JPH0994223A - Apparatus for ophthalmology - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an apparatus for ophthalmology enabling to perform a precise measurement of optometry. SOLUTION: An objective refractor system of an ophthalogical apparatus 1 is capable of objectively measuring a refractivity of a subject at the state where the subject is made to be a fixation to a gazing target of an oculogyric target system. An arithmetic unit 330 obtains an objective value of the subject based on the determined results by the objective refractory system and the gazing system. A regulating unit 300 disposes a gazing target of the oculogyric target system at a position for a far distance position of the subject determined by the arithmetic unit 330 and continuously and objectively measures while fogging the gazing target. By the above motions, a continuously objective measured value on fogging the gazing target of the oculogyric target system can be obtained from far distance based on the objective measurement of the subject, and a limit of controlling capacity of the eyes of the subject can precisely be measured.

Description

Detailed Description of the Invention

[0001]

TECHNICAL FIELD The present invention relates to an ophthalmologic apparatus,
More specifically, the present invention relates to an ophthalmologic apparatus that realizes precise measurement for an eye to be inspected and enables selection of an spectacle lens most suitable for the eye to be inspected.

[0002]

2. Description of the Related Art For example, in a conventional ophthalmologic apparatus which objectively measures various visual functions such as visual acuity and astigmatism of an eye to be inspected, an examiner operates an operation means of the ophthalmic apparatus while looking at an image monitor. The eye is inspected for a specific target, but the eye is focused and aligned to obtain objective measurement values such as the spherical power of the eye.

[0003]

However, in the case of the conventional ophthalmologic apparatus, focusing and positioning of the eye to be inspected is performed simply by making the eye to visually inspect a specific target, and the spherical power of the eye to be inspected and the like. Since the objective measurement values such as spherical power are automatically measured and arithmetically processed to obtain the objective measurement values such as the spherical power, the objective measurement values such as the spherical power include some error, and the precise measurement of the eye to be inspected. There is a problem that the value cannot be obtained.

Therefore, the present invention has been made in view of the above circumstances, and provides an ophthalmologic apparatus which realizes precise measurement of objective measurement of the eye to be inspected and enables selection of a spectacle lens most suitable for the eye to be inspected. It is a thing.

[0005]

An ophthalmologic apparatus according to the present invention comprises an objective refraction measuring system for objectively measuring the refractive power of an eye to be inspected, and a gaze target for fixing the eye to be inspected. A gaze target system having, the objective refraction measurement system, a calculation means for obtaining an objective measurement value of the eye to be examined based on the measurement result by the gaze target system,
After setting the gazing target of the gazing target system at the distance position of the subject's eye obtained by this computing means, it has a control means for continuously performing objective measurement while fogging the gazing target. Is.

An ophthalmologic apparatus according to a second aspect of the present invention comprises an objective refraction measuring system that objectively measures the refractive power of the eye to be inspected, and a gaze target system having a gaze target to fixate the eye. The objective refraction measurement system, a calculation means for obtaining an objective measurement value consisting of a spherical power, an astigmatic power, and an axial angle of the eye to be inspected based on the measurement result by the gaze target system, and distance use of the eye to be inspected obtained by this operation means After setting the gaze target of the gaze target system at the position, control means for continuously performing objective measurement while fogging the gaze target so that the fog amount changes at a predetermined step value, and this continuous other It has an output means for visibly outputting each measurement result of the target refraction measurement system and the cloud amount of the gazing target accompanying the haptic measurement,
It is characterized in that it is possible to estimate the subjective comfort level of the spectacle lens to be prescribed based on the spherical power value that the value in each measurement result of the objective refraction measurement system output by this output means is invariant. is there.

The operation of the ophthalmologic apparatus according to the present invention will be described below.

The objective refraction measuring system in the ophthalmologic apparatus according to the first aspect objectively measures the refractive power of the eye to be inspected while the eye of the eye gaze target system is fixed on the eye to be inspected.

The calculating means obtains the objective measurement value of the eye to be examined based on the measurement results by the objective refraction measurement system and the gaze target system.

