Electro-Optic Binocular Indirect Ophthalmoscope

The present invention relates to ophthalmoscopes and, more particularly, to binocular indirect ophthalmoscopes for observing and examining the fundus oculi of human eyes.

Binocular indirect ophthalmoscopy offers several advantages over direct ophthalmoscopy, including stereopsis and a much enlarged field of view and depth of field. However, the usefulness and flexibility of binocular indirect ophthalmoscopy has been generally restricted to use in the examination of eyes with substantially clear opacity. Other techniques using infrared scanning laser ophthalmoscopes or infrared fundus cameras are generally employed to examine eyes with media opacity.

For example, scanning laser ophthalmoscopy (SLO) using infrared illumination is preferably used to examine eyes with nuclear sclerotic cataracts or mild vitreous hemorrhage, and in combination with indocyanine green angiosgraphy (ICG) to examine the choroidal layer, lesions and subretinal membranes and scars of the eye. SLO uses a low power, focused laser beam, typically He-Ne, to scan the fundus. A video image is obtained by collecting the reflected light from the fundus one point at a time and then by displaying its intensity on, for example, a television monitor. Advantageously, the resolving power of the SLO is limited by the size of the laser spot and/or the size of the aperture through which the reflected radiation is collected. The advantages of SLOs as well infrared fundus cameras are well known to those skilled in the art.

Unfortunately, SLOs as well as infrared fundus cameras are prohibitively costly for most clinicians and lack the accustomed stereopsis, which is helpful in evaluating the topography of the fundus features. For these reasons, a need has arisen for an improved binocular indirect ophthalmoscope having comparable capabilities to those of SLOs or infrared fundus cameras, but yet which is relatively inexpensive.

An improved binocular indirect ophthalmoscope for observing and examining the fundus of the human eye is realized by integrating an electro-optic imaging system in the viewing optics of the ophthalmoscope. Advantageously, this permits the direct stereoscopic observation of the fundus using illumination ranging from the near ultraviolet to the infrared, including the visible spectrum.

In accordance with the principles of the present invention, a light source illuminates a desired portion of a patient's fundus, with the reflected radiation brought to focus to produce an aerial image of the fundus. A pair of ophthalmoscope lenses then magnify and image along two different optical paths the aerial image onto separate imaging sensors, such as charge coupled devices (CCDs) or camera tubes, or onto image tubes such as image intensifiers, and the like. For CCDs and camera tubes, visible displays, such as liquid crystal displays (LCDs) or cathode ray tubes (CRTs), then photo-electrically convert the fundus images formed on the imaging sensors and direct corresponding visible images thereof to an observer's pupils by means of ocular lenses. Of course for image tubes, the observed visible display results when electrons emitted by the photosensitive surface of the image tube strike its fluorescent screen which reproduces the fundus image focused on the photosensitive surface.

Although not limited to, both visible and infrared imaging are readily available by judiciously selecting the spectral characteristics of the light source, filters and imaging sensors of the present ophthalmoscope. This is a particularly distinct advantage over prior art binocular indirect ophthalmoscopes which can only operate in the visible spectrum.

A more complete understanding of the invention may be obtained by reading the following description in conjunction with the appended drawing in which like elements are labeled similarly and in which:

FIG. 1 is plan elevation view of a binocular indirect ophthalmoscope in accordance with the principles of the invention;

FIG. 2 is a schematic plan view of the illumination assembly of the binocular indirect ophthalmoscope of FIG. 1;

FIG. 3 is a schematic plan view of the viewing assembly of the binocular indirect ophthalmoscope of FIG. 1;

FIGS. 4(a)-(d) depict the spectral characteristics of a variety of light sources which may be used in the binocular indirect ophthalmoscope of the present invention;

FIG. 5 is an illustrative diagram depicting the position of the imaging sensors and the light source in the patient's pupil;

FIG. 6 is a diagram of an alternative illumination system which may be used with the binocular indirect ophthalmoscope of the present invention;

FIGS. 7(a)-(b) depict the spectral responsivities of a variety of imaging sensors which may be used in the binocular indirect ophthalmoscope of the present invention;

FIGS. 8(a) and (b) depict illustrative views of the fundus image along a single viewing axis under visible and infrared illumination, respectively;

FIG. 9 is a plan elevation view of an alternative embodiment of the binocular indirect ophthalmoscope in accordance with the principles of the invention; and

FIG. 10 is a schematic plan view of the viewing assembly of another embodiment of a binocular indirect ophthalmoscope in accordance with the principles of the present invention.

