SCANNING LASER OPHTHALMOSCOPE OPTIMIZED FOR RETINAL MICROPHOTOCOAGULATION

Abstract: A combination of scanning laser ophthalmoscope and photocoagulator expands the range of clinical applications of the conventional scanning laser ophthalmoscope, being able of simultaneous imaging and microperimetry with the delivery of therapeutic laser applications to the retina in a preferred non-contact mode. The device, including a therapeutic laser source, optic-mechanical Maxwellian view coupling, Maxwellian view control, and real-time electronic registration of the therapeutic beam location, permits precise positioning and dosage of the retinal applications. Additional safety mechanisms include concurrent temperature measurement of retinal application and shutter activation based on digital image processing techniques.

Description: Patent Application for a SCANNING LASER OPHTHALMOSCOPE OPTIMIZED FOR RETINAL M CROPHOTOCOAGULATION Background-Cross Reference to Related Applications The invention uses the "Modified scanning laser ophthalmoscope for psychophysical applications" of United States Patent n Q 5,568,208, issued October 22, 1996, and is related to United States Patent N B 5,543,866, issued August 6, 1996, entitled "Scanning laser ophthalmoscope for binocular imaging and functional testing" . Background-Field of Invention This invention relates generally to instruments for examining the eye and specifically to an electro-optical ophthalmoscope for analyzing retinal function and assisting retinal microphotocoagulation. Background-Description of Prior Art The ophthalmoscope is well known as an important aid for studying and examining the eye, and in particular, the fundus or retina of the eye. As a result of great interest in preserving man's eyesight, ophthalmoscopes of various constructions have been built and used. The latest version of the ophthalmoscope, a scanning laser ophthalmoscope (SLO) , is particularly appealing because of its unique capability of combining the visualization of the retina or eye fundus with certain psychophysical testing procedures such as the study of preferred retinal loci of fixation (PRLs) , potential acuity measurements, and microperimetry . With the scanning laser ophthalmoscope, a unique, precise correlation between retinal anatomy and function can be established Different stimuli, used in visual psychophysics, can be projected onto the fundus with the help of the scanning laser ophthalmoscope. Overlay graphics are then used to display some stimulus characteristics such as size, location, and intensity on the fundus image m real-time Detailed functional mapping of the fundus is thereby possible Such retinal function mapping is now known to be very helpful to the retinal surgeon when planning therapeutic laser to the retina. These laser applications have been until now delivered to the retina with a different instrument This implies that simultaneous psychophysical testing or even the injection of diagnostic angiographic dyes such as fluorescem or mdocyanm green during the laser treatment is impossible U.S. patent N 2 4,213,678, issued September 29, 1980, discloses a scanning laser ophthalmoscope for the purpose of simultaneously diagnosing and treating retinal disease using two different intensity levels of the scanning laser beam One intensity range can be used for monochromatic imaging, angiographies or psychophysical testing while a much higher level of the same laser beam or a different colmear scanning laser beam is useful for thermal retinal coagulation This novel approach however is not ideal because of the technical difficulties in implementing safety controls for such scanning therapeutic laser beam, the difficulty m modulating the scanning laser beam over a range from non-coagulating to coagulating powers at video rate, and the non-thermal complications of a very high intensity pulsed laser beam at video rate It is nevertheless possible and evident for s/he skilled in the art, to combine optically the scanning laser ophthalmoscope with a traditional non-scanning continuous laser source for the purpose of retinal photocoagulation. This combination, as described on multiple occassions in the prior art, is exemplified by the combination of a traditional slitlamp or indirect binocular ophthalmoscope with a therapeutic laser source These combinations are typically provided with an aiming laser beam that is colmear with the therapeutic laser beam, a focussing device, a micro-manipulator for positioning the therapeutic laser beam onto the desired retinal location, and a combination of safety shutters and filters that interrupts the photocoagulatmg laser in case of malfunctioning of the instrument Also, as proposed before, an analysis of the reflection and backscatter of an appropriate aiming beam immediately before the application of the therapeutic laser to the retina, can reveal localized differences m retinal absorbance for a particular wavelength This in turn can be useful for the adjustment of the laser power in order to obtain consistent burns of equal intensity on the retina in different locations (Pomerantzeff et Al . ) . It has also been proposed to use advanced image recognition and tracking to automatically place the laser applications on the retina where desired by the surgeon However, until the present invention, all coagulating ophthalmoscopes, including the scanning laser ophthalmoscope, have been limited when consistent minimal intensity laser applications on the retina are desired. The thermal changes caused by such laser applications are very difficult if not impossible to visualize and therefore the desired endpomt of the application is often exceeded. This is even accentuated by the fact that the surgeon, upon recognizing the minimal changes on the retina, will need a minimal reaction time delay to stop the therapeutic laser, and during this interval the laser continues to deliver heat to the retina. Also, it is difficult to avoid re- application of laser to the same area or too close to another laser application because of the low visibility of the effects of a minimal application during the current treatment session or at a later session Furthermore, eye movements and changes in the subject's fixation have hitherto limited the accuracy and ease of performing either high resolution microperimetry or applying microscopic laser to the fundus. In the case of microperimetry, a manual "repeat trial on error" presentation of a stimulus to one specific retinal location is possible, using fiducial landmarks as a guide. The procedure however until now corrects the position after the stimulus has been presented. This approach cannot be used when so called adaptive psychophysical testing strategies are involved. They require correction of the subject's changes in fixation immediately before presentation of the stimulus. "Repeat-trial-on-error" is obviously not possible in the case of laser applications. Since the reaction time of the surgeon may exceed 200 ms, a 100 s application can then be wrongly targeted on the retina in the case of fixation loss In the case of non corneal contact coagulation, the iris may be inadvertently hit for the same reason. The minimal reaction time of the surgeon also explains why it is a dangerous concept to have the instrument combine with digital image processing and automated tracking to decide where to treat, in case of malfunctioning or inaccuracy the wrong applications will be placed before the surgeon can even intervene. Automation would also require a precise mapping of the positioning of the micro- manipulator to the fundus coordinates. This coupling is very difficult to realize mechanically, difficult to calibrate and prone to error. At present there is no constant mapping or linkage between the position of the micromanipulator and the position of the aiming beam or therapeutic beam on the retina in any known combination of ophthalmoscope and photocoagulator As mentioned in the related U.S patent, the optical entrance pupil of the Maxwellian view is even more difficult to control manually since usually no reliable fiducial landmarks m the pupillary area are available to the examiner, both in the case of microperimetry or the therapeutic application of laser. In the case of a preferred non-contact photocoagulation technique 1 e without using a corneal contactlens, it is desirable to keep the therapeutic beam within the anatomical pupil to avoid hitting the iris. In microperimetry with the ΞLO, variations m the entry pupil of the Maxwellian view will introduce a potential Stiles-Crawford effect and variations in threshold measurements due to unequal media absorption or scatter in different optical paths through the ocular media. Lastly, in order to use microperimetry under desirable minimal background conditions, a large dynamic range of stimulus intensity to surrounding background is required. Simple one-dimensional modulation, whether acousto-optical or through electrical amplitude modulation of diodes, limits this dynamic range Objects and Advantages The principal object of this invention is therefore to provide a single instrument, a scanning laser ophthalmoscope, with the capability of concurrent optimized microperimetnc testing, angiographic testing, and preferably non-contact microphotocoagulation with the necessary controls for the dosage and optimal placement of microscopic laser applications Dosage can be monitored in real-time through continuous measurement of the heat buildup at the photocoagulation location with an appropriate near infra-red linear detector within the scanning laser ophthalmoscope. The laser application process can then be modified according to the retinal temperature that is measured Digital image processing techniques are used to obtain optimal placement of the laser applications In general this is accomplished by registering the localization of the aiming beam or therapeutic beam in the video raster Feature detecting algorithms are used for this purpose on either the thermal or optically filtered visible light video images m real-time during the laser application. The therapeutic laser beam can be interrupted if e g. the current localization of the application no longer matches with a preselected localization on the monochromatic real-time video image of the retina, as determined by digital image processing techniques such as normalized gray scale correlation With other words, it is now possible with the instrument to deliver very mild consistent retinal laser applications, mostly involving the photoreceptor - RPE complex at predetermined locations and to store these positions as overlay graphics on a reference image of the fundus This precise mapping can then be re-used for outlining further applications without the risk of retreating unrecognizable previous locations or putting the applications to close to each other. The mapping can also be used in the long term microperimetnc evaluation of the impact of laser applications Several other diverse advantages of the device can be envisioned In the art of retinal microphotocoagulation it becomes possible to diagnose and treat with the same instrument in an unprecedented manner. It is possible to perform laser applications and then immediately assess the results with monochromatic or angiographic viewing of the retina, adjusting the treatment if necessary. Microperimetry can instantly verify whether photoreceptors have been destroyed by the laser application; this location can also be marked automatically on a master image for future reference. In general, the infra-red visualization of the fundus and the possibility of projecting a visible fixation cross within the laser raster enhances the patient's cooperation. Also, the therapeutic laser delivery system can be made non-contact, especially with the help of concurrent imaging of the anatomical pupil. This concurrent imaging allows centering of the therapeutic laser beam and prevents accidental iris involvement in the laser applications. In the 20 degree field of view of the instrument large magnification is achieved on a video monitor, resulting in a high accuracy and relative ease of placement of small laser applications. Most importantly, the thermal control and automated recognition of the laser application loci permit the creation of non-visible