JPH11225966A - Ophthalmologic measurement device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To continuously measure the change of the data on eye refracting power or the like before and after the change by providing the device with an indexing system which makes the presentation in the condition that an index is changed from a first index position to a second index position corresponding to the operation of an inspector. SOLUTION: When an inspector operates a measurement start switch 19 indicating the start of the measurement, a control part 18 lights a first index 35 first of all, and then switches the same to a second index to change the index position presented to a person to be measured. Further the control part 18 fetches an image signal from a light receiving element before and after the change of the index position by the switching operation to operate the data every specified time interval during a first specific period, and the data of every specified time interval during a second specified period after the change of the index position by the switching operation, and to store the same in a frame memory 16. The refracting power, the pupil diameter and the distance between pupils (DP) of both eyes are computed on the basis of the first index position data and the second index position data stored in the frame memory 16.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmologic measuring apparatus, and more particularly to an ophthalmologic measuring apparatus for measuring data changes in interpupillary distance, eye refractive power, and pupil diameter of an eye to be measured when an index of a different position is presented to the eye to be measured. It concerns the device.

[0002]

2. Description of the Related Art Conventionally, there has not been provided an apparatus suitable for continuously obtaining data of eye refractive power, interpupillary distance and pupil diameter before and after the change, particularly when the position of an index is changed. Was.

[0003]

In recent years, when the position of an index is changed, there is a demand to continuously measure changes in data of eye refractive power, interpupillary distance and pupil diameter before and after the change. .

The present invention has been made in view of the above circumstances, and provides an ophthalmologic measuring apparatus that meets the above-mentioned demands.

[0005]

According to the present invention, there is provided a light source unit for emitting an illumination light beam for illuminating the fundus of both eyes of a person to be measured, and an illumination light beam from the light source unit is applied to the fundus of both eyes of the person to be measured. An illumination optical system that illuminates and blocks a part of the reflected light flux from the fundus of both eyes of the measurement subject irradiated with the illumination light flux, and the light amount distribution according to the eye refractive power at a position substantially conjugate with the pupil of the measurement target eye. As a change occurs, a light receiving optical system including a light shielding portion disposed in the optical path thereof, and a light receiving portion disposed at a position substantially conjugate with the pupil of the eye to be measured and receiving the light beam received from the light receiving optical system. And a storage unit for storing a light receiving signal of the light receiving unit, and presenting an index to the person to be measured by changing the index presenting position from the first index position to a second index position different from the first index position according to the operation of the measurer. And the light receiving unit obtained before and after the change of the index position by the index system. The present invention relates to an ophthalmologic measurement apparatus including an arithmetic unit that obtains data of a pupil distance of an eye to be measured before and after an index position change, an eye refractive power, and a pupil diameter based on an optical signal. Has multiple indicators,
One of the indicators is configured to be presented as an alternative, and the storage unit relates to an ophthalmologic measurement apparatus configured to store a light receiving signal of the light receiving unit before and after switching of the index, Further, the index system is configured to present the index to the subject at different positions in accordance with the operation of the measurer, and the storage unit performs the presentation of the index at a different position to the subject with the index system. The present invention relates to an ophthalmologic measurement apparatus configured to store a light receiving signal of the light receiving unit during a first predetermined period before a time point and during a second predetermined period after the time point. The position at which the index is presented to the person to be measured is changed after the first predetermined period elapses, and the storage unit stores the first predetermined period, the index position change period, and the second
The present invention relates to an ophthalmologic measurement apparatus configured to store a light receiving signal of the light receiving unit for a predetermined period, and the indicator system causes a subject to present an index at a different position according to an operation of a measurer. The storage unit is configured to control the first predetermined period before the time when the index system presents the index to the subject at a different position by the control unit and the index change after the time. An ophthalmologic measurement apparatus configured to store a light receiving signal of the light receiving unit during a period and a second predetermined period, wherein the calculation unit performs the change from a first predetermined period before the change of the index position. Data on the interpupillary distance, eye refractive power, and pupil diameter of the measurement target eye before and after the index position change are obtained based on the light receiving signals of the light receiving unit continuously obtained during a period until the second predetermined period elapses. Ophthalmology measuring device Furthermore interpupillary distance measured eye before and after the obtained index position change due to the operation unit, the eye refractive power,
The pupil diameter data or, in addition to these data, a change in data of the interpupillary distance, eye refractive power, and pupil diameter of the measurement target eye during the second predetermined period after the change in the index position obtained by the arithmetic unit is displayed. The present invention relates to an ophthalmologic measuring apparatus provided with a display unit.