The control means sets the gazing target of the gazing target system at the distance position of the eye to be examined, which is obtained by the computing means, and then continuously performs objective measurement while making the gazing target cloud.

With such an operation, it is possible to obtain a continuous objective measurement value in which the gaze target of the gaze target system is fogged from the distance position based on the objective measurement of the eye to be inspected, and the accommodation power of the eye to be inspected. The limit of can be measured precisely.

In the ophthalmologic apparatus according to a second aspect, in addition to the operation of the ophthalmologic apparatus according to the above-mentioned first aspect, the output means causes the cloud amount and the objective refraction of the gazing target associated with continuous objective measurement. Since each measurement result of the measurement system is visibly output, the subjective perception of the spectacle lens to be prescribed based on the sphere value that makes the value in each measurement result of the objective refraction measurement system output by this output means invariant It is possible to estimate the comfort level, realize the precise measurement of objective measurement of the eye to be inspected, and further select the optimal spectacle lens for the eye to be inspected based on the subjective comfort level.

[0013]

Embodiments of the present invention will be described below in detail.

The ophthalmologic apparatus 1 of the present invention shown in FIGS. 1 and 2 is provided with a box-shaped apparatus body 50.
0 indicates X on the base table 80 by operating the operation handle 51 that constitutes the operation means with the operation switch 51a.
It is movable in each of the Y and Z directions.

A chin rest 82 for fixing the face of the subject is provided on one end surface side of the apparatus main body 50. The chin rest 82 includes a chin rest 83, a forehead rest 84, and a height mark 8
It is provided with a pillar 86 provided with 5, a chin rest handle 87 and the like.

On the other end surface of the apparatus main body 50, as shown in FIG. 4, an anterior face image of the eye E to be examined, a corneal reflection image described later,
Display means 72 is provided for displaying various measured values, blur confirmation images, and the like.

Above the display means 72, a chart switch board 73 constituting an operating means is provided. On the chart switch board 73, as shown in FIG. 3, a starburst chart switch 74a, a visual acuity chart switch 74b, a visual acuity chart switch 74c, a red-green chart switch 74d, a separated visual target switch 74e,
A picture chart switch 74f is provided.

On the other end side of the apparatus main body 50, as shown in FIG. 1, there is arranged a printer 90 which constitutes an output means having a printer cover 91, and a power source for the base table 80. Switch 93, power cord 94,
A mouse 96 that constitutes an operation means that can be operated by the subject is also provided.

Further, on the other end side of the apparatus main body 50, operating means provided with each mode setting of subjective measurement, objective measurement, addition measurement switch, deep switch, auto start switch, print switch and the like. Is provided with a switch unit 95.

Next, the optical configuration of the apparatus body 50 will be described with reference to FIGS.

The apparatus main body 50 includes an illumination optical system 400 for irradiating a subject's eye E with light, and an optical system 500 for illuminating the subject's eye E with various light fluxes and receiving a reflected image from the subject's eye E. And have.

The apparatus main body 50 including the illumination optical system 400 and the optical system 500 will be described in detail below.

An optical system 500 in the apparatus body 50
Is a cornea measurement system 1A for measuring the radius of curvature of the cornea C of the eye E, an objective refraction measurement system 2 for objectively measuring the refractive power of the eye E, and the visual axis of the eye E. Various visual targets such as a separate visual target 501, which is a visual target to be fixed to the eye E to be fixed during measurement, which will be described later, a picture chart, a starburst chart and a visual acuity chart for subjective examination, and a red-green chart. Gaze target system 3 for projecting
The observation / alignment system 4 is mainly configured to observe the anterior segment of the eye E and to align the optical axis of the optical system 500 with the visual axis of the eye.

A part of the optical path of the observation / alignment system 4 is shared with the optical path of the cornea measurement system 1A.

The cornea measuring system 1A is a cornea C of the eye E to be examined.
A pattern projection system 10 for projecting an annular pattern for measuring the radius of curvature of the eye toward the cornea C, and a measuring optical system 11 for measuring the size and shape of the corneal reflection image of the annular pattern. It is equipped with.

