JP2003010130A - Fundus examination device - Google Patents

Abstract

(57) [Summary] [Problem] To accurately display an examination part in the center even if the display position and magnification are changed. When it is determined in step S0 that there is a request to increase the display magnification, image data of a fundus image is read from a frame memory in step S6, and processing for reducing the resolving power is performed. In step S5, this data is converted into an analog video signal, and the tracking index image T and the observation fundus image Ea ′ irradiated with the measurement light M are displayed on the display unit. If there is a request to increase the display magnification in step S0, the G component of the image data is read from the frame memory in step S1, the index image T is extracted in step S2, and the center coordinates are obtained.
In step S4, centering on the center coordinates of the index image T,
By extracting pixel data to be displayed and outputting this pixel data in step S5, the center point of the index image T is at the center of the display unit, and a further enlarged image is displayed.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a fundus inspection apparatus for inspecting a fundus at an ophthalmological clinic or the like.

[0002]

2. Description of the Related Art A fundus blood flow meter irradiates a blood vessel to be measured on the fundus of a subject eye with a laser beam having a wavelength λ, and the scattered reflected light is received by a photodetector, which is Doppler scattered light reflected from the bloodstream. This is an apparatus that detects a blood flow velocity by detecting as an interference signal of the scattered component and the scattered reflection light from the stationary blood vessel wall and performing frequency analysis. Then, the blood flow velocity (maximum velocity Vmax) is obtained by the principle described below.

Vmax = {λ / (n · α)} · || Δfmax1 | − | Δfmax2 || / cosβ (1) Here, the maximum shift of the frequency calculated from the light reception signals received by the two light receivers. Δfmax1, Δfmax2,
The wavelength of the laser beam is λ, the refractive index of the measurement site is n, the angle formed by the two light receiving optical axes in the eye is α, and the plane formed by the two light receiving optical axes in the eye and the velocity vector of the blood flow. Angle β
I am trying.

As described above, by performing measurement from two directions, the contributions of the measurement light in the incident direction are canceled out, and the blood flow at an arbitrary site on the fundus can be measured. In addition, β = 0 ° can be obtained by matching the angle β formed by the line of intersection between the plane formed by the two light-receiving optical axes and the fundus with the blood flow velocity vector, and the true maximum blood flow velocity can be measured. You can do it.

Conventionally, a fundus image is taken by a television camera,
An apparatus for aligning the apparatus, selecting a measurement site and measuring while observing a television monitor is disclosed in Japanese Patent Laid-Open No. 7-13614.
No. 1 and Japanese Patent Laid-Open No. 7-155299, the display magnification is constant. Japanese Patent Laid-Open No. 8-126611 proposes an ophthalmologic apparatus having a variable display magnification, but the center position when the magnification is changed is fixed.

[0006]

However, the above-mentioned conventional example has the following problems.

(1) The measurement position on the fundus of the eye to be examined is extracted,
When performing alignment so that the optical axis of the eye to be inspected and the optical axis of the objective lens coincide with each other, it is convenient to look at a low display magnification, that is, a wide range of the fundus to find a candidate for the measurement position on the fundus. good. Further, when performing the alignment, it is possible to confirm the mixing of ambient light and to perform accurate alignment when the wide range of the fundus is visible.

(2) When confirming whether or not the measuring light is accurately irradiated on the blood vessel to be measured, the higher the display magnification is, the more detailed information can be obtained, so that the accurate setting is possible. .

However, since the display magnification is constant in the former method, both cannot be satisfied at the same time. Further, it is possible to prepare two display means, but there is a drawback that not only space is required, but also the price becomes high.

In the latter method, the center position is fixed when the magnification is changed. Therefore, when the magnification is increased, if the actual measurement position to be confirmed is not near the center, the measurement position can be displayed. There is a drawback that it protrudes.

Further, it is possible to optically change the magnification, but since the center position at the time of changing the magnification is changed at the same time, a complicated structure is required and the apparatus becomes expensive and large. .

The object of the present invention is to solve the above-mentioned problems,
An object of the present invention is to provide a fundus examination device that can accurately display the examination site in the center even if the display position and the magnification are changed.