[0006]

Embodiments of the present invention will be described below with reference to the drawings.

A first embodiment will be described with reference to FIGS.

In FIG. 1, reference numeral 15 denotes a measurement optical system using infrared light, and reference numeral 31 denotes a fixation target system using visible light.

The optical axis of the measuring optical system 15 and the optical axis of the fixation target system 31 are divided by a dichroic mirror 32 disposed facing the subject, and the dichroic mirror 3
The fixation target system 31 is disposed on the second transmission optical axis 37, and the measurement optical system 15 is disposed on the reflection optical axis 38 of the dichroic mirror 32.

The transmission optical axis 37 is further provided with a half mirror 34.
The first fixation target 35 for long distance is disposed on the transmission optical axis of the half mirror 34, and the second fixation target 36 for short distance is disposed on the reflection optical axis of the half mirror 34. Are arranged. Although not shown, the first fixation target 35 and the second fixation target 36 each include a fixation target illumination source that emits a light beam in the visible range, and the fixation target illumination source is selectively turned on. ing.

The measuring optical system 15 will be described with reference to FIG. Reference numeral 1 denotes an irradiation optical system for projecting a light source image onto the fundus 7 of the eye 3 to be measured. Reference numeral 2 denotes a light receiving optical system for receiving a light beam 10 reflected by the fundus 7.
The light receiving optical system 2 is arranged to face the eye 3 to be measured.

The illumination optical system 1 includes an illumination light beam 1 in the infrared region.
1 and the illumination light beam 11
The illumination optical system 1 projects the illumination light beam 11 from the light source 4 through the pupil 6 onto the fundus 7 so as to form an image of the light source 4. When the eye refractive power of the eye 3 to be measured is a reference diopter value (reference eye refractive power), the image of the light source 4 is focused on the fundus 7.

The light receiving optical system 2 comprises a light shielding member 12, an imaging lens 8 and a light receiving element 9 arranged opposite to the eye 3 to be measured, and the reflected light beam 10 from the fundus 7 is transmitted through the half mirror 5 The light is guided onto the light receiving element 9. The light receiving element 9
Is an area CCD, an image pickup tube, or an aggregate of two or more of them. The light receiving surface 9a of the light receiving element 9 is arranged at a position conjugate with the pupil 6 of the eye 3 to be measured with respect to the imaging lens 8.

The light-shielding member 12 has an edge portion, and the edge of the edge portion coincides with the optical axis O of the light receiving optical system 2 and is arranged so as to shield one side of the light beam 10 with the optical axis O as a boundary. The half mirror 5 is provided at a position conjugate with the light source 4 so that the image of the fundus 7 is focused on the light shielding member 12 when the eye refractive power of the eye 3 to be measured is a reference diopter value. Is set.

In the figure, reference numeral 13 denotes an arithmetic unit, and the arithmetic unit 1
3, the light receiving element 9, the first fixation target 35, and the second fixation target 36 are connected.

The arithmetic unit 13 is provided with the first fixation target 3
5, controlling the blinking of the second fixation target 36 and the light receiving element 9
The diopter value, the pupil diameter and the distance between the pupils are calculated from the light receiving state and the light amount distribution of the above, and the result is output to the display 14.

The measurement of the eye refractive power is performed by using the fixation target system 3
The first fixation target 35 or the second fixation target 36 is collimated.