The pattern projection system 10 has an annular opening 1
00 and a ring-shaped light source 102 which is arranged behind the opening 100 and emits corneal measurement light having a wavelength of 930 nm to 1000 nm.

The light emitted from the annular light source 102 passes through the annular opening 100 and is projected onto the cornea C of the eye E as projection light. The projected light forms a virtual image of the annular opening 100 on the cornea C.

The corneal measurement light reflected by the cornea C enters the measurement optical system 11 as if it emitted a virtual image.

The measurement optical system 11 includes an objective lens 110 and
A mirror 111 that reflects visible light with a wavelength of 400 nm to 700 nm and transmits corneal measurement light (wavelength 930 nm to 1000 nm) in the long wavelength region of 800 nm or more, and infrared light with a wavelength of 865 nm is transmitted. And a mirror 112 that reflects infrared light having a wavelength of 900 nm or more, a relay lens 113, a diaphragm 114, a mirror 115 that transmits red light having a wavelength of 700 nm and reflects corneal measurement light, and a relay lens. 116, a mirror 117 that reflects infrared light having a wavelength of 865 nm and transmits corneal measurement light and red light having a wavelength of 700 nm, an imaging lens 118, an area CCD as the light receiving element 5, an image pickup tube, or the like. It is configured. The detection signal of the light receiving element 5 is processed by the image processing means 71 and sent to the display means 72 under the control of the control means 300 described later.

The cornea measuring light reflected by the cornea C is condensed by the objective lens 110 and then transmitted through the mirror 111. Then, the cornea measurement light is reflected by the mirror 112 and passes through the relay lens 113 to the central portion 1 of the diaphragm 114.
Pass 14b.

After that, the corneal measurement light is reflected by the mirror 115, and is transmitted by the relay lens 116 to the mirror 117.
Is transmitted to the image forming lens 11 through the mirror 117.
It is projected as a cornea measurement ring pattern on the light receiving element 5 by 8.

Refractive power measuring light having a wavelength of 865 nm emitted from the light emitting diode 200 constituting the pattern projection system 20 is received by the condenser lens 201 and then refracted by the conical prism 202 to confirm the blur for measuring the refractive power. The ring pattern 203 which also serves as a pattern is irradiated.

The refracting power measuring light passing through the ring pattern 203 is applied to the ring diaphragm 207 via the relay lens 204, the mirror 205 and the relay lens 206. The refracting power measuring light is transmitted through the ring diaphragm 207 and then reflected by the reflecting surface 208a of the perforated mirror 208.

After that, the refracting power measuring light is reflected by the mirror 2
The light is reflected by 09, passes through mirrors 112 and 111 as components of the measurement optical system 11 of the cornea measurement system 1A, and is projected by the objective lens 110 on the fundus Er of the eye E as an image of the ring pattern 203.

Here, the light emitting diode 200 and the ring diaphragm 207 are optically conjugate, and the ring diaphragm 2
07 and the pupil of the subject's eye E are set at positions optically conjugate with each other.

In the objective refraction measuring system 2, the light of the ring pattern image reflected by the fundus ER of the eye E to be examined is condensed by the objective lens 110. Then, the light passes through the mirrors 111 and 112, is then reflected by the mirror 209, passes through the opening 208b of the perforated mirror 208, and passes through the diaphragm 210.

The refracting power measuring light passes through the stop 210, the relay lens 211, and is then reflected by the mirror 212 that transmits visible light. The relay lens 213 and the mirror 214 are then reflected.
The light is applied to the filter 215 of the optical unit 219 via the.

This filter 215 has a wavelength of 865 nm.
It has a peripheral portion 215b that transmits the refracting power measuring light and a central portion 215a that cuts the refracting power measuring light.