closely spaced minimal intensity applications particularly aimed at destroying the photoreceptor cells while leaving the underlying nourishing choriocapillary and choroid layers fairly intact. The retinal pigment epithelium will then have a better chance to recuperate as well. It is possible to preselect a pattern of laser application loci on the retina. However, the retinal surgeon remains in control of where and when the applications are made since it is s/he who will control the micromanipulator and activation switch. Software such as normalized gray scale correlation will only interrupt or disable the therapeutic laser beam, faster than the surgeon's reaction time, in case of misalignment or overdosage. Unlike proposed automated photocoagulation these are complimentary safety features that will not cause harmful effects if wrongly activated. U.S. patent 5,543,866 discusses the importance of a binocular evaluation of retinal function. Being able to fixate with corresponding preferred retinal loci in both eyes is a major advantage in low vision rehabilitation. At the other end of the spectrum, pseudocentral fixation, is the most significant impediment to visual re-habilitation. These and other important observations play a role in measuring potential visual acuities and planning laser applications to the retina of patients with age related maculopathy. It has further been demonstrated in microperimetry that absolute retinal thresholds correlate with the amount of photopigment that is present in the retina. Stiles-Crawford functions can reveal the general orientation and degree of alignment of the photoreceptors. Abnormalities in above mentioned parameters measure damage to the retinal pigment epithelium-photoreceptor complex in the retina and this information is useful in the planning and follow-up of laser applications as outlined in Application Ser. N- 08/207,385. Well-known adaptive strategies have been optimized for use with the scanning laser ophthalmoscope to measure the above mentioned parameters of vision These strategies measure precisely visual acuity or retinal sensitivity on the retina and specifically benefit from a combined two-dimensional acousto-optical and laser diode modulation to increase the dynamic range of stimulus to background intensity, correction of AOM delay, the use of non-destructive graphics overlays, combined infra-red and visible wavelength illumination of the retina, correction algorithms for fixation shifts before stimulus presentation, and recognition of the entry pupil of the Maxwellian view with an automated, motorized x- y-z feedback control of the location of this entry pupil The combination of such enhancements has never been realized or proposed prior to the invention and is an explicit object of the invention Further objects and advantages of the invention will become apparent from a consideration of the drawings and ensuing description Description of the Drawings FIG 1 is a diagrammatic representation, illustrating the components of the scanning laser ophthalmoscope, optimized for microphotocoagulation Five subparts can be distinguished (1) A scanning laser ophthalmoscope proper, with multiple lasers, detectors, and AOM (2) A motor block component capable of moving the SLO in the xyz directions (3) A therapeutic laser with optical linkage to the scanning laser ophthalmoscope (4) The Maxwellian view control components, part of aforementioned U S. patent (5) Human interface elements consisting of monitors the eye with retina and a pushbutton FIG 2 illustrates the relation between the different electronical components of the scanning laser ophthalmoscope-microphotocoagulator The overlay frame grabber card has an input interface, frame memory, display interface and CPU interface Besides the OFG card(s), the host bus acccomodates a I/O card for interpreting the pushbutton, and interaction with the control circuit of the therapeutic laser Also an interface card for controlling the motors is present The SLO electronics interface shows the synch generator detectors AOM circuitry and direct electrical modulation of diode laser The following circuits are represented (1) video-m pathway (2) Video-out pathway (3) the synchronization pathway and genlockmg of other components of the system including adc , dac, detectors (4) The TTL circuit to and from the therapeutic laser controlling the shutter and communicating activation of the therapeutic beam (5) The circuit serving the different motors FIG 3 details the opto-mechanical link between therapeutic laser and scanning laser ophthalmoscope . FIG 4 illustrates the optical ray tracing of either diagnostic or therapeutic beam. Parallel rays in general illuminate the same retinal location but from a different angle. Non-parallel rays will sweep across the fundus. The Gaussian beam measures about 0.5 mm at the pupillary plane and tapers to about 12 micron on the retina plane. Ray tracing has been simplified. FIG 5 illustrates the effect of a translational shift in fixation. Fixation cross position remains unchanged. Point P on the retina shifts to P'. This is in accordance with the movemement of the small search window within the larger reference window. The search window contains a gray scale feature that can be used in normalized gray-scale correlation. FIG 6 illustrates the adaptive testing algorithm combining an UDTR transformed response staircase with a four alternative forced choice procedure. FIG 7 illustrates the correspondance between the bitlevels of the frame grabber board and the power output at the exit aperture of a 129 pixel square. 26 levels have been measured to plot the polynomial regression curve from which all other bitlevels can be derived. Fig 8 illustrates the adaptive testing algorithm, commonly called PEST procedure, to derive at a final bitlevel, regardless of the stimulus spacing. Reference Numerals in Drawings 10 Prefocussed Gaussian beam of laser light 12 Posterior pole of the eye 14 Scanners, including polygon and galvanometer 16 Maxwellian view of the illuminating path 18 Reflected and backscattered light from the eye 20 Beam separator 22 Pinhole at the retinal conjugate plane 24 Avalanche photodiode 26 Video display monitor 28 Diode infra-red 780 nm laser 30 Amplitude modulation of diode laser 32 He-Ne red 632 nm laser 34 Pair of adjustable linear polarizers 36 Graphics on the retina, visible as overlays 38 Acousto-optic modulator 40 Electronic circuitry of scanning laser ophthalmoscope 42 Distribution of common synchronization to different components 44 Encasement 46 Beamsplitter 48 Superlummescent 880 nm LED 50 Nose, cheeks and eyebrows 52 Cover of scanning laser ophthalmoscope 54 Slanted window of scanning laser ophthalmoscope with diaphragm 56 CCD videocamera with objective 60 Chmrest 62 Vertical movement mechanism using stepper motor 64 Horizontal two dimensional movement mechanism using stepper motors 66 486/33 mHz CPU with overlay frame grabber board 68 Additional overlay frame grabber board 70 Entrance pupil laser beam as overlay on image of anatomical pupil 72 Partial infrared barrier filter 74 Additional graded neutral density filter and diaphragm 80 Therapeutic laser beam 82 Transmission optics 84 Therapeutic coagulator 86 Aiming beam 88 Collimator-telescope 90 Variable aperture 92 Safety filter (s) 94 Electronic interface therapeutic laser 96 I/O link 98 Pushbutton for psychophysical purpose 100 Adjustable mirror hinges 102 Positioning device 104 Framework 106 Support arc 108 Projecting mirror 110 Pivot point of therapeutic laser beam 112 Micromanipulator 114 Second avalanche photodetector with filters 116 Alternative third extended IR sensitive avalanche photodetector Description and operation of an embodiment A typical embodiment of the scanning laser ophthalmoscope optimized for microphotocoagulation is illustrated in Fig 1 through Fig 3, Fig 4 through Fig 8 illustrate a method of operation of the instrument The principles of scanning laser ophthalmoscopy are described in detail in the prior art Features of the scanning laser ophthalmoscope relevant to the invention are further discussed I THE SCANNING LASER OPHTHALMOSCOPE A prefocussed Gaussian beam of laser light, 0 5 mm in diameter 10, is further focussed by the eye optics to aboutabout 12 μ in diameter at the retinal plane, and is scanned over the posterior pole of the eye 12 m a sawtooth manner with the help of scanning mirrors, currently a polygon and galvanometer 14 Both fast horizontal 15 KHz and slower vertical 60 Hz deflections of the flying laser spot are at standard video RS-170 rates and create the rectangular laser beam raster that is seen by the subject. A Maxwellian view 16 is used m the illuminating portion of the scanning laser ophthalmoscope- the pivot point of the scanning laser beam varies minimally during scanning and is optimally situated in the iris plane with an average waist of less than 1 mm Typically a rectangular area of 0 5 cπr on the retina is illuminated This corresponds to a field of view of 40 degrees in diagonal or 32.7 degrees horizontally by 23.4 degrees vertically The field of view can be changed from 40 to 20 degrees by switching optical components In the 20 degree field of view, the pivot point of the Maxwellian view is less variable in position during scanning, but wider in diameter at the entrance point of the Maxwellian view In confocal viewing the focussing I e positioning of the depth of the waist of the Gaussian beamthen becomes very critical to the point that it is possible to measure refraction for psychophysical purposes Astigmatic errors unfortunately cannot yet be compensated with the optics of the instrument itself This would be easy to accomplisch by incorporating a rotation dial of cross-cylinders Also in the 20 degree field of view, it is more difficult to work around focal scattering or absorbing elements in the ocular media Separate calibrations are necessary for the 20 or 40 degree field of view in psychophysical applications It is important to understand that the observer will not see a flying spot but rather a rectangle filled with thin horizontal stripes because of the temporal summation characteristics of the visual system The reflected and backscattered light from the eye 18, now filling the pupil is descanned over the same mirrors, separated 20 from the illuminating beam and passed through a pinhole 22 at the retinal conjugate plane before reaching a fast and sensitive avalanche photodiode 24. This confocal detection is essential for obtaining high contrast pictures of the retina with infra-red illumination. It is accomplished by eliminating stray light at the pinhole Non- confocal viewing modalities, also called dark-field, indirect or Tyndall imaging, are obtained by the insertion of a central stop instead of the pinhole 22 or off-axis illumination of the retina. The amount of light on the photodetector is translated into a voltage that modulates the intensity of an electron beam on the visual display cathode ray tube monitor 26 The electron beam moves synchronically with the scanning laser beam and a real-time video image of the fundus is likewise created on the display monitor. Two laser sources are aligned to illuminate the retina. The two lasers serve a different purpose. A high intensity diode infra-red 780 nm laser 28, electrically modulated 30 and vertically polarized, is nearly invisible to the subject. It produces the retinal image on the display monitor. A colmear low intensity He-Ne red 632 8 nm red laser 32, modulated with a pair of adjustable linear polarizers 34 and horizontally polarized, is visible to the eye It is used to draw psychophysical stimuli 36 in the laser raster for projection onto the retina These stimuli are created by amplitude modulation of the laserbeam at video rates as the red light passes through an acousto-optic modulator 38 The acousto-optic modulator is driven by a standard video source, usually a computer overlay frame grabber card that contains the graphics information This graphics generator is genlocked to the crystal clock of the electronic circuitry 40 Master timing signals are derived from the spinning polygon. It is important to understand the reason for using at least two different lasers. The scanning laser ophthalmoscope is very light efficient about three orders of magnitude less