[0013]

A fundus examination apparatus according to the present invention for achieving the above object comprises an illumination optical system for illuminating the fundus of an eye to be examined with illumination light, and a beam for irradiating the fundus with an irradiation beam. An irradiation optical system, and beam deflection means for deflecting the irradiation beam provided in the beam irradiation optical system,
Imaging means for imaging the illuminated fundus image and irradiation beam image and outputting a video signal, display means for displaying the fundus image and irradiation beam image based on the video signal from the imaging means, and the irradiation beam for irradiation Irradiation beam position detecting means for detecting the fundus position, and based on a detection result of the irradiation beam position detecting means, at least one of a display position and a magnification of the fundus image and the irradiation beam image displayed on the display means is changed. And a display information changing unit for performing the above.

[0014]

BEST MODE FOR CARRYING OUT THE INVENTION The present invention will be described in detail based on the illustrated embodiments. FIG. 1 is a configuration diagram of an embodiment in which the present invention is applied to a fundus blood flow meter. On the optical path facing the eye E to be inspected, an objective lens 1, a bandpass mirror 2 that transmits light in a yellow wavelength range and almost reflects other light flux, and a perforated mirror 3 are provided.
The focusing lens 4, the imaging lens 5, and the two-dimensional CCD camera 6 which are movable along the optical path are sequentially arranged behind the perforated mirror 3 to form a fundus observation optical system.

On the optical path in the reflection direction of the perforated mirror 3,
A relay lens 7, a transparent liquid crystal plate 8 which is a fixation target display element that is movable along the optical path, and an observation light source 9 including a tungsten lamp that emits white light and the like are optically conjugate with the fundus of the eye E to be examined. Place it in a proper position.

On the optical path in the reflection direction of the bandpass mirror 2, an image rotator 10 and a galvanometric mirror 11 having a rotation axis perpendicular to the paper surface and having both sides polished are arranged. Behind the galvanometric mirror 11, a galvanometric mirror 11 is arranged. The lens 12 and the concave mirror 13 are arranged. In the reflection direction of the upper reflection surface 11b of the galvanometric mirror 11, the lens 1
4. A focus unit 15 which is movable along the optical path is arranged. It should be noted that the galvanometric mirror 11 has a notch below the above-mentioned rotation axis, and the lens 14
The front focal plane of is in a conjugate relationship with the pupil of the eye E, and the galvanometric mirror 11 is arranged on this focal plane.

In the focus unit 15, a dichroic mirror 16 is arranged on the same optical path as the lens 14, and a mask plate 17 having a rectangular diaphragm and a mirror 18 are arranged on the optical path in the reflection direction of the dichroic mirror 16. A lens 19 is arranged on the optical path in the transmission direction of the dichroic mirror 16 so that the focus unit 15 can move integrally.

Further, on the optical path in the incident direction of the lens 19, a measuring light source 20 such as a collimated coherent laser diode emitting red light is arranged. Further, on the optical path in the incident direction of the mirror 18, a tracking light source 21 such as helium neon laser light that emits green light, which is different from other light sources with high brightness, is arranged.

On the optical path in the reflecting direction of the lower reflecting surface 11a of the galvanometric mirror 11, a relay lens 22 movable along the optical path, a dichroic mirror 23 for reflecting infrared light, a magnifying lens 24, an image intensity. The fire 25 and the one-dimensional CCD 26 are sequentially arranged,
It constitutes a blood vessel detection system. Also, dichroic mirror 2
Photomultipliers 27 and 28 are arranged in the reflection direction of 3 to form a light receiving optical system for measurement. For convenience of illustration, all the optical paths are shown on the same plane, but the reflection direction of the dichroic mirror 23 is orthogonal to the paper surface.

Further, a system control unit 31 is provided for controlling the entire apparatus, and the system control unit 31 has an A /
RGB signals of CCD camera 6, input means 33 operated by an examiner, D / A converter 3 via D converter 32.
Display unit 3 for displaying the measurement result and the fundus image of the eye to be examined via 4
5, the output signals of the photomultipliers 27 and 28, the image intensifier 25, and the output signal of the one-dimensional CCD 26 are respectively connected, and the output of the system control unit 31 is supplied to the galvanometric mirror control circuit 36 for controlling the galvanometric mirror 11. Connecting.