The filter 215 is opaque to corneal measurement light having a wavelength of 930 nm to 1000 nm and 400 nm to 700 nm in the entire region.
Has the property of transmitting visible light. As a result, the refracting power measurement light passes only through the peripheral portion 215b of the filter 215, the visible light is reflected through the focusing lens 216, and the refraction power measurement light passes through the mirror 217 that transmits the refraction power measurement light. The light is reflected by the mirror 117 of the measurement optical system 11 and is irradiated by the lens 118 onto the light receiving element 5 as a ring pattern image (reflection image of the eclipse confirmation pattern) and converted into an electric signal.

The focusing lens 216 and the filter 215
Means that the light emitting diode 200, the condenser lens 201, the conical prism 202, and the ring pattern 203 of the pattern projection system 20 are housed together in the optical unit 219 and are movable in the optical axis direction. Is driven by the optical axis.

In the objective refraction measurement system 2, the diaphragm 21
0 is optically conjugate with the position of the pupil of the eye E to be inspected with respect to the objective lens 110, and the light receiving element 5 has a ring pattern 203 when the eye E is emmetropic (refractive power 0 Diopter).
It is optically conjugate with the intermediate image plane.

Visible light having a wavelength of 400 nm to 700 nm emitted by the light source 30 of the gaze target system 3 is condensed by the condenser lens 31 and illuminates the chart plate 32.

On the chart plate 32, a star burst chart, a visual acuity chart for subjective examination, a red-green separation chart 501, etc. are arranged in the circumferential direction, and each chart is selectively rotated by rotating around a shaft 34. Is inserted into the optical path of the gaze target system 3.

The light flux passing through the star burst chart, the separation chart 501, etc. is projected onto the eye E by the projection lens 35, and after being reflected by the mirror 36,
The light is reflected by the mirror 217, merges with the measurement optical system 21 of the objective refractive power measurement system 2, passes through the filter 215 via the focusing lens 216, and the mirror 214 and the relay lens 213.
Is guided to the mirror 212 via the mirror 212, passes through the mirror 212, and further, a pair of transmission holes 503a, 503b arranged corresponding to the pair of separated arrangement marks 501a, 501b forming the separation target 501 shown in FIG. The diaphragm (pupil division diaphragm) 503 and the variable cross cylinder 37 are provided.

As shown in FIG. 6, the pair of separatedly arranged marks 501a and 501b of the separation target 501 are composed of a pair of prisms 502a and 502b arranged so that their inclination angles are equal and their inclination directions are opposite to each other. It is attached to the center of the split prism 502.

Then, the light flux passing through the variable cross cylinder 37 passes through the variable cross cylinder 37, is reflected by the mirror 38 and the mirror 111, is projected onto the eye E by the objective lens 110, and is observed by the eye E. It is like this.

The separation optotype 501 and the fundus ER of the eye E to be examined are set in a conjugate arrangement when the eye E is emmetropic, and the diaphragm 503 and the pupil EI of the eye E are set to a conjugate arrangement. Has become.

Further, in the vicinity of the chart plate 32,
Glare light source 3 for emitting visible light for glare test
A plurality of 3 are arranged. The glare light source 33 can also be arranged near the objective lens 110. Also,
Instead of providing the light source 33 to perform the glare test,
For example, the contrast between the visual acuity chart and the base of the chart plate 32 may be changed.

A plurality of light emitting diodes 40 for anterior ocular segment illumination are arranged outside the pattern plate 101 of the pattern projection system 10 in the cornea measuring system 1A, and the red light having a wavelength of 900 nm emitted from each of the light emitting diodes 40. Outside light
The anterior ocular segment of the eye E to be inspected is illuminated.

The light reflected by the anterior segment of the eye E to be examined is condensed by the objective lens 110, passes through the mirror 111, and is propagated along the measuring optical system 11 of the cornea measuring system 1A described above. An image is formed on the light receiving element 5 by the image forming lens 118.

On the other hand, the light from the focusing / positioning light source 41 which emits infrared light having a wavelength of 900 nm is transmitted through the relay lens 41.
a, the half mirror 119 is projected through the objective lens 110 of the optical system 500 onto the cornea C of the eye E to be inspected.