The principle of measurement of the three components of the eye refractive power, the pupil diameter, and the distance between the pupils in the ophthalmologic measuring apparatus having the above configuration will be described below.

As shown in FIG. 3A, when the diopter value of the eye 3 to be measured is a negative diopter value compared to one selected reference diopter value, the image of the light source 4 is located in front of the fundus 7. Considering the reflected light beam 10 reflected at one point on the optical axis in the fundus 7 illuminated by this light beam, the reflected light beam 10 is located in front of the light shielding member 12, that is, the eye 3 to be measured. The upper half (shaded portion) of the light beam condensed on the side and projected onto the light receiving element 9 by the imaging lens 8 is shielded by the light shielding member 12.

On the other hand, as shown in FIG. 3B, when the diopter value of the eye to be measured is the reference diopter value, the reflected light beam 10 is condensed on the light shielding member 12, so that the reflected light beam 10 is blocked. It is not blocked by the member 12.

Further, as shown in FIG.
Is more positive than the reference diopter value, the image of the light source 4 is projected so as to form an image behind the fundus 7, and the reflected light flux 10 reflected by the fundus 7 The reflected light flux 10 condensed on the rear side, that is, on the light receiving element 9 side, and projected on the light receiving element 9 is shielded from the light beam (the upper half in the figure) of the portion opposite to that shown in FIG.

The light flux projected on the light receiving surface 9a changes its light quantity distribution state with respect to the reference diopter value according to the magnitude of the diopter value of the eye 3 to be measured, and whether the diopter value is positive or negative. Is required.

The light receiving element 9 is for detecting the light quantity distribution of the light beam formed on the light receiving surface 9a. The computing unit 13 is formed on the light receiving surface 9a based on the signal from the light receiving element 9. The light amount distribution of the luminous flux is detected, and it is determined whether the eye refractive power of the eye to be measured is positive or negative with respect to the reference diopter value, and its absolute value is calculated. The display 14 displays the obtained result.

In the above embodiment, a half mirror is used as the light beam separating means. However, it goes without saying that various light beam separating means such as a beam splitter and a polarizing prism can be used.

4 (A) to 4 (E), the distribution of the amount of light of the light beam formed on the light receiving surface 9a will be described.

In order to simplify the description in FIGS. 4A to 4E, the optical axis of the light source 4 and the optical axis of the light receiving optical system are matched, and the light shielding member 12 and the imaging lens 8 Are matched. For this reason, the light source 4 and the imaging lens 8 are shown superimposed at the same position, and the light blocking member 12 is omitted.

FIG. 4 (A) ~ (E) shows the case of a negative to the eye refractive power D is the reference eye refractive power D ₀ to be measured eye,
In the following description, it is assumed that all light beams reflected from the fundus 7 are projected onto the light receiving surface 9a by the imaging lens 8. When the distance between the light source 4 and the pupil 6 of the eye to be measured is set to l, and the eye refractive power of the eye to be measured at which the image of the light source is focused on the fundus 7 is defined as the reference eye refractive power D ₀ , the following equation 1 is obtained.

[0028]

## EQU1 ## D ₀ = −1000 / l

FIG. 4A shows that the eye refractive power of the eye to be measured is D.
In the case of (<D _0), shows a projection light flux from a point S ₀ on the axis of the slit-like light source 4 having a length of L in the direction perpendicular to the optical axis, the image of the point S ₀ once , S ₀ ′, and is projected as a blurred image onto the fundus 7 of the eye to be measured. The area 7a to be projected becomes wider as D ₀ -D becomes larger.

FIG. 4B shows the state of the light beam reflected from the light receiving optical system 2 and the fundus 7 of the eye to be measured.