The transmission type liquid crystal plate 8, the image forming lens 4, the focus unit 15 and the relay lens 22 described above are
By operating a focusing knob (not shown),
The fundus Ea of the eye to be inspected E and the transmissive liquid crystal plate 8, the mask plate 17, and the light receiving surface of the image intensifier 25 are moved in the optical axis direction in conjunction with each other so that they are always optically conjugated. ing.

During observation of the fundus, the white light emitted from the observation light source 9 illuminates the transmissive liquid crystal plate 8 from behind, passes through the relay lens 7 and is reflected by the perforated mirror 3 so that only the yellow wavelength light is emitted. After passing through the band-pass mirror 2, passing through the objective lens 1, and once formed as a fundus illumination light beam image I on the pupil Ep of the eye E, the fundus Ea is illuminated substantially uniformly.
At this time, a fixation target F (not shown) is displayed on the transmissive liquid crystal plate 8 and projected onto the fundus Ea of the eye E by the illumination light to be presented to the eye E as a target image F ′.

The reflected light from the fundus Ea returns through the same optical path,
It is extracted as a fundus observing light beam O from the pupil Ep, passes through the central aperture of the perforated mirror 3, the imaging lens 4, and is input to the two-dimensional CCD camera 6 via the eyepiece lens 5 and via the system control unit 31. Is displayed on the display unit 35 as shown in FIG.
Since the fundus image Ea ′ can be observed by the examiner as shown in (3), the device is aligned while observing the fundus image Ea ′.

At the time of measurement, the collimated measurement light emitted from the measurement light source 20 passes through the lens 19 and the dichroic mirror 16. On the other hand, the tracking light source 2
The tracking light emitted from the laser beam No. 1 is reflected by the mirror 18, then shaped into a desired shape by the mask plate 17, and then reflected by the dichroic mirror 16 to be superimposed on the measurement light. At this time, the measuring light is transmitted through the lens 19 to the mask plate 1
An image is formed in a spot shape at a position conjugate with the center of the opening of No. 7. Further, the measurement light and the tracking light pass through the lens 14, and the upper reflection surface 11b of the galvanometric mirror 11
After being passed through the lens 12 once, it is reflected by the concave mirror 13 and again passes through the lens 12 and is returned to the galvanometric mirror 11.

Here, the galvanometric mirror 11 is arranged at a conjugate position of the pupil of the eye to be inspected, the concave mirror 13 and the lens 12 are concentrically arranged on the optical axis, and they cooperate with each other to form the galvanometric mirror 11. A function of a relay system for forming an image at 1 × is provided. Therefore, the light flux reflected by the upper reflecting surface 11b of the galvanometric mirror 11 is returned to the cutout portion of the galvanometric mirror 11, and goes to the image rotator 10 without being reflected by the galvanometric mirror 11. Both light fluxes, which have passed through the image rotator 10 and are deflected by the bandpass mirror 2 to the objective lens 1, are irradiated onto the fundus Ea of the eye E to be examined via the objective lens 1.

As described above, the measurement light and the tracking light are
The galvanometric mirror 11 is incident on the galvanometric mirror 11 in a state of being decentered from the optical axis of the objective lens 1 so as to be reflected in the upper reflecting surface 11b of the galvanometric mirror 11 and returned again, and on the pupil Ep as shown in FIG. Spot image P2
Alternatively, after the image is formed as P2 ′, the fundus Ea is irradiated in a dot shape.

The scattered and reflected light of the measuring light and the tracking light from the fundus Ea is condensed again by the objective lens 1, most of the light flux is reflected by the bandpass mirror 2, passes through the image rotator 10, and under the galvanometric mirror 11. The measurement light and the tracking light are reflected by the side reflection surface 11a, pass through the relay lens 22, and are separated by the dichroic mirror 23.