The direct stereoscopic observation of the fundus of the human eye using illumination ranging from the near ultraviolet to the infrared spectrum is realized by integrating an electro-optic imaging system in the viewing optics of the ophthalmoscope. Such electro-optic imaging systems include the use of CCDs, CRTs, LCDs, camera tubes and image tubes. Where the fundus is displayed as a video image, well known digital image processing techniques may be optionally used to delineate and enhance desired features of the fundus image in real-time, including those techniques used, for example, in SLOs. Such digital image processing techniques may include scaling, rotating, pseudo-coloring or feature extracting of the fundus image, among others.

It is contemplated that the present invention provides comparable visualization as SLOs which are prohibitively costly for most clinicians and lack stereopsis, which is particularly important to measure depth and evaluate the topography of retinal features, such as the optic nerve head and peripheral retina. Moreover, the visualization of the fundus for the present ophthalmoscope is acquired in real-time.

Without any loss of generality or applicability for the principles of the present invention, in some embodiments the description is with respect to conventional imaging and illumination optics. It should, however, be clearly understood that the present invention is equally applicable to other types of imaging and illumination optics too numerous to discuss herein, which are well known in the art. Such alternative optics may be used, for example, to reduce the weight of the ophthalmoscope, provide a greater field of view, minimize aberrations and/or improve image quality. See in general, Born et al., Principles of Optics: Electromagnetic Theory of Propagation, Interference and Diffraction of Light, Pergamon Press, New York (1975).

Also, it should be clearly understood that the electro-optic imaging system of the present invention may be similarly used in direct ophthalmoscopes, if a binocular image is not necessary.

Referring to FIGS. 1-3, there is shown an exemplary embodiment of a binocular indirect ophthalmoscope 100 in accordance with the principles of the present invention. Ophthalmoscope 100 includes an adjustable head assembly 105. Ophthalmoscope 100 may be worn on the head of a clinician using the ophthalmoscope in a manner similar to a conventional indirect ophthalmoscope. Head assembly 105 may have a head band 110 for encircling the head, a strap 115 integral with head band 110 adapted to fit on top of the head, and a semi-circular band 120 pivotally attached to the sides of head band 110 and extending toward the front end thereof. Viewing assemblies 125, 125' below an illumination assembly 130 may be secured to the forward part of semi-circular band 120 by a coupling attachment 135 or other suitable means. Although semi-circular 120 is rigidly secured, it may be pivoted up or down with reference to head band 110 so as to adjust the vertical position of viewing assemblies 125, 125'.

The housing of illumination assembly 130 has a tube 140 or other similar means extending downwardly therefrom into viewing assemblies 125, 125' which is provided with means therein for permitting binocular vision when the observer's eyes are optically aligned with viewing assemblies 125, 125', as discussed herein below. Illumination assembly 130 includes one or more light source(s) 145, such as a bulb, light emitting diode (LED), laser, laser diode or the like, emitting in a predetermined radiation spectrum and connected to a power source of sufficient voltage to operate the source. Of course, multiple light sources may be used, depending on the desired application.

It should be clearly understood that the spectral characteristics of the illumination to the patient's pupil 150 may be tailored to the desired application by judiciously selecting the spectral characteristics of light source 145 and/or the bandpass region of an optical filter(s) 155 positioned, for example, after light source 145. Although not limited to, both visible and infrared imaging are readily selectable. This is a particularly distinct advantage over prior art binocular indirect ophthalmoscopes which can only operate in the visible spectrum. It is important to understand, for example, that infrared radiation is particularly well suited when examining eyes with opacities, including nuclear sclerotic cataracts or vitreous hemorrhage. Infrared light generally penetrates such opacities more efficiently, allowing a visualization of otherwise obscured structures. Infrared light also penetrates the retina itself, allowing the choroidal neovascular membrane to be imaged, which is very difficult to do with conventional indirect ophthalmoscopes. Other radiation wavelengths, of course, may be better suited to view other features of the fundus.