An observation / alignment system 4 is arranged in front of the mirror 115 of the measurement optical system 11 in the cornea measurement system 1A. This observation / alignment system 4 has a wavelength of 7
The light emitting diode 42 that emits light (scale light) of 00 nm, the condenser lens 43 that condenses the scale light from the light emitting diode 42, and the scale light that has passed through the aiming scale 44 is reflected to join the measurement optical system 11. It is composed of a mirror 45 and a mirror 45.

The scale light from the sighting scale 44, after passing through the mirror 115, is projected onto the light receiving element 5 by the lens 118 via the measurement optical system 11, whereby
As shown in FIG. 9, the alignment circle AR is displayed on the display means 72.

Next, regarding the control system of the ophthalmologic apparatus 1,
This will be described with reference to FIG.

The ophthalmologic apparatus 1 comprises a control means 300 including a program memory 311 storing a control program and a control section 310 for controlling the whole, and the control section 31.
The mouse 96, the operation lever 51, the chart switch board 73, the printer 90, the switch unit 95, and the display means 72 are connected to 0.

Also, the illumination optical system 4 is controlled by the control unit 310.
00, control of the optical system 500 and drive control of the lens driving unit 320, and the focusing lens 216.
Is continuously moved in the (+) direction or the (-) direction shown in FIG.

Furthermore, the control unit 310 calculates the subjective measurement value, the objective measurement value, the blurring degree of the blurring confirmation pattern, etc. based on the processing results of the light receiving element 5 and the image processing means 71 which are measured by the respective optical systems. The calculation means 330 is connected.

Next, the operation of the ophthalmologic apparatus 1 will be described.

First, the precise measurement of the subjective sphericity of the eye E will be described with reference to FIGS.

For precise measurement of the subjective sphericity of the eye E, the diaphragm 503 is arranged in the optical path of the objective refraction measuring system 2 and the power switch 9 of the ophthalmologic apparatus 1 is used.
3 is turned on, the examiner sets the objective optometry mode by the switch unit 95, and the switch panel 7
By pressing the separation target switch 74e of No. 3, the separation target 501
Is inserted into the optical path of the gaze target system 3.

In this state, visible light having a wavelength of 400 nm to 700 nm emitted by the light source 30 of the gaze target system 3 is condensed by the condenser lens 31 and illuminates the separation target 501 on the chart plate 32.

Marks 501a, 501 of the separation target 501
The light flux that has passed through b becomes a pair of light fluxes separated by the prisms 502a and 502b of the split prism 502, and merges with the measurement optical system 21 of the objective refractive power measurement system 2 through the projection lens 35, the mirror 36, and the mirror 217. , A focusing lens 216, a filter 215, a mirror 214, a relay lens 213, a mirror 212, a mirror 212, and a pair of separation targets 501 shown in FIG. Separately placed mark 501
The pair of light fluxes is narrowed by the pair of transmission holes 503a and 503b in the diaphragm 503 arranged corresponding to a and 501b, and is guided to the variable cross cylinder 37.

The pair of light beams passing through the variable cross cylinder 37 are reflected by the mirror 38 and the mirror 111, projected onto the eye E by the objective lens 110, and visually recognized by the eye E.

At this time, when the subject presses the plus button or the minus button of the mouse 96 with his / her finger, the lens driving section 320 is optically operated under the control of the control section 310 based on the signal from the mouse 96. The unit 219 is displaced, and the position of the focusing lens 216 is displaced along its optical axis in the plus direction (+) or the minus direction (−) as shown in FIG.

As a result, the images of the pair of separated marks 501a and 501b visually recognized by the eye E are, as shown on the left side, center, and right side of FIG.
The images 601a and 601b of 1b change from a state in which they are separated left and right to a state in which they partially match and a state in which they completely match.

Note that, in FIG. 8, the image 601a of the mark 501a is shown by diagonally shaded red, and the image of the mark 501b is shown.
Image 601b is shown by a horizontal line indicating green.

