sectional images of the entire anterior chamber for use in elucidating pathologies of the cornea, anterior angle region, and iris and for use in identifying and monitoring intraocular masses or tumors; (b) measuring anterior chamber depth, corneal curvature, and corneal refractive power; and (c) providing high resolution images showing corneal thickness variations and the distribution of scattering in corneal stroma for quantitative analysis of corneal pathologies. As is well known, lasers are used in eye surgery for various applications, of which, perhaps the most important are photocoagulation of the retina and photoablation of the cornea. In such applications, laser radiation interacts with ocular tissue and causes structural and topological changes of the tissue. Such applications typically entail monitoring such tissue changes visually on a video monitor by means of a CCD microchip interface or through a binocular eye piece with an ophthalmologic surgery biomicroscope. However, the CCD image of theprior art is limited for two basic reasons. The first reason the CCD image of the prior art is limited is that the CCD image only provides an image of tissue surface. For laser treatment of macular holes, for example, although there is a need to limit tissue coagulation to a well defined area to avoid unnecessary damage of visual functions, there is also a need to limit tissue coagulation in depth to avoid bleeding of the highly perfused coroidal layer. Another example of the need to limit tissue changes in depth is the need to avoid damage of the endothelium layer of the cornea during laser ablation for photorefractive surgery. The second reason the CCD image of the prior art is limited is that it does not provide a quantitative method for controlling tissue change based on laser power, exposure, and spot size. In light of the above, there is a need for an apparatus for use in laser treatment for controlling the extent of tissue change during the laser treatment and for controlling the tissue change based on laser power, exposure, and spot size. Summary of the Invention The present invention is defined in claim 1. An embodiment of the present invention comprises an ophthalmologic surgical microscope which is combined internally with an optical coherence tomography ("OCT") apparatus wherein auto-focusing is provided by driving a motorized internal focusing lens of the ophthalmologic surgical microscope with a signal output from the OCT apparatus. In accordance with one embodiment of the present invention, whenever a particular object in the field of view is interesting, for example, the posterior lens capsule, the OCT apparatus scans the anterior chamber of the eye, along the longitudinal axis of the eye, to provide location information relating to the particular object. Then, the OCT apparatus outputs a location signal to drive the motorized internal focusing lens to auto-focus the ophthalmologic surgical microscope on the particular object. In accordance with another embodiment of the present invention, in-line corneal tomography measurements of the anterior chamber are obtained by using a scanning apparatus, for example, a scanning apparatus comprised of two scanning motors, to provide a raster transverse OCT scan of the cornea, in conjunction with a longitudinal OCT scan. The results of the scans are analyzed by a computer to provide the following data: (a) anterior corneal surface contours, (b) posterior corneal surface contours, and (c) the thickness of the cornea. As one can readily appreciate such contours are three-dimensional contours. These data are used to provide in-line, on-line monitoring of corneal refractive power during a refractive surgical procedure. In accordance with the present invention, embodiments of the ophthalmologic surgical microscope provide eye pieces and a CCD camera for direct viewing during the surgical procedure. Advantageously, since the OCT apparatus is combined with the ophthalmologic surgical microscope internally, the working distance of the microscope objective lens is preserved. Brief Description of the Figure FIG. 1 shows, in pictorial form, an embodiment of the present invention which comprises an ophthalmologic surgical microscope and an optical coherence tomography ("OCT") apparatus; FIG. 2 shows, in pictorial form, a fiber optic embodiment of the OCT apparatus shown in FIG. 1; FIG. 3 shows, in pictorial form, a preferred embodiment of the present invention which comprises an ophthalmologic surgical microscope and an OCT apparatus; FIG. 4 shows, in pictorial form, the chief rays of the OCT beam between the scanning mirrors and the eye for the embodiment shown in FIG. 1; FIG. 5 shows, in pictorial form, the chief rays of the OCT beam between the scanning mirrors and the eye for the embodiment shown in FIG. 3; and FIG. 6 shows, in pictorial form, an example for monitoring and controlling the extent of tissue change during laser treatment. Components which are the same in the various figures have been designated by the same numerals for ease of understanding. Detailed Description FIG. 1 shows, in pictorial form, an embodiment of the present invention which comprises ophthalmologic surgical microscope 100, optical coherence tomography apparatus 200 ("OCT 200"), and video imaging unit 220. As shown in FIG. 1, ophthalmologic surgical microscope 100 is comprised of objective lens 110 which has a long working distance (~200 mm) for focusing on patient's eye 1000 during a surgical procedure. Beamcombiner 120 directs illumination radiation 310 from illumination path 300 and OCT radiation 410 from OCT path 400 toward objective lens 110. As is shown in FIG. 1, beamcombiner 120 is beamsplitter. As is shown in FIG. 1, ophthalmologic surgical microscope 100 further comprises optical magnification changer 130 which is set to a condition suitable for performing a particular surgical procedure (typically there are a number of groups of lenses arranged on a drum for