DE2544561B2 - Ophthalmic device - Google Patents

Description

The right field is the area of the fundus beyond which the device cannot reach. Through the invention also a simpler control (or regulation) and therefore also a more uniform lighting over the Fundus reached.

The device according to the invention enables very good observation and photography in one achieved a single image of the entire retina. In addition, the device requires much less expansion the test subject's pupil than conventional wide-angle devices. This is an ophthalmological examination possible in circumstances where this was previously due to restrictions on the permissible expansion, such as B. in subjects suffering from diabetes, was not possible.

The invention is explained in more detail with reference to the exemplary embodiments shown in the drawing. It shows

Ftp 1 srhpjTialicph im Tpilcphnilt

according to the invention,

Fig. 2 is a perspective view of a lighting cone according to the invention for use with a Fundus camera,

F i g. 3 shows, in an exploded view, different components of an ophthalmoscope according to FIG Invention,

4 shows in section an ophthalmoscope according to FIG Invention,

F i g. 5 shows an illustration to explain the course of the light from an optical fiber through an eye,

F i g. 6 schematically shows the illumination of a retina by means of two fiber lines according to the invention and

F i g. 7 shows, in section, a series of lenses for use in a fundus camera according to the invention.

The wide-angle ophthalmoscope and the fundus camera according to the first embodiment of FIG ι invention contains fiber optic light guides, short optical fibers or called optical fiber bundles, the exit ends or facets of which in two rings for Illumination of the retina are arranged. The two lighting rings work with a contact lens ίο together to create a wide-angle field of view that illuminates evenly through the fiber optic light guide or is illuminated. An important feature of the first embodiment of the invention is that Arrangement of the two lighting fiber rings c. the r, inclination of the fibers at the point of contact with the Cornea and the numerical aperture of the fibers.

A common feature of both the fundus camera according to FIG. 1 and the ophthalmoscope according to FIG

icl oino

Knro ΙΑ 'A ".!" - " tr.- ,!""J.; | " _C IIIIJl ■ »» I tllUVIV IUI UVI (Il Ugt

The essential components of ophthalmic devices are the two optical fiber rings 16 'and 18' of the fundus camera 12 or the light guide ring 16 and 18 of the Ophthalmoscope 14 in FIG. 4th

The contact lens 10 ′, 10 is preferably composed

> ■ -, (FIG. 4) or the lens I according to FIG. 7 from a glass with a refractive index / I ₁ / «2.1. Another glass that can be used to form the contact lenses 10 ', 10 has a refractive index ¹ na = 1.96052. Further design parameters of the contact lenses 10 ', 10.1 are given in Table A.

jo with R = radius of curvature, T = lens thickness. 5 = distance between opposite'-n lens surfaces.

Table A.

radius
R (mm)

thickness
7 "(mm)

Refractive index distance na 5 (mm)

Abbe number
(Dispersion)

R \ = 8.2 «2 = 10.2

Γ, = 9.2

2.1

S ₁ = 4.0

25.6

The contact lens 10, 10 ', I is a concavo-convex single lens and is arranged on a cornea positive focusing.

The diameter d \ of the section of the contact lens 10, 10 ', I which touches the cornea (see FIG. 1) is 8 mm. The usable area of this diameter d \ of the front side of the contact lens 10 ', 10. I is 7 to 8 mm. It should be mentioned that the dimensions given here are intended for an average eye. Of course, the parameters of the ophthalmic devices (ophthalmoscope, fundus camera) can be changed so that they can be used with subjects whose eye size differs from an average eye, such as a small child, since the teaching according to the invention gives all the indications that an ophthalmic Device for examining and / or photographing the retina of children or other test subjects with an eye that deviates from an average eye.

As stated, the devices according to the invention use optical fibers to illuminate the retina. Optical fibers, such as the optical fibers 38 (FIG. 4) or 38 '(FIG. 1), act according to the known principle of total internal reflection. A translucent elongated body with a smooth surface and a higher one Refractive index than its surroundings can transmit light fed in at one of its ends in such a way that it is with low losses due to the total reflection of the light rays diverging from the longitudinal axis of the body exits on the inner surfaces at the other end. To generate total reflection in all fibers exist This consists of a central glass core, which is covered by a glass cladding with a lower refractive index than the core is surrounded. Even if glass fibers are preferable, light-transmitting fibers can also be made from translucent Plastic can be used. The structure of dera .iger optical fibers made of glass or plastic is in itself known Since the optical fibers do not transmit an image in the devices according to the invention, but only for Illumination of the retina is used, the fibers do not need to be coherently arranged.