Marks 501a and 501 shown on the right side of FIG.
When the images of b are completely matched, the marks 501a,
01b is the same as the fundus ER of the eye E to be inspected, and the eye E is a white image 602 in which red and green are mixed.
(Indicated by cross hatched lines) is visually recognized, and at this time, the eye E is visually recognizing a distance position (0 diopter for an emmetropic eye) where the accommodation force does not work.

Further, the position of the focusing lens 216 is displaced in the minus direction along the optical axis by operating the mouse 96, and the images of the marks 501a and 501b are moved to the image 602 as shown in the center of FIG. The images 601a, 60 on both sides
The limit position at which 1b protrudes means the limit of the accommodation force (several diopters) of the eye E, that is, the near position which deviates from the measured value of the distance position by several diopters.

The state of each eye E at the distance position and the near position of the eye E in each of such states is automatically measured by the gaze target system 3, and the image processing means 71 and the computing means 33 are used.
With the operation of 0, the spherical power S, the cylindrical power C, and the axial angle A are obtained, and these values are displayed on the display means 72.

In this way, the subject himself / herself makes a subjective measurement of the subject's eye E by the images 601a, 601b and the image 6 described above.
You can do it while watching 02.

The mark 501 shown on the right side of FIG.
In the state where the images of a and 501b are completely matched and the subject's eye E visually recognizes the white image 602 (shown by cross hatched lines), the subject operates the plus button of the mouse 96, for example. The lens driving unit 320 moves the optical unit 219 under the control of the control unit 310,
The focusing lens 216 is continuously fogged by a predetermined amount of fog. Accordingly, the subject can operate the mouse 96 to perform precise measurement of the spherical power of the subject's eye E.

A specific example of the precise measurement of the spherical power of the eye E to be examined will be described in detail with reference to FIGS. 9 to 12.

FIG. 9 is a schematic optical path diagram of the ophthalmologic apparatus 1 when the eye E is 0D, and FIG. 10 is a schematic optical path diagram of the ophthalmologic apparatus 1 when the eye E is -5D.

Now, the objective measurement value of the spherical power S of the eye E to be measured when the above-described eye E is measured is -5D.
Assume that At this time, as shown in FIG. 10, the separation target 501 has the objective measurement value of the spherical power S of the eye E to be −5D.
For example, the position is fixed for about 1 second.

After that, the lens driving unit 320 is controlled by the control of the control unit 310 based on the above-described operation, and the spherical power S of the focusing lens 216 of the optical unit 219 is changed by + 0.25D step. As described above (the astigmatic power C and the axial angle A are constant), the cloud is continuously made. The movement amount x of the focusing lens 216 at this time is x = f × D / (10
00-15D).

Here, D is the degree of refraction, the moving amount x is the moving amount based on 0D, and f is the focusing lens 216 and the relay lens 2.
13 composite focal lengths.

FIG. 11 shows the relationship between the amount of fog when the cloud is fogged in four steps of + 0.25D steps in this way and the objective measurement result by the ophthalmologic apparatus 1.

As is apparent from FIG. 11, the objective measurement value of the spherical power S associated with the second and subsequent clouds is -0.00D among the four stages of cloud, and therefore the second cloud is The associated measured value of the spherical power S indicates the limit of the accommodation power of the eye E to be examined.

The cloud amount and the objective measurement result by the ophthalmologic apparatus 1 are automatically measured by the gaze target system 3,
The spherical power S, the astigmatic power C, and the axial angle A are obtained by the operations of the image processing means 71 and the computing means 330, and these values are displayed on the display means 72 and printed by the printer 90 as shown in FIG. To be done.

At this time, among the cloud of four stages, a mark indicating the limit of the accommodation power of the eye E is attached to the position of the objective measurement value S-0.00D of the spherical power S associated with the second cloud. If printed, the examiner can know at a glance the complete correction value indicating the limit of the accommodation power of the eye E, and based on this complete correction value, the spectacle lens worn by the subject. It is possible to estimate the subjective comfort level of a new spectacle lens taking into account the spherical power, cylindrical power, and axial angle of.