As shown in FIG. 4 (B), the fundus 7
Considering a light beam from a point I _-n end of the projection area of the upper, the image I _-n of this point 'from the measurement object eye pupil 6 l' is imaged at a distance of, the light beam is imaged The light is projected via a lens 8 onto a light receiving element 9 arranged at a position conjugate with the pupil 6 of the eye to be measured. The relational expression between l ′ and the eye refractive power D of the eye to be measured is as follows.

[0032]

## EQU2 ## D = -1000 / l '

On the other hand, the spread width Δ of the luminous flux emitted from one point on the fundus 7 on the edge is determined by setting the pupil diameter of the eye to be measured to u.
Then, as is apparent from FIG.

## EQU3 ## Δ = u × (l−l ′) / l ′

From Expressions 1 and 2, the following Expression 4 is obtained.

[0035]

Δ = u × (l−l ′) / l ′ = u {(− 1000 / D ₀ ) − (− 1000 / D)} / (− 1000 / D) = u (D / D ₀ −) 1) = u × (ΔD / D ₀ ) Here, ΔD = D−D ₀ .

As the difference between the eye refractive power D of the eye 3 to be measured and the reference eye refractive power D ₀ increases, the spread on the light shielding member 12 increases.

Next, the spread of the light beam on the light receiving element 9 will be described. The light receiving element 9 is always arranged conjugate with the pupil 6 of the eye to be measured with respect to the imaging lens 8 irrespective of the eye refractive power of the eye 3 to be measured. Assuming that the magnification is β, βu on the light receiving element 9
Area of diameter (not affected by the refractive power of the eye to be measured)
A light beam is projected on the surface.

Further, a point In which is symmetric with respect to the optical axis with respect to the optical axis.
Similarly, after forming an image In at a position 1 'from the pupil 6 of the eye to be measured, the light flux from the light source is projected onto the same region βu on the light receiving element 9. When the light source 4 is a point light source and there is no light blocking member 12, each point In,...
.. In determine the light quantity distribution on the light receiving element 9.

Here, in order to consider the light amount distribution on the light receiving element 9, the end position P-n of the light beam projection position on the light receiving element 9, that is, the coordinate position −βu / 2 centered on the optical axis. Considering the incident light beam, the light beam incident on this position is shown in FIG.
It is limited to the light flux in the range of the oblique line A in (C).
Similarly, considering the light beam incident on the position Pn symmetrical to the above-mentioned P-n position with respect to the optical axis, the light beam is limited to the light beam in the range of the oblique line A '. Then, the eye pupil 6 to be measured
When an edge-shaped light-blocking member 12 for blocking one light beam A 'on the optical axis is disposed at a distance of l from the light source 4 (a position conjugate with the light source 4), the light beam incident on the position P-n on the light receiving element 9 is blocked. The light flux is not blocked by the member 12, but is gradually blocked as it goes from the position P-n to the upper position, half of the light flux is blocked at the center P0 position, and all light beams are blocked at the position Pn. It will be. Therefore, the light becomes darker on the light receiving element 9 as it goes upward due to the edge-shaped light shielding member 12, and the light quantity distribution has a constant slope where the light quantity becomes zero at the point Pn.

In FIGS. 4A to 4C, only a light beam emitted from one point on the optical axis of the light source 4 is shown, but one point Sn at the end of the light source 4 (the size of the light source is L Considering the luminous flux from the point of -L / 2 coordinate position), the result is as shown in FIG. The luminous flux from this point Sn is projected onto an area from the In point to the In point on the fundus of measurement 7 shown in FIG. 4D, and the reflected light from the In and In points is In a manner similar to the above, I-n 'and In-In are located at a distance of l' from the pupil 6 of the eye to be measured.
Is formed on the light receiving element 9 and projected onto a region having a diameter of βu. Here, the point S at the end of the light source 4
Among the light beams emitted from -n, the light beam incident on the end position P-n of the light beam projection on the light receiving element 9 is a light beam in a hatched area B in FIG. 4D.