light is necessary to visualize the fundus when compared with conventional ophthalmoscopes However this light is still orders of magnitude the amount used for typical psychophysical testing The problem is solved by using a 780 nm laser with sufficiently high output and for which the silicon detector of the scanning laser ophthalmoscope, but not the eye, is most sensitive, in combination with a low intensity 632 nm laser, for which the human eye is sensitive but insufficient for visualizing the fundus This explains also why the stimuli which are perceived by the subject are usually not visible in the retinal picture, unless very bright The exact position and characteristics of the stimuli can however be shown in real-time on the retinal image w th the help of computer overlays as all image video out of the scanning laser ophthalmoscope, scanners, and graphics video into the acousto-optic modulator are synchronized to the same crystal clock 42 II LASERS, MODULATION AND DETECTION IN THE SCANNING LASER OPHTHALMOSCOPE In fluorescein angiography with the scanning laser ophthalmoscope, a 632 nm He-Ne laser is usually combined with a 488 nm laser that replaces the functions of the 780 nm laser described above. The 488 nm argon laser is used for excitation of the fluorescein molecules. A 500 nm barrier filter with no pinhole at the retinal conjugate plane is used to separate the backscattered excitation light from the fluorescent light. In indocyanin green angiography with the scanning laser ophthalmoscope, a 780 nm diode laser is kept for excitation of the indocyanin green molecules. A 800 nm barrier filter with no pinhole at the retinal conjugate plane is then used to separate the backscattered light from the fluorescent light. With a prism, 514 nm can be isolated from the argon laser. Many wavelengths can now be produced with a diode laser. Additional beam conditioning is necessary with these lasers. For example, the diode 780 nm laser 28 can be replaced by a diode laser of longer wavelength, 904 nm. For every 10 nm increase in wavelength of the diode laser beyond 670 nm, the efficiency for stimulating the retina, will be reduced to one half. This is useful in making the infra-red background illumination for visualizing the retina on the display monitor even less visible to the subject and this is required for measuring absolute thresholds on the retina. Also longer wavelengths will produce different monochromatic images that may yield useful clinical information. The use of two infra-red lasers in combination with a visible wavelength is an option for binocular scanning laser ophthalmoscopy . In this embodiment each infra-red wavelength will be delivered to one eye and the returned light will be directed to a separate detector. The use of multiple detectors and multiple laser sources has been described in the prior art. Appropriate barrier filters are installed accordingly. Surface-emitting quantum-well laser diodes combined with a confocal two-dimensional array detector system, are of increasing interest. This approach will offer the advantages of high packing densities on a wafer scale. An array of up to a million tiny individually modulated cylindrical In 0 2 Ga 0 8 As surface-emitting quantum-well laser diodes with lasing wavelengths in the vicinity of 970 nm and shorter can substitute the traditional laser sources and scanners of a scanning laser ophthalmoscope. This will render the device more compact, less noisy, and less susceptible to mechanical wear and tear. The 632.8 nm He-Ne laser 32 has been incorporated in the scanning laser ophthalmoscope because of its compact and sturdy design. It is however also the wavelength of choice for generating graphics and stimuli. Reasons for this preference are the maximal transmittance and minimal scatter within the transparent media of the eye, a minimal interference with the xanthophyll and hemoglobin pigments, and a typical monophasic cone response when compared with shorter visible wavelengths. These advantages persist if a longer visible wavelength were chosen, e.g. a diode laser at 650 nm. In traditional Goldmann and automated perimeters, stimuli and background illumination are provided by different optical pathways, the lightsource however being the same the advantages of this configuration are twofold First, the background and stimulus fluctuate the same amount as the lightsource is varying m intensity. Second, additional separate modulation of background and stimulus is possible with a neutral density filter and thereby a minimal or zero background with a maximum stimulus as permitted by the light source, is possible Unlike the Goldmann and automated perimeters, stimuli and background illumination are always provided by the same optical path and light source in the scanning laser ophthalmoscope and cannot be further modulated with e.g a separate neutral density filter for each channel. A truly zero background is not possible with either electrical amplitude modulation or acousto-optic modulation and the ratio between stimulus and background has a maximum limit. For acousto-optic modulation, the theoretical limit is 700, 300 is the practical and desired limit but very often only 100 is obtained Incorporating the 650 nm diode laser can expand the dynamic range of stimulus to background illumination intensity by combining in parallel the electrical high-frequency amplitude modulation of the diode with the acousto-optic modulation described before. For this purpose the blue and red output of the overlay frame grabber board are used. The circuitry is easily constructed by s/he who is skilled in the art of electronics This set-up requires the electrical amplitude modulation bandwith of the diode to exceed the video bandwith of the SLO. An easier alternative at present is to combine in parallel fashion two acousto-optic modulators, each of which are controlled by the red and blue video out of the frame grabber board The rise time of acousto-optic modulators can be as fast as 1 ns, bandwith exceeding 40 Mhz The measurement of dark-adapted thresholds , dark-adaptation and Stiles-Crawford functions require a minimal background and sufficiently intense maximum stimulus A dynamic range of maximum stimulus intensity to background intensity of 2 5 log units is acceptable. As mentioned before, the acousto-optic modulator is driven by a standard video source, a computer overlay frame grabber card that contains the graphics information, and is genlocked to the crystal clock of the electronic circuitry A typical example of such a video card is the FG 100-AT or more recently introduced, the OFG card, both available from Imaging Technology Inc , Bedford MA The OFG card is also the essential hardware for alignment and tracking of the pupil or fundus landmarks as described below. Two OFG cards, which are I/O mapped can reside in one CPU, typically equipped with a Intel Pentium microprocessor The OFG board has to provide three basic functions for realizing the different psychophysical testing and imaging procedures with the scanning laser ophthalmoscope: generation of 8 bits graphics, frame grabbing and display of overlays. The different testing algorithms are constructed from an appropriate sequence of software routines The method of microperimetry will be detailed below. The library of basic software routines is, as usual, provided by the board manufacturer. Specific bitlevels of the graphics board, out of 256 possibilities, are combined with appropriate neutral density filter settings placed various positions for approximate and fine tuning of laser light intensities Individual bitlevels are translated into corresponding intensity levels by converting each bitlevel to an analog voltage with the D/A of the graphics board This output voltage is then amplified and off-set by the AOM driver electronic circuit to obtain suitable voltages for modulating the amplitude of a radio-frequency carrier signal The piezo-electric transducer of the acousto-optic-modulator is driven by this signal Acoustic standing waves are created by the piezo-electric transducer The atoms of the crystal then behave as a diffraction grating for the transvers g laser beam The amount of light passing through the diffraction grating as a first-order beam at the Bragg angle, defined by the frequency of the radio signal, is directly proportional to the amplitude of the radio-frequency signal. The time required for the AOM to adjust the intensity after changing bitlevels is called the AOM delay The delay has to be accounted for in calibrating the overlay graphics Inherent fluctuations in the electronics of D/A converter, AOM driver, and laser output will not affect the ratio of light intensities corresponding to any two bitlevels. Short term and long term variations of individual bitlevel intensities exist Short term fluctuations are irrelevant for psychophysics since they are usually smaller than the psychophysical uncertainty and long term variations are neutralized with the help of a radiometer Minimal spatial variations of light intensity also exist within the laser beam raster They are neutralized with either software or a graded neutral density filter. Also a variability in local laser raster geometry has to be taken into account A pincushion or trapezoid deformity of the near rectangular raster is caused by the internal optical configuration of the scanning laser ophthalmoscope. External angular dimensions of graphics are determined with the arctan formula On the retina, equivalent linear distances are calculated using the standard observer's eye of LeGrand with an effective optical radius of 16 7 mm 300 μ on the retina equals 60 external minutes of arc In practice, an uncertainty of about 10 % n absolute s ze is expected because of the metric nonlmeaπties described and the variability in individual eye optics In summary, The laser raster itself is a very unusual for presenting graphics to the retina, graphics are presented multiples of 33 ms, the time interval to draw one complete video frame on the retina Each video frame consists of two interlaced video fields of 16 7 ms and 256 lines, the video fields may overlap during eye movements Within each video field the graphics is composed of discrete pixels and every pixel is illuminated with a Gaussian beam profile n Maxwellian view for only 77 nanoseconds each This is in sharp constrast with the smooth delivery of photons to the retina in conventional Ganzfeld, Newtonian illumination of standard perimeters However the same number of photons arrive on the retina in both illumination systems, but with a completely different spatial and temporal distribution. Under physiologic testing conditions, it has been demonstrated that visual psychophysics is equivalent in both illumination systems III MAXWELLIAN VIEW CONTROL The configuration of Fig 1, 2, and 3 is for use with the Rodenstock Scanning Laser Ophthalmoscope 101 or 102 (Munich, Germany) This configuration is readily adapted for other embodiments of the scanning laser ophthalmoscope by s/he who is skilled in the art The principal optical components for controlling the Maxwellian view of the scanning laser ophthalmoscope-microphotocoagulator are contained in a moulded and closed encasement for the purpose of protection against dust and stray light 44 These components include the beamsplitter 46, optical filters, and illumination source for the anterior segment 48 The encasement is painted matt black on the inside to minimize unwanted scatter, the coating specifically absorbs any reflected therapeutic laser light as described below The encasement is tapered and provides as much sparing as possible for the bodily parts such as the nose, cheeks, and eyebrows of the subject 50 and has three optical apertures The outside finishing matches that of the scanning laser ophthalmoscope 52 to which it is fitted tightly as a clip-on easy to remove if necessary All three apertures are optionally protected by anti-reflection coated glass, centered on the optical axis, and may contain an optical filter as specified below The aperture that is closest to the scanning laser ophthalmoscope measures about 5 by 5 cm, and is parallel with the slanted window of the scanning laser ophthalmoscope at 15 6 degrees 54 This is helpful to eliminate unwanted reflections The front aperture, about 