Accordingly, optical filter 155 may be designed, for example, to selectively pass visible radiation in the range of about 400-700 nm, or near infrared radiation in the range of about 750-900 nm. Of course, discrete radiation wavelengths--in the visible and/or infrared spectrum--may also be spectrally selected. For example, those skilled in the art will readily recognize the advantages of using the radiation wavelength of 805 nm for ICG. In general, using infrared illumination results in higher contrast and better visualization for certain features, including the choroidal layer, lesions, subretinal membranes and scars of the eye.

Optical filter 155 may comprise absorption bandpass filters and/or interference filters, as well as narrow bandpass filters, which are all well known in the art. For narrow wavelength band light sources, such as lasers, which typically emit a single discrete radiation wavelength, the need for optical filter 155 in illumination assembly 130 is obviously obviated. Such filters, however, may still be used in the viewing assemblies so as to eliminate any unwanted radiation from other sources, as discussed herein below.

Shown in FIG. 4 are typical plots of the spectral characteristics of several light sources that may be used for light source 145. Xenon, argon, tungsten lamps and the like may be used to provide broad band radiation from the visible through the infrared spectrum. Semiconductor lasers or LEDS, however, including those using In.sub.x Ga.sub.1-x As, InP.sub.x As.sub.1-x, Al.sub.x Ga.sub.1-x As and GaAs.sub.1-x P.sub.x, among others, are more particularly well suited for providing near infrared radiation (750-900 nm). Preferably, light source 145 emits radiation over a broad spectrum from the visible to the infrared or at one or more discrete wavelength(s) in the infrared spectrum. If desired, the radiation may be modulated to form a repetitive, characteristic radiation pattern which can be used to distinguish the radiation from other possible sources of radiation in the same wavelength spectrum.

Now referring back to FIGS. 1-3, an illumination mirror 160 is used to direct to the patient's eye radiation from light source 145 which is exiting through a condenser 165. Reflective elements, such as multilayer mirrors, may be used to reflect only the radiation wavelengths of interest to the patient's pupil, dispensing with the need for optical filter 155. For use through the infrared spectrum, gold coated mirrors are preferably used. Such mirrors only have a high reflectivity above 500 nm, and as such fortuitously filter out any short wavelength radiation which may be harmful to the eye.

Those skilled in the art will readily note that an ophthalmoscopic lens 170 images light source 145 to the patient's pupil 150. As discussed herein below, ophthalmoscopic lens 170 is held close to the patient's eye and provides an image of the patient's retina from light reflected back from the fundus. An ophthalmoscopic lens of about 15-80 diopters may be used as lens 170. A high power lens typically results in a low image magnification, but a larger field of view. In an emmetropic system, a real image (aerial image) is formed at a focal plane 175 of ophthalmoscopic lens 170. It is contemplated that lens 170 is of sufficiently good optical quality to generate an image of the fundus with an acceptable image resolution. Lens 170, of course, may be fabricated to be selectively transmissive within a desired spectral range, thereby functioning not only as a lens but also as a filter.

Illumination mirror 160 may be moved independently of viewing assemblies 125, 125' located underneath it. Alternatively, illumination mirror 160 may be fixedly mounted with respect to the viewing assemblies and thus moves with it. Regardless of the illumination type, an image of illumination source 145 is produced at the patient's pupil along with the images of the imaging sensors, as illustrated in FIG. 5, and discussed herein below.

Radiation from light source 145 may be optionally directed through an illumination diaphragm 180. If desired, a hemispherical reflector 185 may also be mounted in the rear of light source 145 to effectively concentrate the light through diaphragm 180. Likewise, hemispherical reflector 185 may be selectively reflective within a desired spectral range so as to tailor the radiation spectrum of the illumination. Alternatively, the amount of visible as well infrared radiation directed to the anterior part and retina of the patient's eye may be adjusted to within safe levels through the use of neutral density filters, for example, positioned between the light source and condenser. Or, the intensity of light source 145 may be adjusted by controlling the bias voltage thereto.

