JPH0884703A - Ophthalmological apparatus - Google Patents

Abstract

PURPOSE: To enable accurate measurement and photographing without missing a timing for positioning. CONSTITUTION: A luminous flux from a light source 9 for positioning is projected onto a cornea of an eye E to be inspected and the reflected luminous flux is cast onto a CCD image sensor 7 passing through a half mirror 3 and a light dividing member 5 or the like to project an anterior ocular segment image E' onto a TV monitor 17. On the other hand, the luminous flux reflected on the light dividing member 5 is received with a photoelectric sensor 13 and a signal processor 16 judges positioning to be accomplished when the current quantity of light exceeds a specified threshold level. Thus, an air pressurizing system 15 is driven automatically to blow air to the cornea.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmologic apparatus used for measuring or photographing various ophthalmic characteristics in an ophthalmic hospital or the like.

[0002]

2. Description of the Related Art Conventionally, in an apparatus for measuring or photographing after aligning an object such as an eye to be inspected or eyeglasses to be inspected, if the alignment is delicate and the timing of pressing a measurement button is difficult, a photoelectric sensor is used. The position is detected automatically, and when they match each other, the measurement or photographing is automatically performed.

[0003]

However, since the measurement takes a predetermined time, if the eye moves during that time, the alignment will be misaligned. For this reason, when the state is maintained for a predetermined time after the position is aligned, the measurement is started assuming that the eye does not move within the time required for the subsequent measurement. The timing may be missed, which causes a problem that measurement or shooting fails.

The object of the present invention is to solve the above-mentioned problems,
It is an object of the present invention to provide an ophthalmologic apparatus capable of automatically performing reliable measurement or photographing without missing the timing of alignment.

[0005]

An ophthalmologic apparatus according to a first aspect of the present invention for achieving the above object, projects a light beam on a subject,
By photoelectrically detecting the reflected light flux from the subject, in an ophthalmologic apparatus that aligns the device body and the subject,
Detecting means for detecting a temporal change of the photoelectric detection signal,
Signal processing control means for measuring or imaging the subject according to the output of the detection means is provided.

The ophthalmologic apparatus according to the second aspect of the present invention is an ophthalmologic apparatus that projects a light beam onto a subject and photoelectrically detects the light beam from the subject, and sequentially detects the relative position between the device and the subject. And a signal processing control means for detecting the relative moving speed and direction of the subject with respect to the apparatus based on a signal from the position detecting system.

[0007]

The ophthalmologic apparatus of the first invention having the above-mentioned configuration projects the light flux onto the subject, photoelectrically detects the reflected light flux from the subject, and aligns the device and the subject based on the temporal change of the signal. After detection, the signal processing control means measures or images the subject.

Further, the ophthalmologic apparatus of the second invention projects the light flux on the subject, photoelectrically detects the reflected light flux from the subject, and sequentially detects the relative position between the device and the subject by the position detection system. , The relative movement speed and direction of the subject with respect to the apparatus are detected, and the signal processing control means automatically measures or photographs the subject.

[0009]

DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described in detail based on the illustrated embodiments. FIG. 1 shows a configuration diagram of a first embodiment applied to an air-blowing tonometer. A nozzle 1, a chamber 2, a half mirror 3, a lens 4, a light splitting member is provided on an optical path O1 in front of an eye E to be examined. 5, the lens 6, and the CCD image pickup device 7 are sequentially arranged. A lens 8 and a corneal deformation detecting and aligning light source 9 are arranged in the incident direction of the half mirror 3, and a lens 10, a half mirror 11, and a measuring photoelectric sensor 12 in the reflecting direction of the light splitting member 5. Are arranged, and the alignment photoelectric sensor 13 is arranged in the reflection direction of the half mirror 11.

A pressure sensor 14 for detecting the internal pressure of the chamber 2 is provided, and the chamber 2 is connected to an air pressurizing system 15 including a piston, a cylinder and the like. The outputs of the pressure sensor 14, the CCD image pickup device 7, the measurement photoelectric sensor 12, and the alignment photoelectric sensor 13 are connected to the signal processor 16, and the output of the signal processor 16 is connected to the television monitor 17 and the air pressurization system 15. Has been done.

A light beam emitted from the light source 9 passes through the lens 8, the half mirror 3, the chamber 2 and the nozzle 1 and is projected on the cornea of the eye E to be inspected to form a virtual image I '. The reflected light from the cornea passes through the periphery of the nozzle 1, the chamber 2, the half mirror 3, the lens 4, the light splitting member 5 and the lens 6 and is projected onto the CCD image pickup device 7, and is projected on the television monitor 17 together with the light source image I ′. The eye image E'is displayed.