1 5 by 1 5 cm, is facing the subject's eye, vertically at a comfortable distance as to avoid touching the eyelashes The third aperture 2 by 2 cm is superior or inferior, slanted, and faces a CCD monochrome videocamera with objective 56 which is firmly attached to the scanning laser ophthalmoscope An appropriate objective would be the 25 mm 1 4 C mount Cosmicar lens from Asahi Precision Co , LTD Japan with the 5 mm extension tube An appropriate CCD videocamera would be the Sony XC-75 equipped with a 1/2 inch size interline-transfer CCD The IR blocking filter has been removed from th s camera and replaced by a dummy glass The CCD camera can be easily removed and is in a fixed position relative to the encasement, even if the scanning laser ophthalmoscope moves The axis of the CCD camera is vertical and coincides with the optical axis The scanning laser ophthalmoscope with the attachments described can move vertically with the help of a software controlled stepper motor 62 Two other stepper motors realize the horizontal movements of the scanning laser ophthalmoscope on a platform 64. A computer, equipped with one or two OFG cards, mouse, and keyboard control is provided 66, 68. An appropriate interface card controls the three motors of the scanning laser ophthalmoscope One TV monitor displays the eye fundus with graphics overlay using the scanning laser ophthalmoscope 36 Another TV monitor channel displays the anterior segment of the eye, focussed on the iris with the CCD camera 70 It can provide the exact position of the optical entrance pupil of the scanning laser ophthalmoscope as an overlay The monitors, luminous control buttons, and reading light for the examiner are optically isolated from the subject The only light reaching the subject is coming from the reduced-m-size anterior window of the scanning laser ophthalmoscope This reduction is size is provided by a simple black diaphragm It reduces unwanted light from within the scanning laser ophthalmoscope, unmodulated parts of the laser raster, and the horizontal edges of the video-fields that are produced by the horizontal scanning. These edges often have a higher irradiance because of the inertia in the scanning galvanometer mirror With a modification and extension of the scanning laser ophthalmoscope optics it is possible to [1] visualize the posterior pole, retina or fundus of one eye in detail, [2] to project graphics, for example a 8 by 8 pixel square that is brighter than the background in Maxwellian view onto the retina, [3] simultaneously view the anterior segment of the eye on the same or different monitor, focussed on the iris plane and unambiguously demonstrating with the help of overlays the exact position of the laser beam Maxwellian view used to draw the background and stimulus onto the retina, [4] to observe the Maxwellian view entrance pupil of the therapeutic laser beam as desribed in another chapter, [5] all observations do not interfere with each other, the quality of the retinal image does not imply a lower quality of the iris image and the observation of the iris does not interfere with the purpose of psychophysical testing, for example by introducing a bright background, and [6] it is possible to independently of each other move the psychophysical stimulus location or therapeutic laser application location on the retina to any desired position and simultaneously, at will, move the scanning laser ophthalmoscope and entrance pupil of the laser beams within the anatomical pupil of the iris Thereby the point of entry the pupillary plane can be a variable in psychophysical testing or therapeutic application of laser where the retinal location is kept unchanged and also it is possible to fix the entrance pupil while moving the stimulus position or therapeutic location on the retina. In general, this is realized by (1] introducing a beamsplitter to provide two optical paths, one for the scanning laser ophthalmoscope proper and the second for visualizing the anterior segment of the eye; [2] The introduction of a separate illumination source for the anterior segment with appropriate filters to block unwanted light from reaching the CCD camera. [3] Active or passive stabilization of the stimulus on the retinal image, and selection of entrance pupil of the Maxwellian view system [4] The use of overlays with an appropriate graphics and videocard for demonstrating the exact position of the stimulus or therapeutic laser location on the retina, and the exact position of the laserbeams in the anatomical pupil. [5] The ability to move, manually or with the help of stepper motors the scanning laser ophthalmoscope relative to the subject, and the stimulus position or therapeutic location on the retina with the help of a pointing device and computer program. Movement of the scanning laser ophthalmoscope in a frontal plane will cause the rays of the incident laser beams to use a different part of the entrance pupil. This does not cause a significant shift m the position of the focus on the retinal image because the movement will displace the scanning laser beam rays in a parallel fashion, and parallel rays are focussed on the same retinal location. This retinal location will however be illuminated in an oblique fashion and therefore a Tyndall phenomenon can be observed on the monitor, equivalent to the classic dark field microscopy. This is somewhat similar to the use of a central stop instead of a pinhole at the retinal conjugate plane in confocal detection. Angulatmg the entrance laser beams will result in focussing on different retinal locations. The separate illumination source for the anterior segment can be a superlum escent light emitting diode LED, a close relative of the laser IR diode. The SY-IR53L is a Gallium Aluminium Arsenide super-high output infrared emitting diode in a T-l 3/4 package. It produces noncoherent, nonpolarized IR energy at 880 nm. 880 nm produces negligible interference with the psychophysical testing or application of therapeutic laser. The dispersion angle at half power point is 20 degrees This is important to insure a fairly homogeneous illumination of the anterior segment from a short distance. The forward voltage is typically 1.3 V, power dissipation is 20 mA. Therefore a rechargeable NiCd battery pack is ideal to provide several hours of uninterrupted service The radiant power output is at least 3.4 mW/sq.cm, enough to illuminate the entire anterior segment with a single diode. The small package allows a flexible montage of the diode in the encasement. The illumination of the anterior segment and anatomical pupil does not interfere with the fundus imaging The wide angle distribution of the light, angulation of the diode, and a combination of partial barrier filters 72 for the therapeutic laser wavelength, SLO infra-red lasers and IR LED light, together with control of the diaphragm in the objective of the CCD, reduce the interference from excessive backscatter from the different lasers Purk je images of the IR LED light are however useful m tracking of the entrance beam in the iris plane. As an example, the IR barrier filters remove most of the convergent 780 nm light during the testing procedure. An example is the Kodak Wratten gelatin filter 87C with no transmittance for 632.8 nm, 0.5 % for 780 nm and more than 90% for 880 nm Another example is the Kodak Wratten gelatin filter 87 with no transmittance for 632.8 nm, 30% transmittance for 780 nm and more than 90% transmittance for 880 nm. A combination of interference filters with removal of most of the 780 nm and therapeutic laser wavelength is neccessary when using the instrument as as microphotocoagulator These filters can be selectively removed during calibration of the instrument when it becomes necessary to align the pivot area of the Maxwellian beam of 632.8 nm and therapeutic laser beam with an overlay. The calibration is performed by projection of these different laser beams on a piece of paper that is held in front of the scanning laser ophthalmoscope. This calibration is usually very steady since the beamsplitter, CCD camera and scanning laser ophthalmoscope are fixed relative to each other. The CCD camera is optimally sensitive for IR illumination. The crisp image of the anterior segment with the iris, anatomical pupil, and optionally Purkmje images serve as the fiducial landmarks for the manual or automated x-y-z localization of the entrance pupil of the scanning laser ophthalmoscope. It should be stressed that the pivot point of 632.8 nm does not always correspond with the pivot point of 780 nm, and the therapeutic laser source, and lightscatter will make the pivot point area look much larger than it is in reality, especially if higher energies are used. This is in accordance with the fourth power law of light scatter. Also, only a specific part of the visible entrance location is used for illuminating a specific retinal location and will therefore determine the true point of entry of the laserbeams This may be different from the average position of the beam sweeping across the retina In general, the beamsplitter should favor transmission of 632.8 nm, 780 nm, and therapeutic laser light. Any reflected IR or therapeutic laser light, within the encasement, should be effectively absorbed The choice of the dielectric coatings for the beamsplitter 46 depends on the wavelengths used, their polarization status, and the angle of incidence of the laserlight The ideal beamsplitter is nearly non-absorbing and as such the reflectance will be independent of the angle of incidence of the laserlight. The beamsplitter 46 consists of a single plane-parallel glassplate, 5 by 5 cm, with a partially reflecting low absorption dielectric coating on one side The other side has an antireflection coating optimized for the angle of incidence of 45 degrees. This will prevent ghost images appearing on the video display monitor A sample coating is HEBBAR™ (Melles- Griot, Irvine, California). Some beamsplitters are highly polarization sensitive In a particular scanning laser ophthalmoscope, the mfra-red laser has vertical polarization of the E vector, p-plane with regard to the beamsplitter 46. The He-Ne laser has horizontal polarization of the E vector, s-plane with regard to the beamsplitter 46 Often ideal transmission-reflection characteristics can not be realized for all wavelengths involved. The most optimal coating permits a maximum of 780 nm to transmit, a maximum of 632.8 nm to transmit, and most of the 880 nm to reflect The Melles-Gπot , Irvine, California #BTF 001 passes about 50% of the s- polarized 632.8 nm He-Ne light, more than 90% of the p-polarized 780 nm diode IR, and reflects about 20% of the 880 nm mixed polarization IR LED. Two options exist for equalizing within the laser raster the distribution of irradiant power of 632.8 nm light. As explained before, small differences in intensity occur in the scanning laser ophthalmoscope for various reasons The acousto-optic modulator can adjust intensities according to the location where stimuli are presented or the differences in irradiance can be neutralized with a custom build graded neutral density filter 74 The insertion of an optical filter 74 and beamsplitter 46 in the optical pathway reduces the power of the 780 nm laserlight and therapeutic laser light that illuminates the retina and additionally reduces the amount of light collected by the photodetector from the retina It is reasonable to use a laser source that is more powerful. This source is already available in the scanning laser ophthalmoscope for indocyanin green angiography and is easily adapted for use with the scanning laser ophthalmoscope-microphotocoagulator In summary, one useful addition to the scanning laser ophthalmoscope optimized for retinal microphotocoagulation is the addition of a Maxwellian view control mechanism This facilitates preferred non-contact photocoagulation since the scanning laser ophthalmoscope itself is a large instrument and the entrance beam is not easily seen by the surgeon operating the instrument A contact method of photocoagulation would be very difficult to realize because of the inertia of the heavy scanning laser ophthtalmoscope. Abrupt movement of the instrument, however small, can very easily damage the fragile structures of the eye if it is physically connected to the instrument