providing varying magnifications such as, for example, 5X, 12X, 20X, and so forth). Radiation impinging upon optical magnification changer 130 is collimated. Ophthalmologic surgical microscope 100 further comprises: (a) relay lenses 140 which take collimated radiation output from optical magnification changer 130 and form an intermediate image of an object, for example, eye 1000; and (b) internal focusing lenses 150 which are used to focus on the intermediate image of the object formed by relay lenses 140 and provide a collimated beam (internal focusing lenses 150 move up and down along viewing path 500 to provide an opportunity for internal focus adjustment). After passing through internal focusing lenses 150, radiation is collimated and beamsplitter 160 couples a portion of the collimated radiation into optical path 600 for obtaining a video image. The video image is obtained by use of video lens 190, CCD camera 195, and video monitor 220. As those of ordinary skill in the art can readily appreciate, although the use of a single CCD camera is shown, it is within the spirit of the present invention that embodiments may be fabricated utilizing two beamsplitters, i.e., beamsplitter 160 and a similarly placed beamsplitter, to provide stereoscopic viewing through two CCD cameras. Lastly, tube lenses 170 focus collimated radiation passed through beamsplitters 160 at an object plane of eye pieces 180. Eye pieces 180 then provide collimated output which is focused by a viewer's eyes. Since the above-described viewing path 500 is binocular, stereoscopic viewing can be obtained. As shown in FIG. 1, illumination path 300 is comprised of: (a) incandescent light source 310; (b) condenser lens 320 for collecting radiation output from light source 310; and (c) image lens 330 for filling the entrance pupil of objective lens 110 with the filament of incandescent light source 310. Beamcombiner 340 combines OCT beam 410 with illumination radiation 310 from illumination path 300. In a preferred embodiment, beamcombiner 340 is a cold mirror beamsplitter, i.e., a mirror which reflects radiation at lower wavelengths, for example, wavelengths less than about 700 nm, and transmits radiation at higher wavelengths, for example, wavelengths higher than about 700 nm. FIG. 2 shows, in pictorial form, a fiber optic embodiment of OCT apparatus 200. As shown in FIG. 2, OCT apparatus 200 comprises CW radiation source 220, for example, a superluminescent laser diode having an output centered substantially at 850 nm. Output from source 220 is coupled into optical fiber 230 and is separated into two beams by 50/50 coupler 240. The output from 50/50 coupler 240 is coupled into optical fibers 250 and 270, respectively. The output from fiber 270 is imaged by lens 280 onto reference mirror 290 and output from fiber 250 is directed to transverse scanning mechanism 260. The output from transverse scanning mechanism 260 is directed to impinge upon an object in a manner to be described in detail below. Then, radiation reflected from the object is coupled back into fiber 250 and superimposed by 50/50 coupler 240 with radiation reflected from reference mirror 290 and coupled back into fiber 270. Superimposed radiation output from 50/50 coupler 240 is coupled into fiber 265. As is known, there is interference between radiation reflected from the object and radiation reflected from reference mirror 290 if the optical path difference is smaller than the coherence length of radiation source 220. Reference mirror 290 is moved with a substantially constant velocity by means which are well known to those of ordinary skill in the art (not shown) and, as a result, the interference is detected as a periodic variation of a detector signal obtained by photodetector 275, the periodic variation having a frequency equal to a Doppler shift frequency which is introduced by moving reference mirror 290 with the constant velocity. The output from photodetector 275 is demodulated by demodulator 285, the demodulated output from demodulator 285 is converted to a digital signal by analog-to-digital converter 295 (A/D 295), and the output from A/D 295 is applied as input to computer 210 for analysis. The interference signal vanishes as soon as the optical path difference between radiation reflected from the object and radiation reflected from reference mirror 290 becomes larger than the coherence length of source 220. As shown in FIG. 1, the output from OCT apparatus 200 over fiber 250 is coupled into OCT path 400, which OCT path 400 includes a transverse scanning mechanism which will described below. As described above, in the embodiment shown in FIG. 1, OCT beam 410 has a wavelength centered about 850 nm and beamsplitter 120 is coated with a dichroic coating so that radiation from OCT path 400 can be continuously scanned during a surgical procedure without interruption of viewing by ophthalmologic surgical microscope 100. In accordance with the present invention, there are two configurations utilized to provide transverse scanning. In the first configuration used to provide transverse scanning, as shown in FIG. 1, scanning mirrors 450 and 460 are orthogonally mounted, galvanometer driven scanning mirrors which are mounted on a pair of motors (not shown) and lens 470 collimates radiation output from fiber 250. The scanning motors are operated under the control of computer 210 in a manner which is well known to those of ordinary skill in the art. In the first configuration, scanning mirrors 450 and 460 are located close to the back focus of objective lens 110. FIG. 4 shows, in pictorial form, the chief rays of OCT beam 410 between scanning mirrors 450 and 460 and eye 1000 in the first configuration. As shown in FIG. 4, back focus 1500 of objective lens 110 is close to scanning mirrors 450 and 460 and the chief rays of OCT beam 410 are parallel to the optical axis in object space, i.e., the region between objective lens 110 and eye 1000. As one can readily see