The present invention can be variously modified within the scope of the invention in addition to the above-described embodiments.

[0082]

According to the present invention described in detail above, the following effects can be obtained.

According to the first aspect of the present invention, it is possible to provide an ophthalmologic apparatus capable of accurately measuring the limit of the accommodation power of the eye to be inspected.

According to the second aspect of the invention, in addition to the effect of the first aspect of the invention, an ophthalmologic apparatus capable of estimating the subjective comfort level of the eye to be examined and selecting the most suitable spectacle lens is provided. be able to.

[Brief description of drawings]

FIG. 1 is a perspective view of an ophthalmologic apparatus according to an embodiment of the present invention viewed from an examiner side.

FIG. 2 is a perspective view of the ophthalmologic measuring apparatus according to the embodiment of the present invention viewed from the subject side.

FIG. 3 is an explanatory diagram showing a chart switch board of the ophthalmologic apparatus of the present embodiment.

FIG. 4 is an explanatory diagram showing a display example of a display unit of the ophthalmologic apparatus of the present embodiment.

FIG. 5 is an optical layout diagram of the ophthalmologic apparatus according to the present embodiment.

FIG. 6 is an optical layout diagram for projecting a separation target in the ophthalmologic apparatus of the present embodiment onto an eye to be examined.

FIG. 7 is a block diagram of a control system of the ophthalmologic apparatus of this embodiment.

FIG. 8 is an explanatory diagram showing a visual recognition state of the eye to be inspected of the separated optotype of the ophthalmologic apparatus of the present embodiment.

FIG. 9 is an optical layout diagram of the ophthalmologic apparatus according to the present embodiment when the spherical power is 0D.

FIG. 10 is an optical layout diagram of the ophthalmologic apparatus according to the present embodiment when the spherical power is −5D.

FIG. 11 is a table showing the relationship between the amount of fog and the objective measurement result in the ophthalmologic apparatus of the present embodiment.

FIG. 12 is a table showing a print example of cloudiness amounts and objective measurement results in the ophthalmologic apparatus of the present embodiment.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Ophthalmologic apparatus 1A Corneal measurement system 2 Objective refraction measurement system 3 Gaze target system 4 Observation / alignment system 30 Light source 50 Device body 72 Display means 73 Chart switch board 90 Printer 95 Switch section 216 Focusing lens 219 Optical unit 300 Control means 330 Calculation means 500 Optical system 501 Separable visual target 501a Mark 501b Mark 503 Aperture 601a image 601b image 602 image

 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Takeshi Nakamura 75-1 Hasunuma-cho, Itabashi-ku, Tokyo Topcon Co., Ltd.

Claims (2)

[Claims] 1. An objective refraction measuring system for objectively measuring the refractive power of an eye to be examined, a gaze target system having a gaze target for fixing the eye to be examined, the objective refraction measuring system and the gaze target system. A calculation means for obtaining the objective measurement value of the eye to be examined based on the measurement result by
After setting the gazing target of the gazing target system at the distance position of the eye to be examined, which is obtained by this computing means, there is provided control means for continuously performing objective measurement while making the gazing target cloud. Ophthalmic equipment. 2. An objective refraction measuring system for objectively measuring the refractive power of the eye to be examined, a gaze target system having a gaze target for fixing the eye to be examined, the objective refraction measuring system and the gaze target system. Spherical diopter of the eye to be inspected based on the measurement result by, the astigmatic diopter, a calculation means for obtaining an objective measurement value consisting of an axial angle, and the gazing target of the gaze target system at the distance position of the eye to be examined obtained by this computing means After setting, control means for continuously performing objective measurement while fogging the gaze target so that the amount of fog changes at a predetermined step value, and the amount of gaze target fog associated with the continuous objective measurement. And output means for visibly outputting each measurement result of the objective refraction measurement system, and based on the spherical power value that the value in each measurement result of the objective refraction measurement system output by this output means does not change. That it was possible to estimate the subjective comfort level of eyeglass lenses that should be prescribed to Ophthalmic apparatus and butterflies.