The tracking light is a dichroic mirror 2.
3, and a magnifying lens 24 forms an image of a blood vessel image Ev ′, which is larger than the fundus image Ea ′ by the fundus observation optical system, on the photocathode of the image intensifier 25, is amplified, and then is imaged by the one-dimensional CCD 26. To be done. Then, based on the blood vessel image Ev ′ captured by the one-dimensional CCD 26,
Data representing the movement amount of the blood vessel image Ev ′ is created in the system control unit 31, and the blood vessel image Ev ′ and the movement amount are output to the galvanometric mirror control circuit 36. And
The galvanometric mirror control circuit 36 drives the galvanometric mirror 11 so as to compensate for this movement amount, so that the blood vessel of the measured portion can be tracked.

The infrared measuring light is reflected by the dichroic mirror 23, and the photomultiplier 2
The light is received at 7 and 28. Photomultipliers 27, 2
The outputs of 8 are output to the system control unit 31, and the received light signals are frequency-analyzed in the same manner as in the conventional example to obtain the fundus Ea.
Blood flow velocity is calculated.

On the other hand, the scattered light of the measurement light from the fundus Ea and the tracking irradiation light is condensed again by the objective lens 1,
A part of the light flux transmitted through the bandpass mirror 2 follows the same optical path as the reflected and scattered light of the light flux emitted from the observation light source 9 from the fundus Ea of the eye E and reaches the two-dimensional CCD camera 6.

The output of the two-dimensional CCD camera 6 is converted into digital image data as an RGB signal by the A / D converter 32 and input to the system control section 31 where it is subjected to signal processing and is not shown in the system control section 31. Stored in frame memory. Further, in the system control unit 31, this signal is converted into an analog video signal by the D / A converter 34, and the tracking index image T and the measurement light M are displayed on the display unit 35 together with the observation fundus image Ea ′, and the examiner Make it observable.

The examiner operates an operation rod (not shown) to perform alignment so that the optical axis of the eye E to be examined and the optical axis of the objective lens 1 coincide with each other. Next, while observing the fundus oculi image Ea ′ on the display unit 35, the focus knob is operated to operate the eye E to be inspected.
Focus on the fundus Ea of. Then, as described above, the fixation target F of the transmissive liquid crystal plate 8 and the fundus Ea are optically conjugated and presented to the eye E to be examined.

After that, the examiner selects the blood vessel to be measured. In this case, since the blood vessel to be measured and the measurement site are selected from a plurality of blood vessels, it is desirable that the fundus Ea can be observed as wide as possible. Further, in that case, the influence of ambient light can be confirmed, and the alignment can be performed accurately. For these reasons, the examiner inputs a request for enlarging the magnification of the fundus image Ea ′ displayed on the display unit 35 using the input unit 33 as necessary.

FIG. 4 is a flow chart of the processing performed by the system control unit 31. When it is determined in step S0 that the request for enlarging the display magnification is not input from the input means 33, the image data is read from the frame memory in step S6. , To reduce the resolution. In the present embodiment, the number of pixels that can be captured by the two-dimensional CCD camera 6 exceeds the resolving power that can be displayed on the display unit 35.
The process in 6 is performed to display the fundus image captured by the two-dimensional CCD camera 6 on the display unit 35 over the entire range.

Further, in step S5, this data is D / A
The observation fundus image Ea ′, which is output to the converter 34, converted into an analog video signal, and irradiated with the tracking index image T and the measurement light M, is displayed on the display unit 35. The examiner can observe the fundus image Ea ′ as shown in FIG. At this time, the center position of the display unit 35 substantially coincides with the optical axis of the objective lens 1.

Then, when the examiner selects the site to be measured,
The input means 33 is operated to move the fixation target F so that the site to be measured is near the center of the observation visual field, and the eye E to be examined is guided. Next, the input means 33 is operated to irradiate the fundus Ea with tracking light, and further the rotator operation knob is operated so that the tracking index image T becomes perpendicular to the blood vessel Ev to be measured, and further to the blood vessel Ev to be measured. The angle of the galvanometric mirror 11 is controlled so that the measurement light M is emitted.

At this time, it is necessary to confirm whether or not the tracking index image T is perpendicular to the blood vessel Ev to be measured, and whether the measurement light is accurately applied to the blood vessel Ev to be measured. When the fundus image Ea ′ displayed by is observed at a high magnification, tracking light and measurement light can be confirmed and alignment can be performed more strictly.

