fig1 shows a ophthalmoscope with a solid state camera . the illumination system is the ring light source 7 . the viewing optical path includes a solid state surface sensor 9 located in the imaging plane and having a viewing optical system 6 positioned in front of it . the viewing optical path and the illuminating optical path are on one optical axis , the ophthalmoscope lens 5 being shared . the light emitted by the ring light source 7 is assumed to be approximately parallel . the ring light is projected through the ophthalmoscope lens 5 onto the cornea 4 of the patient &# 39 ; s eye 1 . the ring light projected on the cornea 4 scatters light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system 6 , which in the simplest case comprises an imaging device including an objective with a solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system 6 . fig2 shows a ophthalmoscope having an eyepiece . the illumination system is the ring light source 7 . the viewing optical path includes an eyepiece 10 located in the imaging plane . the viewing optical path and the illuminating optical path are identical , the ophthalmoscope lens 5 being shared . the light emitted by the ring light source 7 is assumed to be approximately parallel . the ring light is projected through the ophthalmoscope lens 5 onto the cornea 4 of the patient &# 39 ; s eye 1 . the ring light projected on the cornea 4 scatters light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . the intermediate image becomes visible to the observer through the viewing optical system 6 and through an eyepiece 10 . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system 6 . fig3 shows an ophthalmoscope having a variable ring light . the illumination system is the ring light source 7 . the viewing optical path includes a solid state surface sensor 9 located in the imaging plane . the viewing optical path and the illuminating optical path are identical , the ophthalmoscope lens 5 being shared . the light emitted by the ring light source 7 is assumed to be approximately parallel . the ring light is projected through the ophthalmoscope lens 5 onto the cornea 4 of the patient &# 39 ; s eye 1 . the diameter of the ring light 7 is variably adjustable , as a result of which one can set it to the width of the iris . the diameter 13 is set in such a way that , on the one hand , no interfering reflections of the cornea detrimentally affect the image being formed and , on the other hand , the brightness or the contrast of the image being formed are optimal . the ring light projected on the cornea 4 scatters light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system , which in the simplest case comprises an objective with a solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . fig4 a through 4 e show several exemplary alternative configurations of the ring light 1 . fig4 a shows a ring light including a plurality of leds 30 , each having a constant wavelength and small radiation angle . for example , the leds may be white for color fundus images , green , 550 nm for high - contrast black - and - white fundus images ( as used herein 550 nm means approximately 550 nm ), blue , 490 - 500 nm as excitation light for fluorescence angiography ( as used herein 490 - 500 nm means approximately 490 - 500 nm , or ir , 880 - 920 nm as excitation light for icg angiography ( as used herein 880 - 920 nm means approximately 880 920 ). the approximate values extend to values above and below the stated values that differ insubstantially in effect . fig4 b shows a ring light having leds 30 , 31 having with different wavelengths . the leds of different wavelengths can always be arranged alternatingly , or else multi - colored leds are used , different examination methods being possible with one arrangement . fig4 c shows optical fibers 32 arranged as a ring . in order to be able to carry out several examination methods , an arrangement is proposed in which the light of a halogen lamp 33 is conducted through appropriate filters and condensers into the optical fiber bundle 34 . fig4 d shows a ring light source 35 including a taper made either of glass or of pmma . the source can be a halogen lamp or several leds of different wavelengths . fig4 e shows an led matrix 36 . due to the matrix arrangement of the illuminating leds , it is possible to set different ring diameters . moreover , elliptical illumination can be generated . through an evaluation of the fundus image being formed , the ring light can be actuated dynamically in the x and y directions and the ring diameter can be varied . fig5 shows an ophthalmoscope with a solid state camera and ring light via a pinhole mirror . the illumination system is a ring light source 7 . the viewing optical path includes a solid state surface sensor 9 located in the imaging plane . the light emitted by the ring light source 7 is assumed to be approximately parallel . the light of the ring light source is reflected in the direction of the ophthalmoscope lens of the main optical axis of the system via a pinhole mirror 14 arranged at 45 °. this arrangement has the advantage that it allows greater freedom in terms of the ring light diameter . moreover , it is conceivable that several ring lights of different diameters and wavelengths can be provided . an led matrix having very fine structures can also fulfill a ring light function . the ring light is projected via the pinhole mirror 14 and the ophthalmoscope lens 5 onto the cornea 4 of the patient &# 39 ; s eye 1 . the ring light projected on the cornea 4 scatters light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system 6 , which in the simplest case comprises an imaging device having an objective with a solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system , or imaging device 6 . fig6 shows an ophthalmoscope with solid state camera ring light via a pinhole mirror , in a non - mydriatic arrangement . the illumination system is a split ring light source 7 . either every other led radiates at the same wavelength or else two light rings ( as in