JPH1080397A - Apparatus for dentistry - Google Patents

Abstract

PROBLEM TO BE SOLVED: To improve accuracy of detection on alignment and to enlarge a detectable range by a constitution wherein an XY alignment detecting means has the first light receiving means, the second light receiving means and a correcting means for correcting information from the first light receiving means based on information from the second light receiving means. SOLUTION: An reflected image reflected on a cornea C is guided to an objective lens 4 after passing through a half mirror 3. A part of a target light collected by the objective lens 4 is reflected by the half mirror 5 and is guided to a two-dimensional PSD (a solid position detecting element) as the first light receiving means constituting a part of an XY alignment detecting system 20. The remaining target light which passed through the half mirror 5 is guided to a CCD camera 6 as the second light receiving means. The CCD camera 6 is used too as an XY alignment detecting means. Positional information on an image of luminous point on the PSD 21 and positional information on an image of luminous point on the CCD camera 6 are inputted into an XY alignment detecting circuit 22.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmic apparatus, such as a corneal endothelial cell observation / photographing apparatus and a non-contact tonometer, which require the eye to be examined and the apparatus to be aligned in a predetermined positional relationship.

[0002]

2. Description of the Related Art A device for observing and photographing corneal endothelial cells in a non-contact manner has been known (Japanese Patent Publication No. 7-12125).
No. 5). In this type of ophthalmic apparatus, an index light for alignment is projected from an oblique direction to an eye to be inspected, and light reflected by a cornea of the eye to be inspected is received from a direction symmetrical with respect to an axis of the eye to be inspected. Alignment detecting means for detecting a positional relationship in the front-rear direction (Z direction) with respect to the target, projecting an index light from the front to the eye to be inspected, receiving reflected light from the cornea from the front, and detecting the eye and the apparatus body XY alignment detecting means for detecting positional information in the vertical and horizontal directions (X and Y directions) of the XY alignment. The XY alignment detecting means is required to detect the absolute position information and shorten the detecting time.
A dimensional PSD is used in practice.

[0003]

SUMMARY OF THE INVENTION However, PSD
(Position sensitive device)
Is for detecting the position of the center of gravity of light incident on the PSD, and is easily affected by disturbance. For example, when the indicator light is projected from the front to the eye to be examined and the reflected light from the cornea of the eye to be examined is received from the front, the pupil is included in the PSD in addition to the index image due to corneal surface reflection (hereinafter referred to as signal light). Light reflected from the fundus passing through the inside, reflected light from the sclera and the iris (hereinafter referred to as background light) is incident. The background light is considerably smaller than the signal light in terms of light intensity, but is widely distributed in the PSD, and becomes a noise in the PSD for detecting the position of the center of gravity of the incident light, and has a non-negligible effect. Further, since the background light blinks at the same wavelength and the same cycle as the signal light, it is difficult to separate the background light from the signal light. That is, this P
The relative position information detected by the SD has a detection error.

In place of the PSD, a CCD (charge coupl
If a solid-state imaging device capable of detecting the light intensity distribution is used as in the case of an ed device, it is possible to remove the background light and detect only the signal light by setting a threshold value for the light intensity. However, the detection by the CCD requires at least about 20 milliseconds as the alignment detection time, which hinders the operation of the apparatus equipped with an imaging optical system controlled at high speed and various correction mechanisms. At the same time, the measurement accuracy of the device is reduced, and the burden on the examiner and the examinee is greatly increased.

To prevent the background light from being incident on the PSD, the diameter of the luminous flux of the index light may be reduced to minimize the reflected light from the sclera, the iris and the like. Then, the reflected light of the index light is P
There is a case where SD is not reached. Hereinafter, the reason will be described.

FIGS. 9A to 9C show an alignment optical system 70. FIG. The alignment optical system 70 has a half mirror 71, an objective lens 72, and a PSD 73. FIG. 9A shows a state in which the cornea C and the device main body are aligned,
FIG. 9B shows a state in which the apex P of the cornea C and the apparatus main body are misaligned, and FIG. 9C shows a state in which the apex P of the cornea C and the apparatus main body are misaligned and the index light is not reflected. This shows a state where the light beam diameter is small.