with the help of a contact glass Other advantages w ll be evident from a description of the optical linkage between scanning laser ophthalmoscope and photocoagulat g light source IV PHOTOCOAGULATOR AND LINKAGE TO SCANNING LASER OPHTHALMOSCOPE The benefit of a Maxwellian view control of the therapeutic beam 80 has been discussed. This chapter will describe the optical linkage between therapeutic laser and scanning laser ophthalmoscope, optimized for a non-contact method. Also, the important mechanism will be described by which the scanning laser ophthalmoscope and CPU is made aware of the cartesian position of the therapeutic or aiming laser beam on the retina, i.e. electronic registration of the retinal application location. The disadvantages of using a scanning therapeutic laser beam that would be switched from a low energy to high energy status at the appropriate retinal location (Pommerantzeff , 1980) have been discussed before Therefore, the therapeutic beam 80 should be maintained stationary, and allowed to move between laser applications only, using special transmission optics 82 The coagulator 84 itself is well known in the art, either argon or currently diode laser, having the possibilty of emitting different wavelengths, particular 514 nm Often a second colmear low power aiming beam 86 is provided. Alternatively, the therapeutic beam can serve as an aiming beam at much lower intensity. Also included n the optical pathway are a collimator- telescope 88 and variable aperture 90 for precisely adjusting the shape and size of the Gaussian therapeutic laser beam. An important element of the photocoagulator is one or more safety shutters 92 or filters. A radiometer is build to monitor power output. An electronic interface 94 connects the aforementioned elements with a control panel that is supervised by the surgeon In addition, the combination scanning laser ophthalmoscope-microphotocoagulator has an important I/O link 96, often a combination of TTL circuits, between the control circuits of the therapeutic laser and the host bus of the CPU. This electronic connection can make the CPU aware of when exactly the therapeutic laser is activated and also provides a means for activating the safety shutter under CPU control. Such TTL circuit has previously been described to connect a pushbutton 98 for psychophysical applications to the CPU. The optical connection between the exit aperture of the laser and a positioning device is preferably made by a combination of extendable mirror hinges 100, instead of flexible fiber optics, in order to tranm t a near perfect Gaussian beam of laser light. Non fiber optics permit focussing to a smaller waist of the Gaussian beam with a relatively large diameter entrance optical pupil Precise positioning in depth and small retinal applications are possible w th th s microphotocoagulation technique. A specially constructed positioning device 102 consist of a framework 104 that permits a support arc 106 to slide across. On the support arc is mounted a projecting mirror 108 This mirror can also slide along the arc and reflects the therapeutic laser light from the other mirrors in the transmission optics The two sliding movements allow the mirror to project the therapeutic laser beam perpendicular to a curved surface, e.g. a part of a sphere, such that the therapeutic laser beam will have a pivot point 110 very similar to the pivot point of the Maxwellian view of the scanning laser ophthalmoscope. The mirror mount itself is moved with the help of a micromanipulator 112 that is handled by the surgeon Typically the positioning device is about 100 mm by 100 mm and will fit into an existing scanning laser ophthalmoscope to which it is fixed with support mounts The Gaussian therapeutic laser beam typically has an effective 0.5mm to 2mm diameter (1/e 2 } Power output is m the mW range, I e. more than 1000X the output of the diagnostic scanning beams. The beam is prefocussed by the collimator-telescope lenses of the photocoagulator and further focussed by the eye optics to a spot as small as 10 μ on the retina. This spot corresponds to the waist of the Gaussian beam A highly reflective beamsplitter for the therapeutic wavelength but very transparant for the other wavelengths of the scanning laser ophthalmoscope such as 632.8 nm and higher is coated according to the principles outlined above for the Maxwellian view control This beamsplitter renders the therapeutic laser beam and various scanning laser beams of the SLO coaxial towards the retina Some therapeutic laser light is however permitted to pass the beamsplitter order to reach a photodetector 114 after returning from the retina. The transmitted light through the beamsplitter and not going towards the retina is carefully absorbed to avoid confusion with the therapeutic laser light that is returning from the retina. All detectors are genlocked to a common time base for producing video output This is useful in localizing the therapeutic laser spot onto the retina For this purpose the detector is provided with a barrier filter to eliminate all light returning from the retina except the therapeutic laser wavelength It is well known in the art of digital signal and image processing to retrieve the position of the isolated flash of light in the video-signal. Because of the common time base of infra-red SLO video images and the detector used for localizing the therapeutic laser beam, a precise indication of the x-y-z position of the therapeutic beam waist is possible using the confocal imaging of the SLO and overlay graphics This information can then be stored retrieved and further image processed. Several applications will then depend on the principle or mechanism outlined above E.g It is possible to plan laser applications in particular locations, it is further possible to store the treated locations for future reference and since the determination of the coordinates of the therapeutic laser beam is happening in real-time, image registration as outlined below can determine whether the intended laser application location is still selected within a radius of acceptance If misalignment occurs, the TTL circuit can rapidly interrupt the therapeutic laser beam This is advantageous since such interruption is likely to occur faster than human reaction would allow Another possibility exists to register the localization of the therapeutic laser application during treatment The eye can be considered an imperfect blackbody radiator at 37 degrees Celsius or 310 degrees Kelvin. The therapeutic laser beam will warm up the tissue locally, e.g. gradually towards the coagulating temperature of 60 deg C. The peak intensity of such blackbody radiation is situated around 8 - 9 μ wavelength. It is very much less (< than 10 ' between 1 and 1.2 μ. A very sensitive and fast linear infra-red detector 116 can only be used between 1 and 1.2 μ because the contents of the eye effectively absorb nearly all IR beyond 1.4 μ. Using the recently introduced linear extended wavelength (l-3μ) photodetectors based on In x Ga x As technology (Hamamatsu, Japan) it is however possible to measure the temperature versus duration of application at videofield time intervals. Again the detector is gen-locked to the other components of the scanning laser ophthalmoscope to provide a common time base. Mirrors and lenses are also optimally coated for the extended IR wavelengths up to 1.4 μ. and the various beamsplitters should allow the extended IR to pass without significant loss. Diverse applications of knowing the temperature rise can be envisaged. It is e.g. possible to produce consistent minimal intensity laser applications, just intense enough to permanently disable the photoreceptors without causing further significant damage to the neighboring tissue. The importance of such approach has been stressed before. Simultaneous psychophysics, an advantage of the combination scanning laser ophthalmoscope-microphotocoagulator , allows the verification of the destruction of the photoreceptors. The practically invisible laser application locations can be permanently marked with overlays as explained above. In summary, the described preferred embodiment of optical linkage between a scanning laser ophthalmosocope and photocoagulating light source, including Maxwellian view control, mechanical Maxwellian view positioning device and common time base synchronization of various detectors allow the precise placement and registration of minimal intensity laser applications and associated psychophysics on the retina. Another advantage of the SLO-microphotocoagulator is the absence of accomodation induced errors in positioning of the laser spot. V. PSYCHOPHYSICS OPTIMIZED FOR THE SCANNING LASER OPHTHALMOSCOPE Several techniques or methods have to be combined to successfully perform psychophysics with the instrument. These include the generation of computerized graphics, projection of these graphics onto the retina using a dual laser system described before, the use of overlay graphics, adjustment of the acousto-optic modulator delay, correction for shifts in fixation and eye movements in conjunction with adaptive testing strategies to determine either retinal sensitivity or visual acuity on the retina. Several key electronic components support these techniques or methods. They include the overlay frame grabber card, acousto-optic modulator, computer with I/O devices attached Indispensable for handling the video that is output by the scanning laser ophthalmoscope and for the generation of graphics that will be projected onto the retina is the overlay frame grabber card, Fig 2. For our applications until now, we used an Imaging Technology OFG card in a 90 Mhz Pentium PC This card can select between four video input sources, and digitizes the incoming video signal to eight bits of accuracy, at a rate of 60 fields per second (RS-170) On board frame memory can store two 512 by 480 pixel video frames This versatility is important e.g. for the software algorithms that correct for fixation shifts in microperimetnc testing and the multiplexing of the signals from a multidetector SLO It is also important in simultaneous recording of the entry position of the SLO Maxwellian view and the area that is stimulated on the retina This relevance will be discussed below The analog- to-d g tal converter on the frame grabber has programmable negative and positive reference values for calibrating the white and black video signal levels A look-up table (LUT) controls the input video and can be used for preprocessing contrast and intensity This feature is particularly useful in facilitating normalized gray scale correlation as further explained. An additional four bits per pixel controls the very fast switching between different output LUTs for individual pixels. Three independent output channels are provided. The output channels generate RS-170 video for pseudocolor display Fast switching between output LUTs is an elegant solution for programming non-destructive graphic overlays. Non-destructive graphic overlays drawn into the incoming video signal are crucial for generating the stimuli in the laser raster of the SLO and on the display monitor Typically, the green output video will deliver the retinal image virtually unchanged to the monitor together with a symbolic graphics overlay outline of the stimulus The blue output of the original video signal is transformed into a graphics pattern. It is used to control the acousto-optic modulator and defines the background and stimulus that is visible to the observer The remaining red output can be used for different purposes One option is a simultaneous control of the electric amplitude modulation of a diode laser Combined with an acousto-optical device, the dynamic range of modulation can then be dramatically increased This increase is desirable in measuring more precisely near absolute thresholds m microperimetry Another critical feature of the frame grabber is the possibility to synchronize to an external video source using the phase-locked loop This is important since the timing signals provided by the high speed rotating polygon are slightly irregular Gen-lockmg (e g provided by a time base corrector) is also necessary when analog output from a video casette recorder is used to drive the acousto-optic modulator At present, an acousto-optic modulator 38 is used to generate the video graphics in the laser beam raster of the scanning laser ophthalmoscope Usually, the digital to analog video generator of the graphics board produces an analog voltage corresponding to the bitlevel of the current pixel the blue channel. This 0 - 1 V output voltage in turn modulates the amplitude of a 40 - 100 MHz radio frequency carrier signal that is produced by the AOM driver. The high bandwith, exceeding the video 10 MHz, guarantees precise modulation of single pixels. The amount of modulation can be controlled with offset and gam potentiometer controls. These values determine the shape of the AOM modulation curve and are therefore important in calibration of microperimetry. The AOM is a special crystal (e.g. fused quartz) in which standing acoustic waves, causing localized differences in refractive index, are created by a piezo-electric transducer. The transducer itself is controlled by the modulated radio frequency signal. The vibrating atoms of the crystal behave as a diffraction grating for the transversmg laser beam Constructive interference of reflected light within the crystal generates higher order beams. The amount of reflected light is approximately linearly proportional to the intensity of the sound waves or modulation A maximum transfer of energy from an undiffracted 0th order beam to the 1st order beam will only occur at a specific angle of incidence- the Bragg angle. Bragg angle, velocity of sound in the crystal and frequency of the carrier signal are related to each other. It is important to position the AOM carefully in the optical path to obtain a maximum range for modulation purposes. The Bragg angle used is very small, approx. 