The light beam reflected by the light splitting member 5 is
The half mirror 11 passes through the lens 10 and is aligned.
Is reflected by the photoelectric sensor 13 and is received by the photoelectric sensor 13. At the time of measurement, the light is transmitted through the half mirror 11 and received by the photoelectric sensor 12.
That is, when the device reaches a predetermined position with respect to the eye E, the light source image I ′ becomes conjugated with the photoelectric sensor 13, and the signal processor 16 detects this signal and the compressed air from the air pressurizing system 15 causes the nozzle 1 to pass. It is sprayed through the cornea. When the cornea undergoes a predetermined deformation, the virtual image I ′ and the photoelectric sensor 12 become conjugated,
When this signal reaches a peak, the pressure inside the chamber 2 is measured by the pressure sensor 14, and the intraocular pressure value is converted from this value.

FIG. 2 shows the change over time of the light amount signal received by the positioning photoelectric sensor 13, the curve f1 is the characteristic of the light amount L when the slide base is moved quickly, and the curve f2 is the slide base. Is a characteristic of the light amount L when is gradually moved. When the light source image I ′ and the photoelectric sensor 13 are conjugate with each other, the curves f1 and f2 have peak values, and the signal processor 16 determines that the positions match when the light amount L exceeds the threshold LO level.

Therefore, when the curves f1 and f2 rise and the slopes at the intersections P1 and P2 with the straight line indicating the threshold value LO are less than a predetermined value, the eye movement is small and the measurement is started.
Emits a signal to drive the air pressurization system 15 to blow air on the cornea. If the eye is moving, the alignment may be out of alignment, in which case the rate of change or slope of the curves f1, f2 will be large and the measurement will not be initiated.

In the above-mentioned embodiment, the relative position between the eye and the device is determined by the light amount L. However, if the position is directly measured, the moving speed and its direction can be known, so that the eye can be measured during the time required for the measurement. It is possible to more accurately predict whether or not the value is within the allowable position range. For example, if the light source image I ′ is captured and tracked from two directions by a photoelectric sensor having a plurality of elements, the relative position can be detected three-dimensionally. Therefore, the moving speed and the direction are sequentially calculated, and the time point is calculated. When it is predicted from the above that the allowable range is reached within the measurement time, the signal processor 16 issues a start signal to inject air.

FIG. 3 is a block diagram of a second embodiment applied to a lens meter, in which a lens 22, a lens L to be measured for measuring a refraction value, a five-hole diaphragm 23, are arranged on a front optical axis O2 of a light source 21.
A lens 24 and a two-dimensional CCD sensor 25 are sequentially arranged, an output of the two-dimensional CCD sensor 25 is connected to a signal processor 26 including a computer, and an output of the signal processor 26 is connected to a television monitor 27. .

The light flux from the light source 21 passes through the lens 22, the lens L to be tested, the aperture stop 23, and the lens 24, and five spot lights are projected on the two-dimensional CCD sensor 25. The examiner sees the five spot lights S reflected on the television monitor 27 and aligns the position of the lens L to be inspected with the alignment mark M. As a result, the optical axis of the lens L to be tested coincides with the optical axis O2, the spot light reaches the center of the two-dimensional CCD sensor 25, and at that time, the signal is automatically taken into the computer in the signal processor 26, The position of the spot light is calculated and the speed of movement is tracked at the same time as the position.

That is, when moving fast, it is judged that the examiner has no intention of measuring and the measurement is not performed even if the position is within the allowable range. When it is time to measure, it moves slowly in the vicinity, so the measurement is performed when the position gradually moves into the allowable range. The position of the spot light is calculated, the refractive index of the lens L to be tested is obtained, and the result is displayed. A sound is also used for this result display so that the measured value can be clearly understood. In this way, unlike the conventional device, there is no need to press the measurement button for each measurement, and the signal processor 2
Since 6 can determine whether or not to measure and automatically perform the measurement, it is possible to prevent measurement at a position where the user does not intend to measure.