According to an embodiment of the invention Mantd fibers with a numerical aperture NA = 035 are used.

A major difference between the conventional and the inventive ophthalmic Devices, in particular the ophthalmoscopes and fundus cameras, consists in the fact that the devices contain according to the invention two rings of optical fibers, namely an outer ring 16 ', 16 and one Inner ring JS ', J8. In the illustrated example (cf. FIGS. 1, 4) the inner ring 18 ', 18 rests against the contact lens 10', 10 and surrounds it. To this

Thus the inner diameter of the inner ring is 18 ', 18 8 min. The inner ring 18 ', 18 is about 0.5 mm thick. Of the The outer diameter of the inner ring 18 ', 18 is dither 9 mm. The outer ring 16 ', 16 has from the inner ring 18', 18 a distance of about 0.5 mm. The inner diameter of the outer ring 16 ', 16 is therefore 10 mm. The one from the l.ichlleiifascrn of the outer ring 16 ', 16 educated king is cn. I mm thick, which is why the Outside diameter of the outer ring 16 ', 16 approx. 12 mm amounts to.

In FIG. 2 are the F-'ascrn of the two rings 16 ', 18' depicted greatly exaggerated. The single fibers. the clic I asemngc if) ', 18' can form a diameter of only about 0.05 mm.

(iemiiH of the invention and in the case of cheeses 38 one The | -! ndcn 20 of the optical fibers which form the inner ring 18, 18 'have a numerical aperture of 0.55 Angle with the contact lens axis of cn. 18 "to 24. Preferably, the cords 20 of the fibers form an angle of in with the axis of the contact lens 10, 10 '. I. (see Iig. 6).

The linden 22 of the äscin, which the outer ring 16, 16 ' form, have an angle with respect to the axis of the contact lens 10, 10 '. I from about 35 to 42. Preferably the linden 22 form a \ '. mkcl of 39 with the axis of the contact lens 10, 10 '. I. when lasing the numerical Aperture 0.55 can be used. The meaning of this alignment of the rings 16, 16 'and 18, 18' is shown in explained below.

The iliac difference between the ophthalmoscope 14 according to Γ i g. 4 and tier l'unduskamcra 12 according to I'ig. ι is that the ophthalmoscope 14 lenses 24, 26, 28 (C i g. 4) or II to Vl (Fig. 7) directly in the device are built in, while with the fundus camera 12 cmc corresponding lens series or an eyepiece that is in I ι g. 1 is shown schematically as lens 30. between a lighting cone 32 'and a camera 34 is arranged.

The required position or alignment of the optical fiber rings 16 ', 16, 18', 18 is explained in more detail with reference to FIGS. 3 and 4. The surface of the lens 10 with the radius R is at the front end of a lens mount 36 Optical fibers 38 are distributed in a fan shape over the lens barrel 36 and the side of the contact lens 10 to form a ring-shaped arrangement of the fibers 38 which is adhered or cemented to the contact lens 10 by means of an opaque or opaque epoxy resin The opposite surface of the contact lens 10 is geometrically designed in such a way that the ends of the fibers 38 form an angle of approximately 18 "to 24 ° to the axis of the contact lens 10. The lens mount 36 is preferably designed so that an angle of 20 ^{c is formed} for fibers 38 with a numerical aperture of 0.55. Subsequently, a spacer 42 is arranged on the contact lens 10 and the annular arrangement of the fibers 38 which form the inner ring 18. The spacer 42 is designed so that it has a conically inclined outer surface 44 which forms an angle of approximately 35 ° to 42 °, preferably 39 °, with the axis of the contact lens 10, the inner surface 45 being inclined at an angle, which corresponds to the angle of the ends 20 of the fibers 38 which form the inner ring 18. After the spacer 42 is in place, fibers 38 are spread over the inclined outer surface 44 of the spacer 42 in a fan shape to form an annular array and are glued or cemented thereto. Then a cone part 46 is for

Securing the above-mentioned arrangement is attached. The cone part 46 can be glued to the lens mount 36 or cemented: the two parts can also be secured to one another by means of a friction connection be. It is also advantageous to use the fanned-out F-laser array with an opaque synthetic resin button to cover them to the contact lens 10 and the Linsenfassiing 36 and the spacer 42 to secure. The casting resin can also be used to glue or cement the cone 46 to the lens mount 36 will. The front end 50 of this arrangement is ground to enclose the two light fiber rings 16, 18 to expose and to create a contact lens 10 that can be attached to a cornea due to its formation. The ophthalmoscope can also have an eyepiece or l.insenhaller 52, which holds the lens 28 and in the lens barrel 36 is screwed. The Linsenfassiing 36. the spacer 42, the Konusleil 46 and the I. Lens hallers 52 are preferably made of corrosion-resistant metal. In use observed a Observer the fundus of the eye via the rear end 54. The image of the fundus can be seen through suitable field lenses (not shown) can be enlarged between the rear side 54 and the observer.