6 - 15 mrad. It is very difficult to adjust, and one of the principal reasons for loss of maximum intensity over time With proper alignment, better than 85 % of the incoming light can be shifted from the 0th order to the 1st order beam, delivering up to 150 μw of modulated 632.8 nm light at the exit aperture of the SLO. Changing the intensities through the acousto-optic modulator takes time. The time is necessary for the standing sound waves to adjust. This happens at a much slower speed than the changes that occur in the video display As a result, a time delay exists between the update of intensity information in the graphics overlay on the monitor and the actual change in intensity visible to the subject in the modulated laser raster. Calibration is of great importance (and has even edicolegal consequences) in assuring the correspondence between what is seen on the monitor and what is seen by the observer The AOM delay can be calibrated by adjusting the position of the real image on the monitor of a bright stimulus that is projected on the wall to match its overlay component This is accomplished by programming the drawing of graphics to the SLO and to the monitor with an appropriate pixel interval (about 50 pixels or 3.5 μs) . Another very important function of the AOM is to provide the blanking of the video signal during the retrace intervals. This will prevent the visible scanning laser beam from being visible during vertical retrace. We have previously discussed the importance of calibrating the acousto-optic modulator delay, and the positive and negative video reference values of the graphics board. These values are stored in a configuration file and can be adjusted if changes have occurred in the scanning laser ophthalmoscope. Further calibration concerns the size of the laser raster and light intensities corresponding to the different bit levels of the video board One bit level has to be specified as the background intensity. It usually corresponds to "255" when darker than background stimuli are used or "0" when brighter than background stimuli are used An intermediate value of "128" is useful to generate a finer gradation of stimulus intensities relative to the background. The drawback is a reduction in dynamic range of the intensity scale. A set of linear polarizers is used to control the intensity of the 632.8 nm laser light before it reaches the AOM. 12 predefined filter positions have to be calibrated An additional set of external ND filters and selective wavelength barriers can be added to the instrument. E.g. Melles-Griot filter FG# 3 will transmit 792 nm at over 90 % and reduce 632.8 nm to 6.3 %. Microperimetry software has to be aware of the background definition, attenuation factors of all ND elements, the normalized AOM calibration curve and absolute output of the laser at maximum settings in order to be able to calculate meaningful values of stimulus and background Stimulus and background are preferably expressed in trolands, as Weber fractions, or dB values of attenuation of the maximum possible stimulus "dB" values can be translated to those units used in automated static perimeters "dB" values used without specifying explicitly the intensities of background and maximum stimulus are meaningless. The AOM calibration curve of Fig 7 has been obtained using a microprocessor controlled laser radiometer "lasercomp" from EG&G GammaScientifIC, Inc, San Diego, Ca. Calibration is traceable to the National Institute of Standards Technology and in complete compliance with MIL-STD-45662A. The silicon detector with an area of 100 sq. mm is connected through a RΞ-232 serial interface to the same multitasking computer that projects a graphics square of 192 pixels, centered within the laser raster, onto the detector. The square itself is shielded from the adjacent areas with the help of a dark screen The detector is closely fitted to the optical head of the scanning laser ophthalmoscope Stray light is eliminated. The residual dark current from the photodiode detector is auto-subtracted For power readings in Watts, the time constant variable of the current-to-voltage circuitry is adjusted until a maximum and stable reading is obtained for each bitlevel This is important because the video timing introduces fluctuations in the output of the laser source Other precautions have to be taken during intensity calibrations. The diode 792 laser within the scanning laser ophthalmoscope is still emitting power, even at the "0" amplitude modulation settings. This leakage power is neutralized with the help of an additional external IR barrier filter, Melles Griot # KG3 that passes 65 % of the light at 632.8 nm and reduces the 792 nm to 4 % . The following conversion formulas have then been applied to convert Wattage into Troland values: (a) a 192 pixel square is equivalent to 0.112 sq. cm on the retina; (b) V(l) at 632.8 nm is equal to 0.247; (c) 100,000 Td equals 52.6 μw/sq. cm on the retina at 555.0 nm. As a result, 1 μW/sq. cm retinal irradiance at 632.8 nm corresponds to 455.9 Trolands. Conversions to equivalent asb and cd/sq. m are easily made. (The Troland value could eventually take into account the Stiles-Crawford effect and losses through the media to arrive at loss-corrected effective Trolands.) Small variations (in the order of 10%) exist within the laser raster. The output of the He- Ne laser itself fluctuates over time and during warming-up of the instrument. Variations of 7 % have been observed. Most variations in intensity output are physiologically insignificant. The normalized shape of the AOM curve seems invariant over time as long as gain and offset values remain unchanged. This facilitates recalibration. Twenty-six bitlevels are routinely measured. These measured values fit a polynomial of the 5th degree with high degree of correlation. The polynomial can be reconstructed with as few as 6 samples for recalibration purposes, according to Lagrange's interpolation method. Curve fitting has been used to obtain the best fitting polynomial. From this function the corresponding Troland values of the remaining bitlevels are derived. These calculated values are within 2 % of the measured values, an acceptable tolerance for perimetric purposes. The main advantage of a curve fitting method, instead of a fixed conversion table containing all bitlevels, is the substantial time saved during recalibration. When inspecting the calibration curve in Fig. 7, it becomes apparent that the gain factor could be slightly optimized. An increase of the gain will maximize the upper bitlevels in the sigmoid curve. The offset value could be adjusted in such way that the minimun of the curve is truly the inflection point at bitlevel 0. As such, the quotient Imax^Imin could be improved from a current 36x to about 300x. A value of 300x is typical for a good acousto-optic modulator and indispensable for measuring near absolute thresholds with 632.8 nm light. In size calibration, the same 192 pixel square at maximum intensity, is projected onto the wall. The square is slightly trapezoid because of the positioning off-axis of the mirrors in the SLO. In the 40 degree field of view, this square will measure about 13.4 cm on a side while the distance from the pivot point to the wall amounts to 67 cm. Using the Arctan formula, the conversion factor of 3.5 external minarc/pixel or 1.73 minarc/pixel in the 20 degree field of view will be obtained. On the retina, equivalent linear dimensions are calculated using the standard observer's eye of LeGrand with an effective optical radius of 16.7 mm, unaccommodated. A Goldmann III equivalent stimulus would correspond to 20 mmarc on a side The smallest acuity letter E that can be projected has a gap size of 1 pixel and corresponds to 20/34. Ametropia correction, held as close as possible to the eye, will minimize deviations from the standard eye metric and will also reduce the size variations when moving the Maxwellian view along the optical axis Non-linearities exist towards the edges of the laser raster. It is therefore important to select a reference point for the correction of fixation shifts close to the area where the stimulus is projected A decimal visual acuity of 1 0 corresponds to 20/20 and per definition is equivalent to 1 external mmarc gap size This corresponds to 4.86 μ on the standard retina. If the 192 pixel square is not equal in length on all sides, then a potentiometer adjustment is necessary to alter the vertical size of the laser raster and equalize the length of all sides Two fundamental properties of retinal functioning, acuity and sensitivity, can be efficiently measured with microperimetry Adaptive paradigms are essential to measure these variables Quantitative microperimetry relies specifically on the efficiency, accuracy, and standardized approach that is provided by these selected algorithms. In adaptive strategies the decision to present a stimulus of a certain size or intensity is decided by the program on the basis of the subject's performance so far. An adaptive procedure usually defines at what level to start, when to change the level, how much to change and finally when to stop and how to calculate an estimate of the threshold Particular to the SLO, a decision has to be made whether to correct for fixation shifts before or after presentation of the stimulus The preferred algorithm for estimating visual acuity applies a well known up-down transformed-response (UDTR) rule to a four alternative forced-choice strategy Fig 6, During the run of the staircase, a letter E is presented with one of four possible orientations. Gap size starts at 6 pixels. Contrast and background can be adjusted but are normally set to maximum and bright photopic respectively. The duration of presentation of the letter E can vary from 0 1 s to continuous A separate fixation cross, also adjustable size and contrast is optional. It is used when measuring acuities in other locations than the preferred retinal locus for fixation or PRL In this situation it is necessary to limit the duration in order to prevent the optokmetic reflex, but long enough to allow recognition Fixation shifts are corrected in the same manner as discussed the next paragraph. Most often the acuity at the PRL of fixation is measured In th s case, the E is projected continuously onto the fundus. After presentation, the subject is asked to communicate the orientation to the examiner who in turn communicates the response to the computer using the arrow keys of the keyboard This buffering guards against wrong input from inexperienced subjects. The subject is asked to guess when the