Further, one point S of the light source 4 symmetrical to the point of Sn
Considering the luminous flux from n, and considering the luminous flux incident on the point P-n on the light receiving element 9, the luminous flux is in the hatched area C in FIG. As described above, when the light source 4 is considered to have a certain size, the amount of light at one point on the light receiving element 9 must be considered as the sum of the light flux from each point of the light source 4.

FIG. 5A shows the respective light beams incident on the position P-n on the light receiving element 9 based on the above-mentioned concept, and shows the position of the Sn on the light source 4. Among the light beams emitted from the light source, the light beam incident on the position P-n is a region B (see FIG. 4D), and as the position on the light source 4 moves upward, the light beam also moves upward, At the light source position S0, the light flux is in the area A (see FIG. 4C), and at the position of Sn on the light source 4, the light flux is in the area C (FIG. 4E).
reference). Therefore, the light quantity at the point P-n on the light receiving element 9 is
It can be considered as the sum of these light fluxes.

Here, the point P on the light receiving element 9 when the light shielding member 12 is arranged at a distance of 1 from the pupil 6 of the eye to be measured.
FIG. 5B is a schematic diagram showing the light amount of -n.

FIG. 5B shows how the light beam is blocked by the light blocking member 12 as the position on the light source 4 changes. The horizontal axis in FIG. 5B indicates the coordinate position on the light source 4 and the vertical axis indicates the light amount. Considering the luminous flux from each point on the light source 4, −L / 2 (L is the coordinate position). The light beams from the point (the size of the light source) to the zero point are not shielded by the light shielding member 12, but are gradually shielded after passing the coordinate point 0, and all the light beams are blocked at the position of Δ (the spread of the light beam). It will be done.

FIG. 5B shows the contribution of the light amount from each point on the light source, where k is the light amount from each point on the light source when the light is not shielded. This corresponds to the light amount value at point P-n on the element. This area value T is as shown in the following Expression 5.

[0046]

## EQU5 ## T = 1 / 2k (L + Δ)

Similarly, other points on the light receiving element 9 will be considered. FIG. 6A shows the light beam incident on the center point P0 on the light receiving element 9 in the same manner as FIG. 5A, and the light beam P0 of the light beam from the point S-n on the light source 4 is shown. The light flux incident on the point is a shaded area of B0, a shaded area of A0 from the point of the center S0 on the light source 4 is a shaded area of A0, and a light flux from the point of Sn on the light source 4 is a light flux in the shaded area of C0. Element 9
6B corresponds to the area T0 of the hatched area in FIG. 6B. That is, considering the light flux incident on the center point P0 of the light receiving element 9 from each point of the light source 4,
From the coordinate position -L / 2 on the light source 4 to the position -Δ / 2, the light beam is not blocked, and after passing the -Δ / 2 position, the light beam is gradually blocked and all the light beams are blocked at the position of Δ / 2. The light beam is cut off, and when this area value T0 is calculated in the same manner as described above, the area value T0 becomes a value represented by the following equation (6).

[0048]

## EQU6 ## T0 = kL / 2

Similarly, the state of the light beam incident on the point Pn on the light receiving element 9 and the light amount at this point are shown in FIG.
(A) and FIG. 7 (B). In FIG. 7A, of the light beams from the point S-n on the light source 4, the light beam incident on the point Pn is a shaded area of B ", and A" from the point of the center S0 on the light source 4.
7B, the light flux from the Sn point on the light source 4 is shown as the light flux in the C "hatched area. In this case, as shown in FIG. Considering the luminous flux incident on the point Pn, from the position -L / 2 on the light source-
The luminous flux is not blocked until the position of Δ, the luminous flux is gradually blocked after passing the −Δ position, and all the luminous flux is blocked at the position of 0. When this area value T0 'is calculated, the following equation 7 is obtained.
It becomes the value shown in.

[0050]

## EQU7 ## T0 '= k (L-.DELTA.) / 2

As can be seen from the results of Equations (5), (6), and (7), the light amount on the light receiving element 9 gradually decreases as going upward from below. The light amount distribution above linearly changes as shown in FIG.