Of course, the sealing cone 32 ' the fundus camera 12 according to FIG. I in the same way by gluing the contact lens 10 'to a lens mount 36'. by laying fibers 38 'over the Contact lens 10 '. by attaching a spacer 42 '. by laying fibers 38 'over the spacer 42 'and by attaching a Komiseils 46' are produced.

The fibers 38, 38 'emerge from the device through an opening in the conical part 46, 46'. taking a cable 56, 56 'into a conventional fiber optic lighting device 58 is plugged in. This causes light from the light source or the lighting device 58 (Fig. I) passed through the cable 56, 56 'into the device for illuminating the test subject's retina. For good ones For results, it is advantageous if the optical fibers in cables 56, 56 'are the same fibers as in the device, i. H. the fibers are 38,38 '.

The ophthalmological device according to the invention is not only constructed in such a way that it is with the organs in the eye is compatible, but that it also makes advantageous use of such organs. For example, the field of view is sufficient of a normal individual up to at least 90 "in an arc. That is, that of the observer's pupil emitted or emitted rays from all points of a field of about 180 ° in an arc kicking a non-dilated pupil and reaching points on the observer retina. Rays covering the retina Reaching from the nasal or nasal area of the field, meeting an area of the retina that is not is photosensitive. On the other hand, when the retina is illuminated, its points emit rays that when Passing through a non-dilated pupil containing a spatial image of the entire retina and one Form a fixed angle of around 180 ° in the curve. This allows a small pupil ophthalmoscope with a optimally corrected condenser or correction insc the observation of the peripheral retina by a not dilated pupil. In order to observe 150 ° of the retina in a single image, however, (at least) 150 ° of the retina can be illuminated without annoying reflections and must be the fixed angle that allows the Contains spatial image of the fundus, are aligned in order to allow simultaneous projection into the retina of the observer.

tcrs to enable.

To illuminate 150 ° of the retina without reflections and to correct the image of the fundus there are two rings 16 ', 18'; 16, 18 of illuminating fibers 38 ', 18 advantageous, v / ie this explained in more detail with reference to the optics of a cornea with reference to FIGS. 5 and 6 will.

F i g. 5 shows schematically the reflections by a crystalline lens ft0 of an eye 62 of the light transmitted through a fiber ring 64. Two locations on the fiber ring 64 are labeled A and B. The corresponding boundaries of the illuminating beam are indicated by thin volumes 66. The images of the points Λ and II on the front surface of the crystalline lens 60, which is considered here as a mirror surface, are designated with C and I) , respectively. The dashed lines 68, which begin at all images C and D , show the rays or bundles of rays containing reflections. The reflections from the places \ and //, which is formed by the iiiiiierfiiiche eier Kristalisitise öö. are marked with /: or / ■ '. Corresponding rays or bundles of rays that comply with the reflections are indicated by .Strichpunktlinien 70, which at Λ 'or. / ■ 'begin. As can be seen from FIG. ^The result is that the final pupil of the observation system must be arranged in the hatched area 72 in order to prevent reflections from penetrating the observer's eye. The fiber ring 64 must therefore be arranged on the robotic cornea so that Ideally, the fiber ring 64 has an inner diameter such that it is 4 mm from the axis 74 of the crystalline lens 66. Accordingly, it is advantageous that the fiber ring 64 of illuminating fibers have an inner diameter of 8 mm.

A second aspect when optimizing the field of view and the field of illumination is the inclination or the angle of inclination of the fiber ring 64. In the case of fibers with a high numerical aperture (0.66), in which the If the fiber ends are inclined below 30 "to the axis 74, the lighting field is approximately 100". With decreasing Winkel also decreases the lighting field. If the angle or numerical aperture of the fiber increases, however, light exiting the fiber ring 64 hits the front surface 76 of the crystalline lens 60. What is undesirable.