letter E's orientation is not clear to him or her, a powerful method to reduce the bias from both the subject and examiner to a fixed level. With 4 alternatives, the probability of answering correctly by chance on two consecutive trials is 1/16. A potential acuity rather than real acuity is measured since it is possible for the examiner to circumvent media opacities and correct for refraction anomalies. When pseudoflxation occurs, a frequent observation, the subject can be asked repeatedly to eccentrically view the letter E The algorithm proceeds quickly the search phase, starting off with a gap size that reduces by 1 pixel after two correct answers. This phase familiarizes the subject with the procedure The search phase ends after two consecutive mistakes. In the tracking phase of the computerized algorithm, two correct answers are required before the algorithm proceeds to a smaller size. One wrong response leads back to the larger letter E "0" pixel gap is a valid option. The average pixel gap size of the letter E is calculated from five staircase reversal values and defined as the acuity threshold This approach estimates the 0.71 point of the underlying acuity psychometric function and aims at correspondence with clinical chart based methods of acuity testing where one would accept two mistakes out of ten on the chart line acuity. All the trials in the staircase procedure are stored and graphically displayed, together with an indication of orientation and whether correctly answered or not. The average pixel gap size is converted to mmarc by multiplying with the appropriate conversion factor. The reciprocal of the mmarc value yields the decimal acuity. According to Ludvigh's data, mmarc acuity drops linearly with retinal eccentricity, hence the usefulness and advantage of a linear scale in extrafoveal fixation. The limited number of steps between reversal values is a result of the fairly large step size of 1.73 mmarc/pixel and doubled in the 40 deg field of view This has to be taken in consideration when interpreting better than 20/34 acuity values in the perifoveal area or acuities better than 20/70 in the 40 deg field of view. The preferred algorithm for estimating retinal sensitivity uses an adaptive yes-no strategy wherein adjustable steps are determined by immediately preceding trials The algorithm is modelled after Taylor & Creelman's "parameter estimation by sequential testing" or PEST The procedure is summarized as follows Fig. 8 Background is selected. An optional fixation cross of variable size and intensity is used. Stimulus size and duration are selected Normal default values are 20 mmarc on a side and 0.1 s. Up to 16 test locations can be selected for multiplexing Each location can have a different suprathreshold starting value The subject's response is again buffered by the examiner. The stimulus bit value is decremented by the initial step size of 16 with each presentation until a reversal of the subject's response occurs Upon reversal the step-size is halfed Th s continues until the minimal step- size is reached. The final stimulus bitlevel that is calculated is defined as threshold. Some means of recovery from steps in the wrong direction is provided. A third step in the same direction will again double the step-size and continue to double with each further step in the same direction unless a reversal will follow the doubling of a step-size, in which case three step-sizes in the same new direction are necessary before doubling. Doubling occurs until the maximum of 16 bitlevels is reached. The testing procedure is characterized by a variable run length, a high degree of robustness against attention loss and errors from the subject and the important advantage of not requiring decisions about stimulus spacing. Precise stimulus spacing is very difficult to accomplish with the acousto-optic modulator. All bitlevels are now useful for the estimation of the threshold but it is only the final bitlevel that will be converted to a Troland value. Corrections for eye movements during fixation can be made immediately before stimulus presentation or immediately after stimulus presentation. This depends on the necessities of the testing procedure. If the stimulus presentation belongs to a predefined grid of test locations or is part of an adaptive strategy, then correction for the displacement vector is necessary just prior to presentation under real-time conditions. For this purpose, any landmark close to the stimulus site can be used. The translational displacement vector is instantly calculated from the difference in cartesian coordinates of the landmark on the initial fundus image that was used to define the grid or location for threshold measurement, with the coordinates on the last image prior to presentation. The landmark coordinates are entered into the computer by the examiner with the help of a pointing device. Hitting the landmark is at times at difficult task. A frozen image at the time of presentation makes it easier to verify to the landmark has been hit. In case of mismatch, the trial can be repeated. If the stimulus presentation is static but does not belong to a grid or algorithm, a correction for fixation shifts is necessary immediately after the presentation in order to present the individual trials on a single final image in the correct location. This approach is very flexible but much less rigorous than the previous method. Both correction methods also plot actual fixation samples in the correct place on the retinal image. A continuously presented stimulus is very efficient to explore the central visual field prior to the selection of appropriate static test locations and starting values. Precise plotting of a traditional iεopter segment is only possible if a correction is made for the subject's reaction time. This could now be accomplished on-line using the two image buffers of the frame grabber, optionally combined with automated registration of image displacements. VI. FUNDUS AND PUPIL TRACKING WITH THE SCANNING LASER OPHTHALMOSCOPE As mentioned before, the entrance pupil and stimulus location on the retina can be selected independently from each other and are subject to a passive or active feedback mechanism to ensure their position regardless of eye movements or fixation shifts. The passive mechanisms include a manual repositioning of the stimulus or entrance beam using fiducial landmarks A simple repeat trial upon error strategy is used for presenting a stimulus to one specific retinal location under visual feedback control as described in a previous paragraph. Typically the pivot area is focussed on the iris using 632.8 nm light, prior to testing. The distance between iris and scanning laser ophthalmoscope is verified at regular intervals. The active mechanisms make use of digital image processing techniques for pupil and fundus tracking. A second OFG board 68 within the same CPU can perform these tasks using for example a technique called two-dimensional normalized gray-scale correlation. Such software is provided by Imaging Technology, Inc, Bedford, Ma. A 7 degree rotational tolerance and 60 ms search time are acceptable for the rather liberal requirements in clinical testing procedures. For pupil tracking the reference picture is the anterior segment, for retina tracking it is the fundus image. Feedback regarding eye movements and fixation shifts can then be used to adjust the x-y-z stepper motors 62, 64 or the psychophysical test algorithm as described before Fig 4,5. It is possible to multiplex both video coming from the scanning laser ophthalmoscope and CCD camera. Therefore one computer with two boards is sufficient In two-dimensional normalized gray-scale correlation a search patttern is retrieved withm the larger fixed reference pattern Multiple search patterns can coexist A reliable method to lock the antero-posterior distance of the scanning laser ophthalmoscope to the iris is the quantification of the size of different fiducial landmarks within the image of the anterior segment. These can include the Purkmje images Summary, Ramifications, and Scope The scanning laser ophthalmoscope-microphotocoagulator is an electro-optical device that broadens the range of clinical applications of the conventional scanning laser ophthalmoscope. The three cardinal features are a special Maxwellian view coupling device, control over the Maxwellian view entry location, and computer awareness of the location of aiming beam or therapeutic beam through usage of a common time base between different detectors With the device it is possible to visualize the retina and simultaneously perform microperimetry for the purposes documented in the related U.S. patents. Without changing instruments, the capability now exists to administer laser applications to the retina. Not having to change instruments, with different optical characteristics, is an important issue because of the instantaneous feedback with regard to the angiographic pattern and psychophysical response that one can obtain even during the treatment session. This feedback is represented on the same image that is used to direct the laser applications and will therefore enhance the precision of the treatment A so called non-contact method of therapeutic laser is possible for two mam reasons. First, a specific optical linkage mechanism between the scanning laser ophthalmoscope and the terapeutic laser that allows the use of essentially the same Maxwellian view for both the therapeutic laser and the scanning laser ophthalmoscope. Second, the use of the Maxwellian view control described in previous U S. patent, to verify the presence of the pivot point of the therapeutic laser within the anatomical pupil of the eye. This positioning could be maintained either passively by the surgeon or actively using digital image processing on the image of the anterior segment of the eye. It is e.g. possible to interrupt the therapeutic beam when it inadvertantly hits the iris margin. The use of mirror-optics and transmission instead of fiber optics allows a well-defined Gaussian beam to enter the eye. Especially m the 20 degree field of view, it is possible to manipulate the antero-posterior position of the minimal waist of such therapeutic laser beam This focussing permits some additional adjustment as to the depth of impact of the laser application in the retina. Selective targetting of the photoreceptor layer is then made somewhat easier with the proper selection of wavelength, size, intensity, and duration of the laser application. The ability to concentrate the thermal destruction to the photoreceptor-pigment epithelium complex may be very useful since selective removal of metabolically very active photoreceptor elements will reduce the consumption and competition for oxygen, glucose and other necessary elements, of which the transportation across the diseased retina is already impaired in early stages of age related maculopathy (e.g. thickening of Bruch's membrane, soft drusen permeability) The improved oxygenation, provided the choriocapillary layer is largely kept intact, in turn can reduce the production of angiogenetic "stress" stimuli produced by the RPE complex and in this way avoid the neovascularisation stage of age related macular disease This mechanism may also lead to the dissapearance of the drusen by reducing the workload of, and enhancing the productivity of the photoreceptor phagocytosis and renewal cyclus. Microperimetry is useful to select the areas for laser treatment and then to follow-up on the functional status of the retina between the non-con luent applications Possibly retinal areas with dimished retinal function are more likely to attract new vessels and therefore should be eliminated first The laser treatment should respect potential conjugate PRL of fixation and the horizontal meridian, as much as possible Microperimetry can be used to verify that a particular area on the retina has been destructed because it should result in a dense scotoma. This is important since minimal applications, e g controlled by the thermal detector, are hardly visible. The applications however can be permanently marked on any retinal image using overlays These overlays of the location of the aiming or therapeutic laser beam are indeed possible because of the use of a gen-locked detector in combination with appropriate barrier filters and image processing This detector can be the thermal IR or regular visible wavelength detector as previously explained Human reaction time is longer than 250 ms Digital image processing can see faster any misalignment from an intended laser application location or a rapid increase in temperature Digital image processing can effectively reduce the reaction time to one videoframe Microperimetry applications now incorporate all the necesary features for accurateness fast overlays, AOM delay control, normalized gray-scale correlation for fundus and pupil tracking, and adaptive strategies to determine key parameters of retinal function. Fundus location as well as Maxwellian view entry location can be variables in microperimetry to derive these key parameters Although the description above contains many specif cities, these should not be construed as limiting the scope of the invention but as merely providing illustrations of some of the presently preferred embodiments of this invention. Other embodiments of the invention including additions, subtractions, deletions, or modifications of the disclosed embodiment will be obvious to those skilled in the art and are within the scope of the following claims. The scope of the invention should be determined by the appended claims and their legal equivalents, rather than by the examples given