For visible radiation, the retina may be safely exposed to illumination levels of about 100-150 mW/cm.sup.2. See, for example, Mainster et al., Ophthalmology, Vol. 89, pp. 852-857 (1982). At radiation wavelengths near about 800 nm, illumination levels of about 500-600 mW/cm.sup.2 are believed to be safe. See, for example, Sliney et al., "Hazard Analysis of Broadband Optical Source," U.S. Army Environmental Hygiene Agency. In general, the absorption is much lower for near infrared radiation than for visible. As such, it is believed that for the same level of illumination, the eye is less likely to be harmed with near infrared radiation. Furthermore, the use of high gain imaging sensors permits lower illumination levels to be used.

Nevertheless, to minimize the exposure of the eye to harmful radiation while maintaining the same brightness, it is contemplated that the light source may be pulsed and synchronized with the beginning of a video frame, if the visible display is a video image. Typically, for pulsed radiation the safe limits of illumination are much greater. Pulses as short as 1/100th of a second or less may be used with imaging sensors having a long persistence duration. Although such a time period is shorter than one video frame (1/30th of a second), the flashed or pulsed illumination still allows a full image to be displayed because of the relatively slow decay of the imaging sensor. The flashed illumination results in an "after image" on the imaging sensors that can be obtained even after the illumination has been extinguished. Of course, since the image decay starts as soon as the flashed illumination disappears, the amount of decay needs to be corrected so that the bottom of the video image remains as bright and with comparable contrast as the top. For example, automatic gain control may be used for such corrections.

To insulate the observer from heat generated by light source 145, such as a filament type source, a laminated tunfnol layer of about a few millimeters or other suitable heat insulator may be positioned between the housing of light source 145 and its outside frame. The intensity of the illumination light can then be adjusted by limiting the aperture of illumination diaphragm 180. Alternatively, the light source itself may be separated from the ophthalmoscope and connected thereto through an optical fiber, as discussed herein below.

Alternatively, a prism (not shown) may be used with condenser 165 to direct the illumination from the higher disposed light source to the lower disposed level of the viewing axis. In this latter case, the illumination will then be refracted downward by the prism to intersect the viewing axis. In this latter instance, illumination mirror 160 is not necessary. Other types of illumination techniques may also be used, such as, for example, slit beam illumination, retro-illumination and the like. See, for example, U.S. Pat. No. 3,403,957, which is incorporated herein by reference.

Alternatively, the illumination system of Schepens et al., for example, may also be used as shown in FIG. 6. In this latter case, radiation from light source 145 is collimated by a condensing lens 190, passes through diaphragm 195 and is focused in the plane of optical filter 205. Diaphragm 195 is located at the focal plane of an objective lens 200. The light is reflected further by mirror 210 and passes through teleocentric ocular lens 215, forming an image of diaphragm 195 in an image plane 220. After passing through ophthalmoscopic lens 225, the light is focused in the pupil plane of the patient's eye. By changing ocular lens 215, it is possible to change the illumination diameter in image plane 220 without changing the light power. Advantageously, this type of illumination provides a uniform illumination for different magnifications and reduces the illumination pupil diameter in the patient's pupil plane. See, U.S. Pat. No. 5,400,092, which is incorporated herein by reference.

Referring specifically to FIG. 3, viewing assemblies 125, 125' include a mirror assembly 230 having, for example, two reflective surfaces, 235, 235' at approximately 45.degree. to the viewing direction along an optical axis 240. This angle, however, may be adjusted to obtain the best stereopsis. Preferably, mirror assembly 230 is movable over a short distance--about 3 mm--in a direction parallel to optical axis 240 of the ophthalmoscope. This alters the length of the stereo base of the ophthalmoscope. Alternatively, each reflective surface may be replaced with a prism.