This front surface 76 is the entrance pupil for the observation system. A direct illumination of the The entrance pupil gives a reflection of the halo emitted by the fiber ring 64 and blurs the middle part of the image of the fundus. When the inside of the first fiber ring is 4 mm from the axis of the lens, which consists of fibers of the numerical aperture 0.55 and at the angle of 20 "to the Axis is inclined ', a field of 100 "is illuminated, without light emerging from the fibers passing through the entrance pupil with a radius of 1 mm (cf. FIG. 6). Through the second ring of fibers with a numerical aperture of 0.55 and an inner diameter of 10 mm from the axis of the lens and an inclination of 39 "to the axis is the ßeleiichtungfcld enlarged to 150 "without light emerging from the second ring onto the final pupil of the observation system hits or falls.

It should be noted that! the angle of inclination of the fibers is determined taking into account the numerical aperture of the lasers. If z. B. the numerical aperture 0.5). is the optimal angle for the fiber ends that form the inner ring. 20th However, when fibers of a numerical apeiuir be chosen from 0.6b, must be a wave! eggs Fiber ends that form the inner ring only have 12 amount to IOD ties icicles / ιι illuminate, iJ closer this device has a contact lens. which is surrounded by a fiber ring with an inner diameter of 8 mm. where the numerical aperture and the inclination of the fiber ends are chosen so that 100 of the field be illuminated and the final pupil is free from direct illumination. and that of a second Fiber ring is surrounded. which is so arranged and so inclined. that the periphery up to about 1) 0. in turn without direct illumination of the step pupil. is illuminated.

As mentioned, the ophihalmological device, such as the ophthalmoscope 14 or the fundus camera 12, can contain the lens series or the eyepiece 50 for aligning and focusing the fundus image after it has passed through the contact lens 10, 10 ′, I. The ophthalmoscope 14 has a first lens series. as shown in FIG. 4, built directly into the device and produces, together with the contact lens 10. I, two-fold magnification. The first lens series contains a lens 24 which is a doublet of a biconvex lens II in surface contact with a biconcave lens III. The second biconvex single lens 26 is removed from the doublet 24 with an ac .land S>. The second doublet 28 is at a distance Sj from the individual lens 26. The second double lens or doublet 28 contains a convex-concave lens V in surface contact with a lens V1 which is convex-concave in the forward direction. The lens parameters are given in Table B. A minus sign means a center point radius or a curvature that lies on the object side of the corresponding vertex.

Table B. Radius. R. Thickness. T Distance. S. Refractive index Abbe number
(Dispersion) lens R, = -76.3872 mm
R ₄ = 33.2181 mm T ₂ = 12 mm 1.85026 32.23 II R ₅ = 33.2181 mm Tj = 3 mm Sb = 5 mm 1.5168 64.17 III Rf ₁ = -963680 mm
K ₇ = 38.2638 mm Ta = 10 mm Si = 4 mm 1.4645 65.77 IV K ₈ = 109316 mm
Rq = 9i, 6508 mm Γ5 = 4 nm 13168 64.17 V / ?, o = 1260.0548 mm Tb = 8 mm 1.7215 29.25 VI

Il

Di <! Film camera 12 according to FIG. 1 contains a corresponding lens series or the eyepiece 30 / for use together with the contact lens 10 'and a camera 34 with (for example) 50 mm focal length. This Unscnscric together with the contact lens 10 'generates a magnification of 1.8 of the picture to be photographed. The Linsenscric is shown in Fig. 7 and contains a doublet with a biconvex lens II in

Table C.

Surface contact with a biconcave lens III at a distance S \ from the contact lens 10 '. A planoconvex lens IV is arranged at a distance .V> from the lens III, and a doublet of a biconcave lens V in surface contact with a biconvex lens Vl is from the lens IV at a distance .S3. Dip Linsenparaiiietcr are given in Table C.