Claims: Claims: I claim 1. A combination of a scanning laser ophthalmoscope and a photocoagulator to enable the placement of laser applications onto a retinal location under simultaneous and continuous observation of said retinal location and its neighborhood, comprising the elements of A said scanning laser ophthalmoscope, having at least two laser sources from which a visible laser beam is used for generating a visible laser raster that contains graphical stimuli and is projected onto the retina, and another essentially invisible and colmear laser beam of sufficient power output is used for obtaining a video image of said retinal location and its neighborhood with photodetectmg means of said scanning laser ophthalmoscope on a monitor, B said photocoagulator comprising a therapeutic laser source from which a therapeutic laser beam of sufficient power output can produce said laser applications onto said retinal location, further including a colmear aiming beam, a micromanipulator to direct said colmear aiming beam and said therapeutic beam onto said retinal location, pre-focuss g means for said therapeutic laser source, and supporting electronics controlling the size, duration and intensity of said laser applications, C means for optically coupling said scanning laser ophthalmoscope with said photocoagulator including optical elements selected from the group consisting of mirrors, barrier filters, bandpass filters, interference filters, polarizing filters apertures, absorbers, beam shaping devices, and liquid crystal filters placed in the optical path of said scanning laser ophthalmoscope and said photocoagulator so that the production of said laser applications does not oversaturate said photodetectmg means of said scanning laser ophthalmoscope, D. a computer with an overlay frame grabber card, said overlay frame grabber card including means for synchronizing video input and video output to timing signals provided by said scanning laser ophthalmoscope, further having sufficient on-board memory and at least three independent output channels so that said computer with overlay frame grabber card is capable of simultaneously digitizing and manipulating in real-time video images of the retina, incorporating said retinal location and its neighborhood, generating said graphical stimuli for projection onto the retina and indicating the correct location of said graphical stimuli, said aiming beam and said therapeutic laser source onto said monitor, E. modulating means for said visible laser source to create said graphical stimuli m said visible laser raster using said computer with overlay frame grabber card for indicating the correct location of said graphical stimuli onto said monitor, whereby it becomes possible to continuously visualize said retinal location and its neighborhood using non-bleachmg light levels on a monitor, project a fixation target, position simultaneously said aiming beam onto said retinal location, activate said therapeutic laser source for a variable amount of time while monitoring the position of said retinal location, and from time to time examine angiographically or psychophysically said retinal location and its neighborhood without the need of swith g from said scanning laser ophthalmoscope to a different diagnostic instrument or interrupting the observation of said retinal location and its neighborhood 2 The combined scanning laser ophthalmoscope-photocoagulator according to claim 1, wherein means for optically coupling said scanning laser ophthalmoscope with said photocoagulator includes A. a succession of flat mirror interfaces and structural support means joined together so that enough degrees of freedom exist to move last mirror freely on a virtual surface that is curved in such manner that a pivot point is created for said therapeutic beam, similar to the pivot point of said visible and said invisible beam; B said optical elements selected from the group consisting of mirrors, barrier filters, bandpass filters, interference filters, polarizing filters, apertures, absorbers, beam shaping devices, and liquid crystal filters, C. a beamsplitter; whereby said therapeutic beam and said visible laser beam can be rendered approximately colmear before reaching said retinal location in the eye 3. The combined scanning laser ophthalmoscope-photocoagulator according to claim 1, further comprising the improvement of having means for interrupting said therapeutic beam including electronic circuit connecting attenuating means for said therpapeutic beam and said computer with said overlay frame grabber card, said electronic circuit triggering said attenuating means upon sufficient displacement of said retinal location in frame memory of said overlay frame grabber card as determined by digital processing of grabbed said video images, whereby it becomes possible to attenuate said therapeutic laser beam m case of misalignment faster than human reaction time would allow 4 The combined scanning laser ophthalmoscope-photocoagulator according to claim 1, further comprising the improvement of having means for measuring retinal temperature increase at said retinal location and neighborhood caused by said laser applications including second photodetectmg means build into said scanning laser ophthalmoscope in similar manner as said photodetectmg means, second photodetectmg means used for measuring the amount of thermal radiation of near infra-red wavelengths .at video rate with the scanning optics of said scanning laser ophthalmoscope; whereby the intensity, location and rate of temperature increase caused by said laser applications at said retinal location is measurable using said computer with said overlay frame grabber card and enabling to attenuate said therapeutic laser beam in case of overdosage faster than human reaction time would allow 5. The combined scanning laser ophthalmoscope-photocoagulator according to claim 1, further comprising the improvement of having means for simultaneous observation of anterior and posterior segment of the eye, said means for simultaneous observation allowing the continuous visualization on a monitor of said retinal location and its neighborhood and the pivot points of said therapeutic beam, visible beam and invisible beam; whereby it becomes possible to interrupt said therapeutic beam using said computer with said overlay frame grabber card in case of misaligment, permitting further automatic repositioning of said therapeutic beam using the X-Y-Z motorized platform of said scanning laser ophthalmoscope, thereby minimizing the chances of inadvertantly delivering said laser applications outside the anatomical pupil of the eye and facilitating non-contact delivery of said laser applications 6 A method for measuring retinal function at a precise retinal location using a scanning laser ophthalmoscope, comprising the steps of: (a) presenting a double colmear laser raster to a retina, wheieby a laser raster serves to produce a video representation of said retina on a monitor while a second laser raster is going to be used for projecting a graphical stimulus having a predefined value from a computer controlled overlay graphics card onto said retina; (b) correcting for any time delay between overlay graphics on said video representation and the projection of said graphical stimlus onto said retina; (c) determining coordinates of a fiducial landmark on said retina in said video representation prior to presentation of said graphical stimulus, (d) adjusting in a cartesian manner the video coordinates of said graphical stimulus whereby it becomes possible to project said graphical stimulus at the same said retinal location regardless of eye movements or shifts in fixation, (e) adjusting the characteristics of said graphical stimulus according to the outcome of previous presentations of said graphical stimulus and following the instructions of a computerized algorithm; (f) presenting said graphical stimulus, (g) repeating the above steps from (a) through (g) until a desired endpo t is reached, sa d endpomt defined as the amount of retinal functioning at said retinal location 7 A method for measuring retinal function at a precise retinal location using a scanning laser ophthalmoscope according to claim 6, further comprising the improvement of determining said coordinates of a fiducial landmark with the method of normalized gray scale correlation, whereby repeated registration of said fiducial landmark is possible before or after said presentation of graphical stimulus and without the need for manual referencing of said fiducial landmark 8 A method for measuring retinal function at a precise retinal location using a scanning laser ophthalmoscope according to claim 6, further comprising the steps of A Determining the entry point of the Maxwelian view used by said visible beam, B Adjustment of said entry point prior to presentation of said graphical stimulus along the XYZ axes C Repeating steps A through C until a desired endpomt is reached whereby it becomes possible to measure the influence of the orientation of photoreceptors and media opacities in the eye on said retinal function 9 A method for measuring retinal function at a precise retinal location using a scanning laser ophthalmoscope according to claim 6, wherein the improvement comprises calculation of the intensity of said graphical stimulus using the method of polynomial regression on a curve representing the correlation between a subset of all possible bitlevels for the intensity of said graphical stimulus and the corresponding value of said bitlevels m radiometric or photometric units, whereby it becomes possible to use all said bitlevels for determining said retinal function and efficiently calibrate said scanning laser ophthalmoscope for measuring said retinal function 10 A method for enlarging the dynamic range of possible intensity values for a graphical stimulus including the steps of A connecting the input of a acousto-optic modulator to a first output channel of a graphics card, B connecting the input of a diode laser amplitude modulation circuit to a second output channel of said graphics card, C establishing common synchronization between said first output channel and said second output channel, D passing the laser beam of said diode laser through said acousto-optic modulator, E. selecting a first bitlevel for said first output channel and a second bitlevel for said second output channel ; F. modulating said acousto-optic modulator and said diode laser with voltages produced by said graphic card at said first bitlevel and said second bitlevel; whereby it becomes possible to obtain a number of different intensity values for said graphical stimulus equal to the product of said first bitlevel and said second bitlevel.

Inventors: VAN DE VELDE FRANS J, VAN DE VELDE, FRANS, J.
Applicants: VELDE FRANS J VAN DE, VAN DE VELDE, FRANS, J.
Application year: 1997
Main classification: A61B
IPC codes: A61B3, A61B17, A61F9