9 (a) to 9 (c), the index light K converted into a parallel light beam by an index light projection optical system (not shown) for projecting the index light is reflected by the half mirror 71, and the surface of the cornea C is exposed. It is led to T. Index light K projected on cornea C
Is reflected by the corneal surface T such that a bright spot image R is formed at an intermediate position between the vertex P of the cornea C and the center of curvature of the cornea C. The reflected index light passes through the half mirror 71, is condensed by the objective lens 72, forms an image on the PSD 73, and forms an image R ′ corresponding to the bright spot image R at the center.

If the beam diameter of the index light K is sufficiently large (see FIGS. 9 (a) and 9 (b)), the reflected light from the cornea C will not be displaced between the cornea C and the apparatus body. Of course, even if there is a position shift, part of the position returns to the optical path, so that an image is formed on the PSD 73 by the objective lens 72 and the alignment state can be detected. However, when the beam diameter of the index light K is small (see FIG. 9C), the cornea C
If the relative position of the reflected light is greatly deviated, the reflected light is reflected in a direction deviating from the optical path.
No incident on 2. Therefore, the reflected light does not reach the PSD 73, and the alignment state cannot be detected.

As described above, when the diameter of the index light projected onto the eye E to be inspected is reduced to reduce the background light and to improve the detection accuracy of the alignment, the position of the eye E is moved vertically or horizontally. If there is a large deviation, the light reflected by the cornea C does not enter the light receiving optical system, and as a result, there is a problem that the alignment detectable range becomes narrow.

SUMMARY OF THE INVENTION The present invention has been made in view of the above circumstances. It is an object of the present invention to set a wide alignment detectable range and reduce the alignment detection time without lowering the alignment detection accuracy. It is an object of the present invention to provide an ophthalmologic apparatus that can reduce the time, and can significantly reduce the burden on the examiner and the subject.

[0011]

According to a first aspect of the present invention, there is provided an ophthalmologic apparatus, comprising: an index light projecting unit configured to project alignment light onto an eye to be inspected; X that receives a reflection image from the cornea of the subject and detects the relative positional relationship between the eye to be inspected and the apparatus body in the vertical and horizontal directions.
An ophthalmologic apparatus having a Y alignment detecting means;
The XY alignment detecting means includes: first light receiving means;
The second light receiving means, characterized by having a correction means for correcting the information from the first light receiving means based on the information of the second light receiving means, preferably, the first light receiving means The light receiving unit includes a light receiving element that obtains the position of the eye to be examined by obtaining the position of the center of gravity of the incident light including the corneal reflection light of the index light, and the second light receiving unit detects a light intensity distribution. And a second light receiving element for detecting the position of the eye to be examined by extracting a corneal reflection image of the index light based on a set predetermined threshold value. Preferably, the first light receiving means uses a two-dimensional PSD as a light receiving element, and the second light receiving means uses a two-dimensional CCD as a light receiving element.

According to the first aspect of the present invention, accurate alignment detection is possible even when the first light receiving means having a detection error based on the background light is used, and the measurement time can be reduced. In addition, since the alignment detectable range can be set wide without lowering the alignment detection accuracy, the burden on the examiner and the subject can be significantly reduced.

An ophthalmologic apparatus according to a fourth aspect is the ophthalmologic apparatus according to the first aspect.
3. The apparatus according to claim 3, further comprising Z alignment detecting means for detecting a relative position between the subject's eye and the apparatus main body in the front-rear direction, wherein the apparatus main body is controlled based on information detected by the Z alignment detecting means and the XY alignment detecting means. It is characterized by comprising a driving means for automatically driving. An ophthalmologic apparatus according to a fifth aspect is characterized in that, in the third or fourth aspect, the two-dimensional CCD is also used as an anterior segment observation optical system for observing the anterior segment of the subject's eye. .

[0014]

Embodiments of the present invention will be described below with reference to the drawings. In FIG. 1, reference numeral 1 denotes an anterior ocular segment observation optical system. The anterior eye observation optical system 1 is disposed on the left and right of the eye E to be inspected, and a plurality of infrared illumination light sources 2 for directly illuminating the anterior eye, a half mirror 3, an objective lens 4, a half mirror 5, a CCD camera. 6, a light shielding plate 7 is provided. The reflected image of the subject's eye E from the anterior segment is guided to the CCD camera 6 via the half mirror 3, the objective lens 4, and the half mirror 5, and the anterior segment image is formed on the imaging surface of the CCD camera 6. . The CCD camera 6 outputs an image signal to a monitor device (not shown), and an anterior eye image E ′ is displayed on the screen 8 of the monitor device, as shown in FIG. The light shielding plate 7 is retracted from the optical path of the anterior ocular segment observation optical system 1 at the time of observing the anterior ocular segment and inserted into the optical path at the time of corneal endothelium imaging.