.inse Kadiiis . H Thickness. r Distance. S. Hrcc'h / iihl Abbe number
(Dispersion) Il / ?. =
R, - 36 576 mm
I127.76I11H1 T ₂ = 20 mm ■ V | = 1.85026 32.23 IV K-, =
R _h =
Ri = - 1516.J8 111111
OO
1684.02 mm T ₁ -
/, ~ 6 mm
I 5 now ■ V- =
• S'i = 1.5168
1.4645 64.17
65.77 V A »=
Ri = 4191.0 mm
-4292.6 mm T; = 6 mm 1.5168 64.17 Vl Ru, = 2407.92 mm γ _ 20 111111 1.7215 29.25 = 23 111111 = 30 mm
= 20 mm

I lici / u.> IiInII / eicliiuiiucn

Claims (12)

Patent claims: 1. Ophthalmic device, with a contact lens, through which the inside of the eye can be observed, and with first optical fibers, the ends of which form one The first ring surrounding the contact lens and opposite the cornea, thereby marked, that the ends of second optical fibers (38, 38 ') form a second ring (16, 16') which extends outwards at a distance from the first ring (18, 18 ') and opposite the cornea, that the first optical fibers on the one hand form the first ring (18, 18 ') with a first radius and on the other hand end in this at a first angle that the first ring (18, 18 ') the central part of the field of view of the contact lens (10, 10 ') is illuminated and the entrance pupil (72) of the Observation system is not directly illuminated, and that the second optical fibers (38, 38 ') such on the one hand form the second ring (16, 16 ') with a second radius and on the other hand in this end at a second angle that the second ring (16, 16 ') the periphery of the field of view illuminated and the entrance pupil (72) is not directly illuminated. 2. Apparatus according to claim 1, characterized in that the inner diameter of the first ring (18, 18 ') is 7 to 8 mm 3. Apparatus according to claim 2, characterized in that the inner diameter of the first ring (18, 18 '; 64) is approx. 8 mm. 4. Apparatus according to claim 3, characterized in that that the numerical aperture of the optical fibers (38, 38 ') 0.55 and the first angle approx. 18 ° to 24 ° r> be. 5. Apparatus according to claim 4, characterized in that the first angle is 20 °. 6. Apparatus according to claim 4 or 5, characterized in that the second angle is approximately 35 ° to 42 ° 7. Apparatus according to claim 6, characterized in that the second angle is 39 °. 8. Apparatus according to claim 7, characterized in that the outer diameter of the first ring (18, 18 ') is 9 mm, that the difference between the inner diameter of the second ring (16, 16') and the outer diameter of the first ring (18, 18 ') is 0.5 mm, and that the second ring (16, 16') I mm thick. 9. Apparatus according to any one of claims 1 to 8, characterized in that the first angle is through the geometric shape of the contact lens (10) is determined, that a spacer (42, 42 ') is arranged over the first optical fibers (38, 38') that the second optical fibers (38, 38 ') are arranged on the spacer (42, 42'), and that the spacer (42, 42 ') has an outer surface (44, 44') inclined for the second angle 10. Device according to one of the claims'. till 9, characterized in that the device is an ophthalmoscope (14). 11. Apparatus according to claim 10, characterized by a first doublet (24) of lenses at a first distance (Si) from the contact lens (10, I), one lens being a biconvex lens (II) in surface contact with a biconcave lens (Hl),
a biconvex single lens (26, IV) at a second distance (S ₂ ) from the biconcave lens (III).
a second doublet (28) of two convex-concave lenses (V, Vl) in surface contact and with a third distance (Sj) from the single lens (IV),
where the individual lenses (1-VI) have the following parameters (Fig. 4): Radius, r Thickness. T Absland, S. Refractive index Abbe number (Dispersion) III
IV R ₁ = 8.2 mm
R ₂ = 10.2 mm 7Ϊ = 92 mm 4.0 mm 2.1 25.6 Rj 763 872 mm
R ₄ = 33.2181 mm T ₂ = 12 mm 1.85026 32.23 R ₅ = 33.2181 mm Tj = 3 mm S ₂ = 5 mm 1.5168 64.17 R ₆ = -963680 mm
R ₇ = 38.2638 mm Ta = 10 mm S) = 4 mm 1.4645 65.77 R » = 109.2916 mm
R ₉ = 91.6508 mm Ά = 4 mm 1.5168 64.17 / ί, ο = 1260.0548 mm Tt = 8 mm 1.7215 29.25 12. Device according to one of claims I to 9, characterized in that the device is a fundus camera (12) in which a conical part (46 ') is connected via an eyepiece (30) to a camera lens (34), the conical part (46 ') the Contains contact lens (10 ') through which the eye can be photographed (Fig. I). I). Device according to claim 12, characterized in that that with a camera lens (.34) mn h ^r ) 50 mm focal length the eyepiece (30) has:
a first doublet of lenses disposed in a first distance (Sj) from the contact lens (10 ', I), one lens being a biconvex lens (II) in face to face contact with the other lens, which is a biconvex lens (lti) , a plano-convex single lens (IV) at a second distance (S ₂ ) from the biconcave lens (II I),