FIG. 4 is a block diagram of the third embodiment applied to the fundus camera, in which the objective lens 30, the switching mirror 31, the perforated mirror 32, the lens 33, and the switching mirror are located on the front optical path O3 of the eye E to be examined. 34 and a recording medium 35 such as a film are sequentially arranged. A lens 36, a photographing light source 37, a lens 38, and a fundus illuminating light source 39 are sequentially arranged in the incident direction of the perforated mirror 32, and a two-dimensional CCD sensor 40 is arranged in the reflecting direction of the switching mirror 31. In the reflection direction of 34, the lens 41 and the TV camera 4
2 are arranged. Further, an LED light source 43 that illuminates the anterior segment is provided around the objective lens 30. The outputs of the two-dimensional CCD sensor 40 and the television camera 42 are connected to the signal processor 44, and the output of the signal processor 44 is connected to the television monitor 45.

At the time of alignment, the LED light source 43 illuminates the anterior segment of the eye E to be inspected, and the reflected light is the objective lens 30,
The image near the pupil Ep is passed through the switching mirror 31 and a two-dimensional CC image is obtained.
An image is captured by the D sensor 40, and a pupil image Ep 'is displayed in the left corner of the television monitor 45.

The light flux from the fundus illuminating light source 39 is a lens 38, a photographing light source 37, a lens 36, and a perforated mirror 3.
2, the switching mirror 31 goes out of the optical path O3, passes through the objective lens 30, and illuminates the fundus Er. The counter light passes through the perforated mirror 32, the lens 33, the switching mirror 34, and the lens 41 and is projected on the television camera 42, and the fundus image Er ′ is displayed in the center of the television monitor 45.

The image of the TV camera 42 and the image of the two-dimensional CCD sensor 40 are combined by the signal processor 44, the fundus image Er 'is projected in the center of the TV monitor 45, and the pupil image Ep' is displayed in the left corner.
Is displayed, and the examiner aligns while looking at the fundus image Er 'and the pupil image Ep'. The signal processor 44 sequentially calculates the focus and center position of the pupil image Ep ', and when the positions match, the image is focused and the pupil image Ep' comes to the center of the left corner screen.

The signal from the signal processor 44 at this time causes the photographing light source 37 to emit light, and at the same time, the switching mirrors 31 and 34 are switched.
Bounces off and the fundus image Er 'is recorded on the recording medium 35 such as a film.
Will be taken. Also in this case, the focus of the pupil image Ep 'and the rate of change of the position signal are detected, and when the rate of change of the eye movement is within the allowable range and the rate of change is equal to or less than the predetermined value, the photographing signal is emitted. Further, it is also possible to calculate the moving speed and the direction similarly to the first embodiment and use them together to detect the alignment.

[0024]

As described above, the ophthalmologic apparatus according to the first aspect of the present invention photoelectrically detects the reflected light flux from the subject and detects the alignment between the apparatus and the subject from the temporal change of the signal, Measurement or imaging can be performed without losing timing after alignment, and operability is improved.

Further, the ophthalmologic apparatus according to the second aspect of the present invention detects the reflected light flux from the subject photoelectrically and sequentially detects the relative position of the apparatus and the subject by the position detection system, so that the apparatus of the subject is detected. By detecting the relative moving speed and direction, it is possible to accurately predict that the eye stays within the allowable position range during measurement, and it is possible to perform fine measurement or photographing without failure.

[Brief description of drawings]

FIG. 1 is a configuration diagram of a first embodiment.

FIG. 2 is a graph of an alignment signal.

FIG. 3 is a configuration diagram of a second embodiment.

FIG. 4 is a configuration diagram of a third embodiment.

[Explanation of symbols]

 1 Nozzle 7 Imaging Device 9, 20, 37, 39, 43 Light Source 12, 13 Photoelectric Sensor 14 Pressure Sensor 15 Air Pressurization System 16, 26, 44 Signal Processor 17, 27, 45 Television Monitor 22 Test Lens 25, 40 Two-dimensional CCD 35 Recording medium 42 Television camera

Claims (2)

[Claims] 1. An ophthalmologic apparatus that aligns the apparatus main body with a subject by projecting a light flux onto the subject and photoelectrically detecting a reflected light flux from the subject to detect temporal changes in the photoelectric detection signal. An ophthalmologic apparatus comprising: a detection unit for detecting and a signal processing control unit for measuring or photographing an object by the output of the detection unit. 2. An ophthalmologic apparatus for projecting a light flux onto a subject and photoelectrically detecting the light flux from the subject, and a position detection system for sequentially detecting a relative position between the device and the subject, and the position detection. An ophthalmologic apparatus comprising: a signal processing control unit that detects a relative movement speed and direction of a subject with respect to the apparatus based on a signal from a system.