In FIG. 1A, reference numeral 10 denotes an index projection optical system. The index projection optical system 10 includes a light source 11 that emits infrared light, a condenser lens 12, an aperture stop 13, a pinhole plate 14, a dichroic mirror 15, and a projection lens 16. The pinhole plate 14 has a role of forming an alignment index, and the focal point of the projection lens 16 matches the position where the pinhole plate 14 is provided. The aperture stop 13 is provided at a position conjugate with the vertex P of the cornea C of the eye E with respect to the projection lens 16. The projection lens 16 forms a part of the fixation target optical system 17. The fixation target optical system 17 includes a fixation light source 18 that emits visible light, and a pinhole plate 19.
The pinhole plate 19 is disposed at the focal position of the projection lens 16, and the fixation target light emitted from the fixation light source 18 passes through the pinhole plate 19 and the dichroic mirror 15, and is then converted into a parallel light beam by the projection lens 16. The converted light is reflected by the half mirror 3 and guided to the eye E. The subject gazes at the fixation target light to fix his / her gaze.

The infrared light emitted from the light source 11 is condensed by a condenser lens 12, passes through an aperture stop 13, and is guided to a pinhole plate 14. The light beam that has passed through the pinhole plate 14 is reflected by the dichroic mirror 15 and guided to the projection lens 16. The projection lens 16 converts the light beam passing through the pinhole plate 14 into a parallel light beam, and the parallel light beam is reflected by the half mirror 3 and projected on the cornea C as index light for XY direction alignment detection. The index projection optical system 10 plays a role of projecting the XY direction alignment detection index light toward the cornea C of the eye E to be inspected. The index light projected onto the cornea C is, as shown in FIG.
Is reflected at the surface T of the cornea C such that a bright spot image R is formed at an intermediate position MP between the vertex P of the lens C and the center of curvature MR of the cornea C.

The image reflected by the cornea C passes through the half mirror 3 and is guided to the objective lens 4. The objective lens 4 is also used for the XY alignment detection system 20. A part of the index light condensed by the objective lens 4 is reflected by the half mirror 5 and guided to a two-dimensional PSD 21 as a first light receiving unit constituting a part of the XY alignment detection system 20. Details of the two-dimensional PSD 21 will be described later.

The remaining index light transmitted through the half mirror 5 is guided to a CCD camera 6 as a second light receiving means. A bright spot image R2 is formed on the imaging surface of the CCD camera 6. The CCD camera 6 is also used as an XY alignment detecting means, and its details will be described in detail. In FIG. 2A, a bright spot image corresponding to the bright spot image R2 is shown as a symbol R2 '. In FIG. 2A, reference numeral 24a denotes an auto-alignment mark generated by an image generating means (not shown);
Is a mark indicating an allowable alignment range.

In FIG. 1B, reference numeral 30 denotes a photographing illumination optical system. The photographing illumination optical system 30 includes a photographing illumination light source 31, a condenser lens 32, a slit plate 33, a dichroic mirror 34, an aperture stop 35, and an objective lens 36. For example, a xenon lamp is used as the photographing illumination light source 31. The dichroic mirror 34 has a role of transmitting visible light and reflecting infrared light. The aperture stop 35 is conjugate with the cornea C with respect to the objective lens 36. The dichroic mirror 34 is also used as a part of the illumination optical system 40 for Z alignment detection. The illumination optical system 41 for Z alignment detection includes a light source 41, a condenser lens 42, a slit plate 4
3 The light source 41 emits infrared light. The infrared light emitted from the light source 41 passes through the slit plate 43 while being converged by the condenser lens 42, becomes slit light, is reflected by the dichroic mirror 34, is guided to the aperture stop 35, and transmits through the aperture stop 35. After that, the objective lens 3
6 illuminates the cornea C while being guided by the cornea C while being focused. The visible light emitted from the photographing illumination light source 31 is condensed by a condenser lens 32 and guided to a slit plate 33, and the visible light passing through the slit plate 33 passes through a dichroic mirror 34 as slit light and is similarly transmitted. Aperture stop 3
5, the cornea C is illuminated from an oblique direction by the objective lens 36.