Incoming light rays emanating from the fundus of eye 245 propagates through ophthalmoscopic lens 170, strike reflective surfaces 235, 235', and then are directed laterally onto a second pair of mirrors 255, 255', respectively. If desired, each mirror may be mounted such that its angle of rotation is adjustable. In the event that a mirror becomes misaligned, realignment is then readily possible. Mirrors 255, 255' may be in form of a prism, such as a Schmidt or Pechan prism which shortens the length of system by folding the rays of the light within the prism. At the same time, such prisms can re-invert the aerial image without interfering with the optical axis, although not necessary.

Mirrors 255, 255' provide two optical paths, 260, 260' corresponding to viewing axes 305, 305' which are at an angle to each other (.about.15.degree.) and to optical axis 240. Presenting the fundus image to the observer along two different viewing axes advantageously provides a binocular image in a manner similar to conventional ophthalmoscopes. Mirrors 255, 255' reflect the light rays through lens 265, 265', respectively, which focus onto imaging sensor 270, 270' an image of the aerial image of the patient's eye. It is contemplated that mirrors 255, 255' as well the others in the present ophthalmoscope may be gold coated for use with radiation wavelengths from the visible through the infrared spectrum. Optionally, optical filters 275, 275' may be positioned in front of imaging sensors 270, 270' to only pass the radiation wavelengths of interest so as to provide improved image quality.

Alternatively, an optical filter(s) may be positioned in front of mirror assembly 230, instead of using filters 155, 275, 275'. In this latter case, those skilled in the art will readily note that both the illumination and reflected radiation propagate through the same optical filter positioned in front of mirror assembly 230.

Typically, the spectral characteristics of optical filters 275, 275' are chosen to be comparable to those of optical filter 155, if present. One exception, however, is when it is desirable to collect the fluorescence of the retina, such as for ICG. In this latter case, the retina, which has been subjected to a specific dye, is illuminated by a particular wavelength and viewed using a different radiation wavelength to detect the fluorescence thereof. The fluorescence can be a native florescence of the tissues or the fluorescence of dye used to selectively color some detail of the eye. Regardless, imaging sensors 270, 270' should be particularly sensitive to the radiation wavelengths of interest for the desired application, typically from the visible through the infrared spectrum.

View assemblies 125, 125' are each slidably movable so as to be spaced apart from each other to permit the adjustment of the spacing between pupils 280, 280' of the observer. Typically, the interpupillary distance ranges between 56-72 mm.

It is contemplated that imaging sensors 270, 270' may be solid state CCDs or camera tubes, such as those found in video cameras, which are sufficiently sensitive to the radiation wavelengths of interest, including the near infrared spectrum. Other suitable devices, such as image intensifiers suitable for night vision, may be used, thereby combining in a single device, imaging sensors 270, 270' and visible displays 285, 285', as discussed herein below.

Image intensifiers are image tubes that reproduce on a fluorescent screen an image of the radiation pattern focused on its photosensitive surface. Typically, a first generation image intensifier includes a photocathode (imaging sensor) upon which a radiant image is focused, an electron lens, and a fluorescent screen (visible display) upon which the output is displayed. Such image tubes may be used to convert non-visible radiation from an image into a visible display or to produce an image that is brighter than the input image. It is contemplated that suitable image intensifiers are preferably of a second or third generation type which do not use an electron lens. Such image intensifiers, however, employ micro-channel plates having an automatic gain setting responsive to the illumination of the incident light.

Those skilled in the art will readily note that CCDs, unlike camera tubes, are solid state imaging devices which do not require a scanning beam. Such devices are capable of producing a video image display through the use of an external display, such as a LCD or a CRT. Individual cells of the CCDs are formed into a TV-type raster by an array of parallel conducting strips and channel stops at right angles thereto. In operation, electron-holes pairs are created when light is incident on the cells. Charges representing the picture element signals are stored in potential wells under biased electrodes. The charges are transferred by applying a pulse voltage to the electrodes with the image transferred in this manner to a storage raster during the vertical blanking period. Each horizontal line is then read out from the storage raster sequentially in a similar manner to provide, for example, a video signal. This video signal then may be displayed as an image on a LCD, CRT and the like.