a second doublet from a convex-concave lens (V) in surface contact with a biconcave lens (VI) at a third distance (Si) from the single lens (IV), where the individual lenses (I -Vl) are as follows Have parameters (Fig. 7): lens Radius, r Thick, T Distance, p Refractive index Abbe number
(Dispersion) I. R \ = 8.2 mw
R ₂ = 10.2 mm Ti = 9.2 mm 2.1 25.6 Il R ₁ = 36 576 mm
Ra = 1127.76 mm T ₂ = 20 mm 5, = 1 ^ 5026 32.23 III A ₅ = -151638 mm Tj = 6 mm S ₂ = 1.5168 64.17 IV R ₆ = oo
A ₇ = 1684.02 mm Ti = 15 mm S ₃ = 1.4645 65.77 V Rs = 4191.0 mm
A ₉ = 4292.6 mm Ti = 6 mm 1.5168 64.17 VI Rio = 240752 mm Tf, = 20 mm 1.7215 29.25 = 23 mm = 30 mm = 20 mm The invention relates to an ophthalmological device >> according to the preamble of claim 1. Ophthalmological devices of this type are used for examination, observation and / or in particular photographic record of the inside of an eye and are preferably ophthaimoscopes (ophthalmoscopes) «> or fundus cameras (retinal or fundus cameras). A conventional ophthalmoscope (see. DE-OS 22 22 378) and a conventional fundus camera have optical or optical fibers that are in a j> Contact lenses are built in a circle and form a single ring around the contact lens. This one Ring can also consist of several adjoining ends of optical fibers radially (cf. FR-PS 15 83 436). The ring is opposite the 4i> Contact lens firmly aligned. For a ring with a numerical aperture of at least 0.66 it is now advantageous to align this so that the fibers form an angle of 25 ° to 35 ° with respect to the axis of the Form contact lens. In the case of an ophthalmoscope or π a fundus camera with such a fiber ring high numerical aperture can be 100 ° of the fundus or fundus of the eye are illuminated or illuminated. The ßelcuchtungsfcld can but without any harmful effects when using ίο conventional optical fibers, they cannot be enlarged any further. It is therefore the object of the invention to provide an ophthalmological device, in particular an ophthalmoscope and a Funduskarnera, to create whose lighting field is so great that the eye will begin with a Vj Field of view in front of at least approx. 150 ° without scanning with conventional optical fibers as Bcleuehiungsqucllen can be observed or recorded. The solution to this problem is through the features of the characterizing part of claim I bo given. The invention enables an uphihalmological Device that, with conventional optical fibers, has a comparatively low numerical aperture (at least) 150 ° of the fundus is illuminated, so that a field of view of 150 ° can be observed or without scanning can be signaled. For this purpose, the ophthalmic device contains a contact lens that is placed on the cornea of the test person (e.g. the patient) put on v, ird and surrounded by two separate optical fiber rings is. The alignment and the numerical aperture of the optical fibers forming the Riiige are determined so that a maximum area of the fundus is illuminated, without the light from the optical fibers on the front surface of the entrance pupil of the person to be examined Eye hits. The invention thus sees z. B. an indirect wide angle ophthalmoscope propose having a contact lens to be placed over a cornea that of two Optical fiber rings for illuminating the fundus is surrounded. The two fiber rings are to be raised the illumination of the fundus while avoiding harmful reflections. The first or Inner ring is formed from fibers of a numerical aperture and inclined so that 100 ° of the retina or Retina to be illuminated. The outer or outer ring of fibers illuminates the edge area or the Periphery of the retina up to 150 °. The arrangement and the inclination of the rings are calculated so that one Blocking of the entrance pupil of the re-observation system is prevented, direct illumination of the entrance pupil being avoided. One with the ophthalmic device Lens series or an eyepiece to be used with the contact lens is specified in the claims. Further in the claims is a fundus chamber made up of the contact lens, the two optical fiber rings and the lens series or Jem eyepiece together with a Kaiucra with 50 mm focal length. In one embodiment of the invention, an ophthalmological device has a special lighting device, to illuminate the fundus of the eye in such a way that interference or harmful effects are avoided are diminished when observing the fundus through the crystalline lens of the eye. The invention provides an ophlhalmologische.es Wide-angle device with a very large field of view and a very large observable field compared to conventional ones Devices. The field of view is the area of the fundus that is exposed by the observer or the Observation device is captured in a single image in every direction of observation, and the observable