fig4 b ) are provided . the light emitted by the ring light source 15 or 16 is assumed to be approximately parallel . the ring light source is reflected into the imaging optical system via a pinhole mirror 14 arranged at 45 °. two ring light arrangements are proposed , ir - leds 15 and white leds 16 . the non - dilated eye of the patient fundamentally reacts to visible light . illuminating the fundus of the eye with infrared light allows a preliminary examination of the retina . unfortunately , the images formed do not have a high contrast and are only possible in black - and - white ; color images can be taken with a flash in the visible spectrum since the iris only contracts after the flash is over . this method is generally known . according to the invention , the ring light arrangement is divided , with the white leds 16 only functioning in flash operation and the ir - leds 15 serving for a preliminary examination of the fundus of the eye . the ring light is projected onto the cornea 4 of the patient &# 39 ; s eye 1 via the pinhole mirror 14 arranged at 45 ° and through the ophthalmoscope lens 5 . the ring light projected on the cornea 4 scatters light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system 6 , which in the simplest case comprises an imaging device with an objective with a solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system or imaging device 6 . two solid state cameras are provided , an ir - sensitive camera 17 serving for the preliminary examination , and a color camera 9 ( e . g . re - start camera synchronous to the flash ) serving to photograph the fundus of the eye . here , the cameras can be coupled into the viewing optical path either via a partially transparent mirror 18 or via a hinged mirror 18 that briefly swings out when the snapshot is made . fig7 shows an ir ophthalmoscope with an optical path angled relative to the eye and solid state camera . the illumination system is a ring light source 7 . the viewing optical path consists of an ir - sensitive solid state surface sensor 9 located in the imaging plane and having a viewing optical system or imaging device 6 . the two optical paths are identical , the ophthalmoscope lens 5 being shared . the light emitted by the ir ring light source 7 is assumed to be approximately parallel . the ring light is projected onto the cornea 4 of the patient &# 39 ; s eye 1 through the ophthalmoscope lens 5 of the ir - blocking filter 19 which , at the same time , reflects the infrared light almost completely . the ring light projected on the cornea 4 scatters the ir light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system 6 , which in the simplest case comprises an imaging device with an objective with an ir - sensitive solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system or imaging device 6 . the eye of the patient looks through an ir - blocking filter 19 arranged at an angle of 45 ° with respect to the viewing axis , said ir - blocking filter 19 serving , at the same time , as an ir mirror , that is to say , the ir ophthalmoscope can be used to view the retina without disrupting the view of the patient . this technique can be used in electro - physiological examinations ( e . g . electroretinogram ). the patient looks at stimulating patterns , either on a monitor 20 or a light matrix 20 , the observer views the retina of the patient and can evaluate its position . since it is known that low - contrast images are obtained when ir - illumination of the fundus of the eye is used , an on - line reworking of the camera signal is proposed and it is also possible to use false - color technology . fig8 shows an ir ophthalmoscope with an optical path angled relative to the eye and solid state camera for viewing one &# 39 ; s own retina . the illumination system is a ring light source 7 . the viewing optical path consists of an ir - sensitive solid state surface sensor 9 located in the imaging plane and having a viewing optical system or imaging device 6 . the two optical paths are identical , the ophthalmoscope lens 5 being shared . the light emitted by the ir ring light source 7 is assumed to be approximately parallel . the ring light is projected onto the cornea 4 of the patient &# 39 ; s eye 1 through the ophthalmoscope lens 5 of the ir - blocking filter 19 which , at the same time , reflects the infrared light almost completely . the ring light projected on the cornea 4 scatters the ir light into the inside of the eye 1 . the retina 2 constitutes an illuminated object . the eye lens 3 images the retina 2 into infinity and the ophthalmoscope lens 5 focuses it in an intermediate image plane 8 . a viewing optical system 6 , which in the simplest case comprises an imaging device with an objective with an ir - sensitive solid state surface sensor 9 , is needed in order to be able to make the intermediate image visible or to capture it . any unsharpness in the image is compensated for in the direction of the main optical axis by a fine focusing drive 11 of the viewing optical system or imaging device 6 . the observer 22 looks at a video monitor 21 through an ir - blocking filter 19 arranged at an angle of 45 ° with respect to the viewing axis , said ir - blocking filter 19 serving , at the same time , as an ir mirror . the signal 23 of the solid state surface sensor 9 is reproduced in the monitor 21 . the observer 22 sees his own retina . since it is known that low - contrast images are obtained when ir - illumination of the fundus of the eye is used , an on - line reworking of the camera signal is proposed and it is also possible to use false - color technology .
a fundus camera includes a viewing optical path , an imaging device , and an illuminating optical path including at least one led and a pinhole mirror reflecting the at least one led into the imaging device , wherein at least a portion of the illuminating optical path shares an optical axis with at least a portion of the viewing optical path , and wherein the at least one led includes a plurality of leds disposed in a shape of a ring .