Shown in FIG. 7 are typically plots of the spectral responsivity of CCDs and image intensifiers. In FIG. 7(a), each curve is correspondingly labeled for illustrative purposes with the image intensifier model number from Hamamatsu, Inc. having that spectral response. As noted, CCDs are typically sensitive to visible radiation up to and including the infrared spectrum near 1100 nm. The photocathodes of the image intensifiers, however, may be judiciously selected to be particularly sensitive to longer wavelength infrared radiation as well as visible radiation of course, various photocathode materials may be used which have the desired spectral responsivities, ranging from the near ultraviolet to the infrared spectrum.

Preferably, such electro-optic imaging systems should have a resolution at least sufficient to resolve details in the vascular pattern of the patient's fundus for examination purposes, such as 10-30 line pairs/mm. It is contemplated that both black and white as well as color images may be obtained, depending on the choice of the imaging sensors. For example, color CCDs are readily available in sizes of 1/3-1" diameters and are capable of providing real-time color images. Also, various camera tubes as well as image intensifiers are readily available from different manufacturers, such as from Hamamatsu, Inc. Japan, or Delft Electroniache Producten, Netherlands, among others. In particular, image intensifier model no. XX-1451-J from Delft Electroniache Producten, may be used in the present ophthalmoscope.

Referring again to FIG. 3, visible displays 285, 285' photoelectrically convert the aerial image taken through lenses 265, 265' by means of imaging sensor 270, 270' and display images thereof on a display in accordance with such a photoelectric conversion. Where camera tubes or CCDs are used to convert the optical image into an electrical signal which represents the light intensities present in the optical image focused on the tube, the resulting display is a video image. Image tubes, such as image intensifiers, of course do not typically produce a video image. Rather, the fluorescent screen of the image intensifier directly displays the image to the observer without first converting the optical image into an electrical signal.

Color LCDs of approximately 1/3-3/4" diameter having, for example, a 0.01 mm dot pitch may be used and may be purchased from various manufacturers. Alternatively, monochrome LCDs as well as CRTs of similar dimensions may also be used, which are relatively less expensive than color LCDs. It is contemplated that the CRTs are preferably about 80 mm or less in length, which are widely sold by different manufacturers. In addition to visible displays 285, 285', a television monitor 290 may also be connected to at least one of the imaging sensor so as to display the fundus image for teaching purposes.

In the case of LCDs, on the back surface thereof there are provided preferably with back lights to illuminate the LCDs. Ocular lens 295, 295' may be used to expand the visible fundus images to a desired magnification, typically 5.times. or less. Ocular eyepieces 295, 295' may be movable along the optical axis a few millimeters, for example, by rotating a collar (not shown) so as to compensate for ametropia in the observer. Ocular lenses 295, 295' each provide a virtual image of the visible display image of the fundus image, preferably at or near infinity so that it can be comfortably viewed by a normal relaxed eye. Each, however, is along a different viewing axis.

Various types of ocular lenses may be used, such as Huygens, Ramsden, Kellner, Plossl, or Erfle eyepieces, which are all well known in the art. Simple magnifiers may also be used, such as doublets, and triplets. See, for example, Military Standardization Handbook--Optical Design, MIL-HDBK-141. Erfle eyepieces may be preferable since they are well corrected for most aberrations and have a comfortable eye relief.

Those skilled in the art will readily understand that ocular lenses 295, 295' are used to view and preferably magnify the fundus images displayed on visible displays 285, 285'. The distance of the patient's eye to ophthalmoscopic lens 170 will depend upon the power thereof, but will generally be in the range of about 25 to 50 cm. Also, for optimum stereopsis, the images of the imaging sensors must be separated from each other as far as possible while falling within the pupil of the eye to be examined, as depicted in FIG. 5. Furthermore, the image representing the light source should also strike the pupil of the eye and should be separated as far as possible from the images representing the imaging sensors so as to minimize unwanted reflections along the viewing axes of the ophthalmoscope. For polarized illumination, such as from a laser, polarizing filters, however, may be used to minimize any specular reflection off the cornea.