Reference numeral 50 denotes a photographing optical system. The photographing optical system 50 includes a photographing illumination optical system 3 with respect to the optical axis of the eye E to be inspected.
It has a role of receiving reflected light from the endothelial cells of the cornea C of the eye E and observing the corneal endothelial cells from an oblique direction substantially symmetric to 0. The photographing optical system 50 includes an objective lens 51, a dichroic mirror 52, a mask 53, a mirror 54, a relay lens 55, a light shielding plate 56, and a mirror 57. The dichroic mirror 52 has a function of reflecting infrared light and transmitting visible light. The mirror 57 is disposed at a position that does not hinder the anterior segment observation light beam, and is tilted at the same angle as the tilt angle θ on the object side (the eye E side).

The slit light beam L emitted by the photographing illumination optical system 30 is reflected by the cornea C as shown in FIG. Part of the slit light beam L is first reflected on a corneal surface T which is a boundary surface between the air and the cornea C. Further, a part of the light beam transmitted through the corneal surface T is reflected by the corneal endothelial cell surface N. The light amount of the reflected light beam T 'from the corneal surface T is the largest, the light amount of the reflected light beam N' from the corneal endothelial cell surface N is relatively small, and the light amount of the reflected light beam M 'from the corneal stroma M is the smallest. The reflected light flux is transmitted through the dichroic mirror 52 while being condensed by the objective lens 51, and is once imaged on the mask 53. Further, extra reflected light fluxes T ′ and M ′ other than forming a corneal endothelial cell image are blocked by the mask 53,
The reflected light flux N ′ that has passed through the mask 53 is reflected by a mirror 54 and is condensed by a relay lens 55 while being reflected by a mirror 57.
And a corneal endothelial cell image is formed on the CCD camera 6. As shown in FIG. 5, a corneal endothelial cell image 58 is displayed on the screen 8 of the monitor device by the video signal from the CCD camera 6.

The objective lens 51 has a Z alignment detection system 6
0. The Z alignment detection system 60 has a linear sensor 61. The linear sensor 61 is provided at a position conjugate with the cornea C with respect to the objective lens 51. The reflected light by the cornea C of the slit light projected by the illumination optical system 40 for Z alignment detection is reflected by the objective lens 51.
The light is reflected by the dichroic mirror 52 and focused on the linear sensor 61 while being focused. The linear sensor 61 has a role of detecting a light intensity distribution. FIG. 6 shows the light amount distribution on the linear sensor 61. In FIG. 6, reference numeral 62 denotes a peak portion of the light beam reflected by the surface T of the cornea C, and reference numeral 63 denotes a peak portion of the light beam reflected by the corneal endothelial cell surface. Linear sensor 6
The detection output of 1 is input to the Z alignment detection circuit 64.

The position information of the bright spot image R1 'on the PSD 21 and the position information of the bright spot image R2' of the CCD camera 6 are input to the XY alignment detection circuit 22. As shown in detail in FIG. 7, the XY alignment detection circuit 22 includes a position detection circuit 22a, a position detection circuit 22b, an error calculation circuit 22c, an internal memory 22d, a correction circuit 22e, and a switch 22f.

The light quantity distribution on the imaging surface of the CCD camera 6 is as shown in FIG. 2B along the line AA 'shown in FIG. In FIG. 2B, reference symbol R2 ″
Is the light amount distribution corresponding to the bright spot image R2 ', and the symbol R3 is the pupil E
1, the light amount distribution of the reflected light reflected from the inside of the fundus,
R4 is the light amount distribution of the light reflected by the iris E2, R
Reference numeral 5 denotes a light amount distribution of the reflected light reflected by the sclera E3. In FIG. 2B, the amount of light reflected from the fundus through the pupil E1 is the smallest, the amount of light reflected next by the iris E2 is small, and the amount of light reflected by the sclera E3 is small. Is the largest.