Then, the examiner operates the input means 33,
The fundus image Ea ′ displayed on the display unit 35 is magnified, but the center of the fundus image Ea ′ captured by the two-dimensional CCD camera 6,
That is, if the display magnification is increased around the center point of the coordinates of all pixels, the tracking index T and the portion irradiated with the measurement light may not be displayed outside the display unit 35 as shown in FIG. is there.

Therefore, in the present embodiment, the system control unit 31 extracts the tracking index image T from the fundus image captured by the two-dimensional CCD camera 6, calculates the center position of the tracking index image T, and centers that point. Control is performed such that the fundus image Ea ′ is enlarged and displayed on the display unit 35.

The RGB image data converted into digital data by the A / D converter 32 is used by the system control unit 3
1 and is stored in a frame memory (not shown).

If it is determined in step S0 that there is a request for magnification enlargement in the input means 33, the G component image data is read from the frame memory in step S1. In the present embodiment, the tracking light source 21 has a green color (wavelength:
(543 nm) helium neon laser light is used. Since the fundus image has many R components, the system control unit 31 uses the G signal of the RGB signals obtained by the two-dimensional CCD camera 6 to extract the tracking index image T and calculate the center position. .

In step S2, the tracking index image T is extracted from the image data of the fundus image Ea '. FIG. 6 shows pixels x [n] to x [n + 15], y [n] to pixels in the thick frame shown in FIG.
The 16 * 16 pixels of y [n + 15] are obtained by binarizing the gradation level of the G component image data. Figure 6
The tracking index image T is formed on a pixel having a value of 1 in each pixel. The values of pixels other than the tracking index image T are 0.

In step S3, the position of the tracking index image T on the fundus image Ea 'is calculated. x in the x direction
The pixels of [n + 6] to x [n + 10] have y in the y direction.
Since the tracking index image T exists in each of the pixels [4] to y [10], when the respective midpoints are calculated, {(n + 10)-(n + 6)} / 2+ (n + 6) = in the x direction.
n (8), {(n + 10)-(n + 4)} / 2 in the y direction
+ (N + 4) = n + 7, and (x [n + 8], y [n
+7]) becomes the center coordinates of the tracking index image T.

In step S4, the pixel data to be displayed is extracted with the center coordinates of the tracking index image T calculated in step S2 as the center, and this pixel data is output to the D / A converter 34 in step S5. By doing so, as shown in FIG. 8, the center point of the tracking index image T is the center of the display unit 35, and a further enlarged image is displayed on the display unit 35.

In the present embodiment, the fundus image Ea ′ displayed on the display unit 35 is fixed at a magnifying power of 3 when a screen magnifying request is input to the input means 33. May be variable, and may be set by the examiner from the input means 33.

In the present embodiment, the examiner operates the input means 33 after irradiating the fundus Ea with the tracking light.
Although the fundus image Ea ′ displayed on the display unit 35 is magnified, it is possible to magnify the fundus image Ea ′ displayed on the display unit 35 even before the tracking light is applied to the fundus Ea ′. At this time, since the position of the tracking index image T calculated on the fundus Ea calculated in step S3 cannot be calculated, the image of the fundus image Ea ′ displayed on the display unit 35 is centered on the center point of the coordinates of all pixels in step S4. Extract the data. It is also possible to determine the position of the measurement point based on the position information of the image rotator 10 and the galvanometric mirror 11, and to enlarge the fundus image centering on the measurement point.

FIG. 9 is an explanatory diagram of the relationship between the measurement site and the optical axis of the objective lens 1. The galvanometric mirror 11: the magnification of the pupil Ep of the eye to be inspected is n: n ′, the deflection angle of the galvanometric mirror 11 is δ, Let δ ′ be the incident angle of the tracking light and the measurement light with respect to the optical axis of the objective lens 1 to the pupil Ep of the eye E to be inspected.
Then, the following equation is obtained.

Tan δ ′ / tan 2 δ = n / n ′ (1) The coordinates of the measurement point are (xb, yb), and the coordinates of the measurement point from the coordinates (0, 0) on the fundus Ea of the optical axis of the objective lens 1. (X
b, yb) is r, and the representative value fe of the model eye is taken as the focal length of the eye E to be examined, the following equations (2) to (4) are obtained from the equation (1).