In the above description, the spread width Δ on the light-shielding member 12 when considering a light beam emitted from one point of the fundus is considered.
Has been described on the assumption that is smaller than 1/2 of the size L of the light source.

Next, when the eye refractive power of the eye 3 to be measured shown in FIG. 3B is a reference value, and when the eye refractive power of the eye 3 to be measured shown in FIG. Similarly, the light amount distribution on the light receiving element 9 can be considered in the same manner as described above. In this case, when the eye refractive power of the eye 3 to be measured is a reference value,
As shown in FIG. 9, when the uniform distribution and the eye refractive power of the eye 3 to be measured are positive, the distribution state is opposite to that shown in FIG. 8, as shown in FIG.

The slope of the light quantity distribution described above indicates the diopter value (eye refractive power), and the direction of the slope indicates the sign of the diopter value. This will be described below with reference to FIG.

If the slope of the light quantity distribution is defined as Δf / f0,

Δf / f0 = (kΔ / 2) / (kL / 2) = Δ / L

The spread Δ of the light beam, that is, the amount of blur Δ
Is given by Equation 9 below from Equation 4.

[0057]

Δ = u × (l−l ′) / l ′ = u × ΔD / D ₀

Therefore, the following equation (10) is obtained from the equation (8).

[0059]

[Equation 10] _{Δf / f0 = uΔD / LD 0} ∴ ΔD = (LD 0 / u) (Δf / f0) ΔD = K (Δf / f0), (K = LD 0 / u)

## EQU10 ## Therefore, the equation (10) represents the reference diopter value D.
Deviation ΔD and Δ of the diopter value of the eye to be measured with respect to ₀
This shows that f / f0 is proportional. Accordingly, the deviation Δ of the diopter value of the eye to be measured can be obtained by obtaining Δf / f0 from the light quantity distribution, and the diopter value D can be obtained by the following equation (11).

[0061]

[Formula 11] D = D ₀ + ΔD

As described above, the diopter value of the eye to be measured can be obtained from the light amount distribution of the light beam reflected from the fundus. Note that the above-described light amount distribution is schematically illustrated, and in practice, the change in light amount corresponding to each part of the eyeball shown in FIG. 12A (see FIG. 12B, the light amount shown in FIG. 12B). The distribution indicates the light amount distribution at the reference diopter value), that is, the protrusion ρ of the light amount at the bright spot 21 due to the reflection of the cornea.
Or a drop σ in the amount of light at the iris 20 part outside the pupil 6. In addition, blinking at the time of measurement, or eyelashes,
There are various factors that affect the measurement results, such as lens turbidity.

Accordingly, a more specific description will be given below.

In FIG. 14, reference numeral 15 denotes a measuring optical system of the above-mentioned ophthalmologic measuring apparatus, 9 denotes a light receiving element, 13 denotes a calculator, 14 denotes a display, and 16 denotes an image of the light receiving element 9 and a result of an arithmetic processing section. A frame memory, 17 an arithmetic processing unit, 18 a frame memory 16, a synchronization command for the arithmetic processing unit 17,
A control unit 19 for switching the lighting of the fixation target 35 and the second fixation target 36 and performing a sequence command such as control of taking in data from the light receiving element 9 is a measurement start switch 19.

Hereinafter, the measurement operation of the eye 3 to be measured in a predetermined state, for example, when the first fixation target 35 in FIG. 1 is turned on and the subject is collimated with the first fixation target 35 FIG.
This will be described with reference to FIG.

First, the examiner observes the image of the eye to be measured displayed on the display 14. FIG. 16A shows a screen on the display 14, on which an eye image to be measured is displayed so as to overlap with the reference indices 22R and 22L indicating a predetermined area. At the center of the pupil of the binocular image of the eye to be measured, a bright spot image formed by a light beam reflected by the cornea of the eye to be measured among the light beams from the light source 4 is formed. The examiner confirms that the binocular images are included in the reference indices 22R and 22L, that the approximate alignment adjustment is completed, and that the subject is aiming straight, and then the measurement start switch 19 Turn ON. ON of this measurement start switch 19
As a result, the video signal from the light receiving element 9 is
6 and stored. A plurality of video signals are automatically and continuously stored in the frame memory 16 at predetermined time intervals by one operation of the measurement start switch 19.