The binocular indirect ophthalmoscope of the present invention offers several advantages over prior art ophthalmoscopes. That is, images are not only viewed directly as binocular images using illumination of a desired spectrum, but are also acquired electro-optically, allowing them in certain cases to be stored in a video format for storage as well as real-time image processing. That is, well known digital image processing techniques may be used to delineate and enhance desired features of the fundus image in real-time. For example, signal processors 300, 300' may be optionally used to process video images from imaging sensors 270, 270', if available, and then display in real-time the enhanced images via displays 285, 285'. That is, by properly manipulating the appearance of the image, specific features become more visible to the observer.

The use of pattern recognition also enables fundus features in normal and diseased eyes to be delineated, such as hemorrhages, exudates, scars, and the like. Digital image processing techniques, include contrast enhancement, edge enhancement, noise reduction, scaling, rotating, and pseudo-coloring the fundus image, which are all well known in the art. See, for example, Digital Image Processing by Pratt, John Wiley & Sons, (New York 1978). One particular advantage of such image processing techniques, is the ability to provide electronically a non-inverted image to the observer without using bulky optics in the viewing assembly to do so. Also, the fundus image maybe zoomed independently of the power of ophthalmoscopic lens 170 by accordingly processing the video images from imaging sensors 270, 270', which processing may be performed in real-time.

Those skilled in the art will readily recognize that signal processors 300, 300' may include a micro-processor based device, A/D converters, control logic, software and other associated electronics. The construction of such devices is well known in the art and hence will not be discussed herein.

It should be clearly understood that the fundus image of the patient's eye is captured by the imaging sensors and preferably visibly displayed as a binocular image to the observer regardless of the wavelength of illumination chosen. For example using CCDs or image intensifiers, the infrared images of the fundus are converted to the visible part of the spectrum. Furthermore, proximity focused type image intensifiers may be used to generate non-inverted fundus images. FIGS. 8 (a)-(b) depict illustrative views (monocular) by the observer under visible and infrared illumination, respectively, uniformly impinging on the fundus. FIG. 8(b) illustrates the enhancement of the fundus features, particularly higher contrast and resolution, when illuminated by near infrared illumination. Such an illumination may also be desirable since the patient's pupil does not react to infrared light, thereby obviating the need to dilate the patient's pupil.

It may be also desirable to have a reticule or grid electronically displayed to the observer and aligned with the center of the viewing axis. This may be readily accomplished using the digital image processing capabilities of signal processor 300, 300' which can superimpose any desired image, such as reticules, grids, scales as well as previously recorded fundus images and the like.

Alternatively, the present binocular indirect ophthalmoscope may use an optical fiber bundle 310 to guide or direct the illumination radiation from light source 145 to illumination assembly 130, as illustrated in FIG. 9. In this latter embodiment, light source 145 may be located external to illumination assembly 130. For example, light source 145 may be secured to head assembly 105 in any suitable manner, such as near the rear of head band 110 or located within a housing several feet away. In the latter case, this results in a generally lightweight construction for the ophthalmoscope and further adds to the reduction of strain placed on the user.

Referring now to FIG. 10, there is illustrated another embodiment of the present invention, which is similar to the first embodiment and in which one rather than two imaging sensors are used. Similarly, mirrors 255, 255' focus on a single imaging sensor 1010 two independent non-overlapping images of the fundus of the patient's eye. It should be clearly understood that these images are still taken along two different viewing axes 305, 305' so as to permit stereoscopic viewing. Likewise, visible displays 285, 285' photoelectrically covert the non-overlapping fundus images and display images thereof to the observer through suitable ocular eyepieces. It is contemplated that the use of a single imaging sensor maybe more cost effective due to today's high cost of CCDs and image intensifiers. Furthermore, a single viewing display may be used, so long as two separate images taken along different viewing axes are displayed to the observer.

It should be understood that various other modifications will be readily apparent to those skilled in the art without departing from the scope and spirit of the present invention. For example, the electro-optic imaging and display system of the present invention may be used in direct ophthalmoscopes. Accordingly, it is not intended that the scope of the claims appended hereto be limited to the description set forth herein, but rather than the claims be construed as encompassing all the features of the patentable novelty that reside in the present invention, including all features that would be treated as equivalents thereto by those skilled in the art to which this invention pertains.