R = fe · tan δ ′ = (n / n ′) · fe · tan 2δ (2) xb = r · cos γ = (n / n ′) · fe · tan δ · cos γ (3) yb = r · sinγ = (n / n ′) · fe · tanδ · sinγ (4) Here, γ is the measurement point (xb, yb) on the fundus Ea and x
It is the angle formed by the axis and the rotation angle of the image rotator 10. The counterclockwise direction is the positive direction.

From equations (3) and (4), it can be seen that the position of the measurement point of the eye E to be examined with respect to the optical axis of the objective lens 1 can be determined by the position information of the image rotator 10 and the galvanometric mirror 11.

The system control unit 31 calculates the position of the measurement point by the method described above. In the flowchart of FIG. 4,
This process may be performed instead of steps S2 and S3.

As a result, the measurement point is centered,
The tracking index image T and the fundus image Ea ′ irradiated with the measurement light M are enlarged and displayed on the display unit 35 as shown in FIG.

In the first embodiment, the examiner changes the magnification of the fundus oculi image Ea 'displayed on the display unit 35 by inputting the input means 33. However, tracking light is emitted to the fundus Ea. The display magnification of the display unit 35 can be automatically changed by detecting whether or not it is displayed.

FIG. 10 shows a flow chart of the second embodiment. The processing in steps S1 and S2 is the first
Similar to the case of the above embodiment, it is determined in step S7 whether or not the tracking light is irradiating the fundus Ea.
This determination extracts the tracking index image T in step S2. If the tracking index image T is not detected at this time, it is determined that the tracking light does not illuminate the fundus Ea. Alternatively, it may be determined whether or not the input unit 33 has received an input for irradiating the fundus Ea with tracking light.

In step S7, the tracking light is emitted to the fundus Ea.
If it is determined that the light has not been radiated to step S6, step S6
In step S5, the image data is read from the frame memory and a process for reducing the resolution is performed.
The A converter 34 converts it into an analog video signal, and the tracking index image T and the measurement light M are displayed on the display unit 35 together with the observation fundus image Ea ′. The examiner can observe the fundus image Ea ′ as shown in FIG.

When it is determined in step S7 that the tracking light is applied to the fundus oculi image Ea ', the processes of steps S3 to S5 are performed as in the first embodiment.

In the present embodiment, whether or not tracking light is radiated to the fundus Ea is detected and the display magnification of the display unit 35 is automatically increased, but the examiner operates the input means 33. Then, until the tracking index image T, the measurement light M, and the measured blood vessel Ev can be precisely aligned after the tracking light is applied to the fundus Ea.
It may take several seconds to several tens of seconds.

That is, the tracking index image T is almost perpendicular to the measured blood vessel Ev and near the measured blood vessel Ev.
It may be necessary for the examiner to operate the rotator operation knob (not shown) to control the angle of the galvanometric mirror 11 before the irradiation of. Therefore, the display magnification of the display unit 35 may be automatically increased after a certain period of time from the irradiation of the tracking light on the fundus Ea.

Further, when both the tracking light and the measurement light are irradiated, the display magnification of the display unit 35 is automatically increased for the first time, and when the tracking light irradiation is completed,
The display magnification may be automatically reduced.

In the above embodiment, the fundus blood flow meter for measuring the blood flow on the fundus Ea has been described. However, it is applicable to an ophthalmologic apparatus which simultaneously measures the blood vessel position and the blood vessel diameter in addition to the blood flow velocity. It is also possible to apply.

[0061]

As described above, in the fundus examination apparatus according to the present invention, the display magnification of the fundus image of the eye to be examined can be changed, and even when the display magnification is further increased, the tracking light and the measurement light are used as the fundus of the eye to be examined. Since the position of irradiating the laser beam is detected and the position is controlled so as to be always substantially in the center of the display means, there is no possibility that the tracking light and the measurement light are outside the display range of the display means and cannot be confirmed.

Therefore, since it is possible to always observe how the tracking light and the measurement light are applied to the blood vessel to be measured on the screen in which the fundus image is enlarged, it is possible to check the irradiation position of the tracking light and the measurement light more strictly. Can be aligned,
As a result, the accuracy of the measured value can be further improved.