In the position detecting circuit 22b, by providing a threshold value L 'shown in FIG. 2B, boundary addresses A1 and A2 between the reflected light amount distribution R5 by the sclera E3 and the reflected light amount distribution R4 by the iris E2 are extracted. The light amount information of the address smaller than the address A1 and the light amount information of the address larger than the address A2 are discarded. next,
The position detection circuit 22b extracts the light amount from the address A1 to the address A2 for each address, extracts the address having the light amount exceeding the threshold value L ', and extracts the address x1 having the maximum light amount among the addresses.
The extracted address x1 is the position information of the bright spot image R2 '. The position information based on the address x1 obtained in this manner has a detection error removed.

A bright spot image R1 'corresponding to the bright spot image R is formed on the image receiving surface of the PSD 21 as shown in FIG. The light intensity distribution on the image receiving surface is, for example, as shown in FIG.
In (b), the symbol R1 ″ schematically shows a light amount distribution corresponding to the bright spot image R1 ′, and the symbol N1 schematically shows a light amount distribution based on the background light reflected by the anterior eye and the like. The distribution becomes a detection error. The PSD 21 outputs the position information x2 as the position of the center of gravity obtained by averaging the total amount of light.
Therefore, the position information x based on only the bright spot image R1 'is not obtained, and the position information x2 includes a detection error Δ based on the presence of the background light. The position information x and the position information x1
Corresponds to one-to-one.

The position information x2 of the position detection circuit 22a is supplied to an error calculation circuit 22c and a correction circuit 22 via a switch 22f.
e. The switch 22f is normally connected to the side of the error calculation circuit 22c, and the control circuit 65 switches the switch 2 when the bright spot image R2 'enters the mark 24a.
2f is switched from the error calculation circuit 22c to the correction circuit 22e. The position information x1 output from the position detection circuit 22b is input to the error calculation circuit 22c. The error calculation circuit 22c calculates a difference between the position information x1 and the position information x2. This difference is the detection error Δ. Then, a correction equation is constructed based on the detection error Δ. This correction formula is stored in the internal memory 22d.

The correction circuit 22e corrects the position information based on the detection output of the position detection circuit 22a by using the correction formula stored in the internal memory 22d. This corrected position information x
Are input to the control circuit 65. When the alignment detection is repeated, the correction formula is substantially the same for the same subject and the same subject's eye. Therefore, the correction formula stored in the internal memory 22d can be repeatedly used for the calculation in the correction circuit 22e. When the subject changes or when the left and right of the subject's eye are changed, the internal memory 22d is reset and reset.
Further, this correction formula may be constructed by the error calculation circuit 22c every time measurement is performed. If the position information based on the arithmetic circuit 22a is corrected based on the correction formula stored in the internal memory 22d in this manner, the position detection circuit can maintain the same accurate position information as the CCD camera 6 having a low detection speed. 22a
Thus, position information can be detected at a higher speed.

While observing the anterior segment image E 'on the monitor screen 8, the examiner moves the apparatus body in the XYZ directions so that the bright spot image R2' enters the mark 24a indicating the auto alignment allowable range and is in focus. To adjust the alignment manually.

When the power supply is turned on, the control circuit 65 turns on the light sources 2, 11, 18, and 51. When the bright spot image R2 'enters the mark 24a, the control circuit 65 automatically drives the apparatus main body by a driving unit (not shown) so that the apparatus main body is aligned with the eye E to be inspected.

The detection output of the Z alignment detection circuit 64 and the detection output of the XY alignment detection circuit 22 are input to the control circuit 65, and the XY alignment detection circuit 22 allows the positional relationship between the top, bottom, left, and right of the apparatus body with respect to the subject's eye to be within an allowable range ( When it is at the mark 24b in FIG.
An alignment completion signal is output to the control circuit 65. The Z alignment detection circuit 64 outputs a Z alignment completion signal to the control circuit 65 when the distance of the apparatus body to the eye to be examined in the optical axis direction is within an allowable range. Note that the Z alignment detection circuit 64 outputs a Z alignment completion signal when the address z of the peak portion 63 exists within a range of δ on both sides of the reference address Q of the linear sensor 61 as a center. That is, when the detection result of the XY alignment detection system 20 is within the mark 24b and the detection result of the Z alignment detection system 60 is within the allowable range,
The light sources 2, 11, 18, and 51 are turned off, and the light source 31 automatically emits light. As a result, the cornea C is illuminated with the slit light, and an image of the corneal endothelial cells is taken.