from FIG. 4, radiation reflected from the outer rim of the cornea of eye 1000 will be directed away from a return path to OCT apparatus 200 due to the large angle of incidence of the radiation on the cornea. The second configuration used to provide transverse scanning is illustrated in FIG. 3. As shown in FIG. 3, relay lens 490 is used to transfer the OCT point source from fiber 250 to an intermediate image which is located between scanning mirrors 450 and 460 and scanning mirrors 450 and 460 are located very close to the back focus of scanning lens 480. FIG. 5 shows, in pictorial form, the chief rays of OCT beam 410 between scanning mirrors 450 and 460 and eye 1000 in the second configuration. As shown in FIG. 5, the chief rays of the scanning beam are parallel in relay space, i.e., the space between scanning lens 480 and objective lens 110 and the chief rays are focused close to the center of curvature of the cornea of eye 1000. Since OCT beam 410 is focused at the center of curvature of the cornea, it is normal to the surface thereof and the reflected beam is retroreflected into the return path. As a result, in the second case, the maximum signal strength is obtained everywhere on the cornea and the embodiment shown in FIG. 3 is the preferred embodiment of the present invention. In accordance with a first aspect of the present invention, OCT unit 200, in accordance with instructions from computer 210, scans the anterior chamber of eye 1000, along the longitudinal axis of the eye, in a manner known in the art to provide location information relating to a particular object, for example, the posterior lens capsule. This object is one of several layers in the anterior chamber of the eye. Each maximum of the OCT signal reflected from these layers corresponds to a specific layer. The reference mirror scans a distance of the order of several centimeters corresponding to the focusing image of internal focusing lens 150 in the object space of the surgical microscope. The zero positon of the reference mirror corresponds to a nominal distance of the object plane from objective lens 110. Computer 210 detects each of the OCT signal maxima and registers the respective positions of the reference mirror. This information gives the distance of each layer from objective lens 110. Each maximum corresponds to a specific layer. The number of layers is unique for the specific circumstances of cataract surgery. The number of the layer of interest can be determined by the operator and is part of the initial configuration of the computer program. Usually, the posterior lens capsule is the layer of interest. Then, computer 210 positions internal focusing lenses 150 (by sending an appropriate signal to motor 155) so that the corresponding focal plane of the surgical microscope, depending on the position of internal focusing lenses 150, is at the position of the posterior lens capsule identified with the said procedure. In addition, the output from computer 210 may be displayed on CRT 211 wherein various features obtained by the OCT longitudinal scan are made apparent by a display, for example, of signal strength as a function of location. Since the position of the posterior ocular lens is well known, it can readily be identified by a trained observer. Then, user input to computer 210 by means, for example, of keyboard 212 and/or a mouse (not shown), is used to specify a range of locations of the longitudinal scan to use for auto-focusing. In response to the user input, computer 210 chooses a location which produces a signal strength maximum within the specified range of locations and determines an appropriate position of internal focusing lens 150 to achieve proper focus on the location providing the signal strength maximum. Then, computer 210 sends an appropriate signal to motor 155 to move internal focusing lens 150 to the appropriate position. In accordance with a second aspect of the present invention, OCT unit 200 and scanning mirrors 450 and 460, in accordance with instructions from computer 210, provide a raster, transverse OCT scan of the cornea in conjunction with a longitudinal OCT scan, all in a manner known in the art. The results are analyzed by computer 210 to obtain corneal topography measurements such as: (a) anterior corneal surface contours, (b) posterior corneal surface contours, and (c) the thickness of the cornea. As one can readily appreciate such contours are three-dimensional contours. These data are used to provide on-line monitoring of corneal refractive power during a refractive surgical procedure. In one embodiment of this aspect of the present invention, thresholds are input to computer 210 for the purpose of identifying signals maxima corresponding to predetermined surfaces in the chamber of the eye. Then, computer 210 makes a correspondence between signals having levels above the maxima with the predetermined surfaces and captures the spatial coordinates of the surfaces in space from the longitudinal scan position and from the position of the OCT beam in the raster scan. These values in space are stored in computer 210. The thickness of the cornea is determined from the spatial difference between signal peaks produced by the posterior and anterior corneal surface during a longitudinal scan and the well known optical properties of the cornea, such as, for example, index of refraction. When the raster scan is completed, computer 210 performs a fit of the spatial coordinates of the surfaces to provide posterior and anterior corneal surface contours. As is well known to those of ordinary skill in the art, the surfaces of the cornea are not spherical and, as a result, the surfaces may be described by a set of curvatures, which set will be referred to as a curvature distribution. The surface contours are utilized to determine measures of the curvatures in the curvature distribution of the posterior and anterior surfaces of the cornea and, from them, a measure of corneal refractive power.