Further, since it is detected whether or not the tracking light and the measurement light are illuminating the fundus of the eye to be inspected and the display magnification and the display position of the fundus image of the eye to be inspected are changed based on the detection result, a troublesome manual setting is required. The same effect as the above can be obtained without requiring.

[Brief description of drawings]

FIG. 1 is a configuration diagram of an embodiment.

FIG. 2 is an explanatory diagram of an observation fundus image which is not enlarged and displayed after focus is completed.

FIG. 3 is an explanatory diagram of a luminous flux arrangement on a pupil.

FIG. 4 is a flowchart of the first embodiment.

FIG. 5 is an explanatory diagram of a display example of an enlarged observation fundus image.

FIG. 6 is a distribution diagram of tracking index images extracted from pixels of a G signal in a two-dimensional CCD camera.

FIG. 7 is a pixel configuration diagram according to a G signal in a two-dimensional CCD camera.

FIG. 8 is an explanatory diagram of a display example of an enlarged observation fundus image.

FIG. 9 is an explanatory diagram of a relationship between a measurement site and an optical axis.

FIG. 10 is a flowchart of the second embodiment.

[Explanation of symbols]

1 Objective lens 2 band pass mirror 3 perforated mirror 6 two-dimensional CCD camera 8 Transmissive liquid crystal plate 9 Observation light source 10 image rotator 11 Galvanometric mirror 13 concave mirror 15 Focus unit 16,23 Dichroic mirror 20 Light source for measurement 21 Tracking light source 24 magnifying lens 25 Image Intensifier 26 one-dimensional CCD 27, 28 Photomultiplier 31 System control unit 33 Input means 35 display means

Claims (9)

[Claims] 1. An illumination optical system for illuminating the fundus of an eye to be inspected with illumination light, a beam irradiation optical system for irradiating the fundus with an irradiation beam, and a deflection optical system provided in the beam irradiation optical system for deflecting the irradiation beam. Beam deflecting means, imaging means for imaging the illuminated fundus image and irradiation beam image and outputting a video signal, and display means for displaying the fundus image and irradiation beam image based on the video signal from the imaging means, Based on the detection result of the irradiation beam position detecting means for detecting the fundus position irradiated with the irradiation beam, and the irradiation beam position detecting means,
A fundus examination apparatus comprising: a display information changing unit that changes at least one of a display position and a magnification of the fundus image and the irradiation beam image displayed on the display unit. 2. The irradiation position of the irradiation beam with respect to the fundus detected by the irradiation beam position detecting means when the display information changing means changes the magnification of the fundus image and the irradiation beam image displayed on the display means. The fundus examination apparatus according to claim 1, wherein the display position is changed so as to display in the display range of the display means. 3. The display information changing means sets a low magnification when the irradiation beam position detecting means does not detect irradiation of the fundus of the irradiation beam, and sets a high magnification when detecting irradiation of the fundus. The fundus examination apparatus according to claim 2, wherein: 4. The display information changing unit changes the setting of the magnification after a certain period of time after the irradiation beam position detection unit detects the presence or absence of irradiation of the fundus of the irradiation beam. Fundus examination device. 5. The display information changing unit determines whether to control at least one of a display position and a magnification of the fundus image and the irradiation beam image displayed on the display unit based on the input information of the input unit. The fundus examination apparatus according to claim 1, which is determined. 6. The fundus examination apparatus according to claim 1, wherein the irradiation beam position detection unit detects the fundus position irradiated with the irradiation beam based on a video signal from the imaging unit. 7. The irradiation beam position detecting means detects an exit angle of the beam deflecting means to the subject's eye, and detects the fundus position of the irradiation beam irradiated. Fundus examination device. 8. The beam deflecting means has a rotating mirror provided at a position substantially conjugate with a subject's eye pupil behind the objective optical system,
The fundus examination apparatus according to claim 7, wherein the irradiation beam position detection means detects an angle of the rotatable mirror. 9. The beam rotator according to claim 7, further comprising an image rotator provided behind the objective optical system, and the irradiation beam position detector detects the rotation angle of the image rotator. Fundus examination device.