Based on the information output from the XY alignment detection circuit 22 and the information output from the Z alignment detection circuit 65, an alignment state between the apparatus body and the eye E is detected, and the detection result is output to a CRT or the like. It can also be configured to display. Although the embodiment has been described above, a pair of orthogonal one-dimensional PSDs may be used instead of the two-dimensional PSD. In this case, the optical path may be divided by a half mirror to guide the index light to the pair of one-dimensional PSDs. Further, a corneal thickness measuring function for calculating the corneal thickness by a known means from the interval between the reflection images from the corneal surface and the corneal endothelial cell surface on the linear sensor 61 of the Z alignment detection system 60 may be added.

[0033]

According to the first aspect of the present invention, as described above, the range in which alignment can be detected can be set wide without reducing the alignment detection error, and the alignment detection time can be shortened. As a result, the burden on the examiner and the examinee can be greatly reduced.

[Brief description of the drawings]

FIG. 1 shows an optical system of an ophthalmologic apparatus according to the present invention,
(A) shows a side view of the optical system, and (b) shows a plan view of the optical system.

FIG. 2A is an explanatory diagram of an anterior eye image displayed on a screen of a monitor device, and FIG. 2B is a view on a line AA ′ (X direction) including a bright point R1 ′ in FIG. FIG. 4 is a diagram showing light intensity at the point.

FIG. 3 is an enlarged view showing a projection state of the index light onto the cornea shown in FIG.

FIG. 4 is an explanatory view showing an irradiation state of slit light to the cornea shown in FIG. 1;

FIG. 5 is an explanatory diagram of a corneal endothelial cell image displayed on a screen of a monitor device.

6 is a diagram showing a light amount distribution state of a slit light beam on the linear sensor shown in FIG.

FIG. 7 is a diagram illustrating details of the XY alignment circuit of FIG. 1;

FIG. 8 shows a bright spot image R1 received on the PSD shown in FIG.
(A) is a diagram showing an image of a bright spot image R1 ', and (b) is a light on a BB' (X direction) straight line including the bright spot of FIG. It is a figure showing intensity.

FIGS. 9A, 9B, and 9C are explanatory diagrams for explaining states of an index light beam diameter K and an alignment detection range, respectively.

[Explanation of symbols]

 6 CCD camera (second light receiving means) 20 XY alignment detection system 21 Two-dimensional PSD (first light receiving means) 22 XY alignment detection circuit 22a Position detection circuit (position detection means) 22b Position detection circuit (Position detecting means) 22c: error calculating circuit 22d: internal memory 22e: correcting circuit (correcting means) 50: photographing optical system 60: Z alignment detecting system 64: Z alignment detecting circuit 65: control circuit E: eye to be inspected C: cornea

Claims (5)

[Claims] 1. An index light projecting means for projecting an alignment index light onto an eye to be inspected, and a reflection image of the index light from a cornea of the eye to be inspected, and a vertical and horizontal direction between the eye and the apparatus body An opthalmologic apparatus comprising: XY alignment detecting means for detecting a relative positional relationship between the XY alignment detecting means;
An ophthalmologic apparatus comprising: a second light receiving unit; and a correcting unit that corrects information from the first light receiving unit based on information of the second light receiving unit. 2. The first light receiving means includes a light receiving element for obtaining a position of the eye to be examined by obtaining a position of a center of gravity of incident light including a corneal reflection light of the index light, and the second light receiving means. And a second light-receiving element that detects a position of the eye to be examined by detecting a light intensity distribution and extracting a corneal reflection image of the index light based on a set predetermined threshold value. An ophthalmologic apparatus according to item 1. 3. The ophthalmologic apparatus according to claim 1, wherein the first light receiving means uses a two-dimensional PSD as a light receiving element, and the second light receiving means uses a two-dimensional CCD as a light receiving element. 4. A Z-alignment detecting means for detecting a relative position of the subject's eye and the apparatus main body in the front-rear direction,
The ophthalmologic apparatus according to any one of claims 1 to 3, further comprising a driving unit that automatically drives the apparatus main body based on detection information of the Z alignment detecting unit and the XY alignment detecting unit. 5. The anterior segment observation optical system for observing the anterior segment of the eye to be inspected, wherein the two-dimensional CCD is also used.
Or the ophthalmologic apparatus according to claim 4.