Claims: Ophthalmologic surgical apparatus which comprises: an ophthalmologic surgical microscope (100) comprising a moveable internal focusing lens (150); an optical coherence tomography (OCT) apparatus (200) for providing detection signals corresponding to light reflected from a particular layer in the eye (1000); means for internally coupling optical output from the OCT apparatus into the ophthalmologic surgical microscope; and analysis means (285, 295, 210) for analyzing detection signals output from the OCT apparatus characterized in that the internal focusing lens (150) is moved in response to the analyzed detection signals output from the OCT apparatus, whereby the ophthalmologic surgical microscope is auto-focused so that the microscope (100) focuses at the position of the particular layer of the eye (1000). The ophthalmologic surgical apparatus of claim 1 wherein the means for internally coupling comprises: raster scanning means (450, 460) for raster scanning optical output from the OCT apparatus; relay lens means (490) for transferring the optical output from the OCT apparatus to an intermediate image which is disposed within the raster scanning means; and scanning lens means (480) for transferring the intermediate image to an objective (110) of the ophthalmologic surgical microscope wherein the intermediate image is located close to the back focus of the scanning lens means. The ophthalmologic surgical apparatus of claim 2 wherein the scanning lens means is disposed so that chief rays of the scanned output from the raster scanning means are substantially parallel between the scanning lens means and an objective lens of the ophthalmologic surgical microscope. The ophthalmologic surgical apparatus of claim 3 wherein the raster scanning means comprises orthogonally mounted mirrors. The ophthalmologic surgical apparatus of claim 2 wherein the analyzing means comprises: means: (a) for causing the OCT apparatus to scan an object along a longitudinal axis; (b) for examining the detection signals output from the OCT apparatus; and (c) for sending an auto-focus signal to motor means for driving the internal focusing lens of the microscope. The ophthalmologic surgical apparatus of claim 5 wherein the examining means comprises: (a) means for displaying the detection signals; (b) means for receiving user input; and (c) means, in response to the user input, for sending an auto-focus signal to the motor means. The ophthalmologic surgical apparatus of claim 5 wherein the analyzing means further comprises means for detecting one or more maxima of the detection signals output from the OCT apparatus and for sending the auto-focus signal to the motor means in response to at least one of the one or more maxima. The ophthalmologic surgical apparatus of claim 7 wherein the analyzing means further comprises means for determining the distance between the one or more maxima. The ophthalmological surgical apparatus of claim 1, further comprising raster scanning means for raster scanning optical output from the OCT apparatus; and analysis means for (a) causing the OCT apparatus to scan a chamber of an eye along a longitudinal axis; (b) analyzing detection signal output from the OCT apparatus; and (c) providing a contour map of surfaces of the chamber. The ophthalmologic surgical apparatus of claim 9 wherein the analysis means for analyzing detection signals comprises means: (a) for detecting one or more maxima of the detection signals; (b) for associating the one or more maxima with one or more surfaces of the chamber; and (c) for providing contour maps of the one or more surfaces. The ophthalmologic surgical apparatus of claim 10 wherein the analysis means further comprises means for determining a distance between at least two of the one or more surfaces. The ophthalmologic surgical apparatus of claim 10 wherein the analysis means further comprises means for determining a curvature distribution which characterizes at least one of the one or more surfaces. The ophthalmologic surgical apparatus of claim 10 wherein the analysis means further comprises means for displaying the contours.

Inventors: HELLMUTH THOMAS DR, WEI JAY, HELLMUTH, THOMAS, DR., WEI, JAY
Applicants: ZEISS CARL, ZEISS STIFTUNG, CARL ZEISS, CARL-ZEISS-STIFTUNG
Application year: 1995
Main classification: G02B21
IPC codes: G01B9, G02B21, A61F9, A61B3, A61B18