The time interval for capturing a plurality of video signals is set such that the change in the factors of the eye refractive power, the pupil diameter, and the distance between the pupils of the eye to be measured can be detected. If this time interval is 1/15 second, for example, 15 frames can be captured per second. The capture time interval is 1
It is desirable to set to capture several frames or more per second.

The arithmetic processing unit 17 stores the frame memory 1
The arithmetic processing is performed by the steps described below based on the video image stored in 6.

First, the position of a bright spot image generated by corneal reflection is detected.

The image stored in the frame memory 16 is such that both eyes have a predetermined area (corresponding to the area of the above-mentioned reference indices 22R and 22L), for example, the right eye has (X1; Y1).
Are imaged so as to be included in. FIG. 16B is an enlarged view of this area.

(X 1; Y 1) of the frame memory 16
The light quantity is compared between the pixels of the light receiving element 9 within the area, and a point 21p having the highest light quantity value is obtained. This point 21p
Is a point having the brightest light amount in the bright spot image. FIG.
(C) is an enlarged view of the area around the bright spot. Next, a predetermined area (Jx;
Jy). In this area, the light amount values of the images are compared, points of the image at a predetermined level or higher are extracted, and the center of gravity (hereinafter, referred to as the center of gravity of the bright spot) 21G of the figure of the bright spot image formed by a set of these points. Is calculated.

Next, a predetermined area (to be described later) (Xs; Ys) for erasing the luminescent spot with the luminescent spot center of gravity 21G as the center.
Is set. Since the center of the bright spot formed by corneal reflection is not always the brightest, simply defining a predetermined area for the bright spot elimination with the brightest point 21p as the center,
There is a risk that the bright spot image will protrude from this area,
As described above, this fear does not occur when the center of gravity of the bright point 21G is set as the center.

For the left eye, the position 21G 'of the center of gravity of the bright spot is calculated in the same procedure as described above.

The positions 21G and 2 of the luminous point centroids for both eyes
When 1G 'is obtained, the distance between the positions of the centers of gravity of the two bright points, that is, the distance W between the pupils, is obtained.
(See FIG. 17). By obtaining the distance W between the pupils of the two bright points, the distance between the eyes of the subject and the inclination θ of the straight line connecting the two bright points are obtained, so that the subject can be inclined several times with respect to the apparatus. Are detected respectively.

As described above, the bright point centroids have been obtained for both eyes. Hereinafter, the bright points of both eyes are removed based on the positions of the bright point centroids.

The following description is for the right eye.

When the center of gravity of the bright spot is determined, as described above,
As shown in FIG. 18B, a detection area (Xs; Ys) in the vicinity of a bright point centered on the center of gravity of the bright point is set. The amount of light at points a and b intersecting the boundary of the detection area (Xs; Ys) with the scanning line in the X direction parallel to the edge is obtained, and the points a and b are approximated by straight lines. The straight line connecting the points a and b shows the light quantity distribution in the detection area (Xs; Ys) in which the influence of the bright spot on the scanning line in the X direction is removed (FIG. 1).
8 (C). In the light amount distribution indicated by δ in FIG.
The light amount distribution curve obtained by scanning in the direction is shown).

The equation of the approximate straight line between the points a and b is represented by the following equation (12).

[0079]

L = {(Lb−La) / Xs} × X + La

Such scanning is performed over the entire detection area (Xs; Ys), and a correction value for the detection area (Xs; Ys) from which the influence of the bright spot is removed is obtained and stored.

Next, the light amounts at points c and d intersecting the boundary of the detection area (Xs; Ys) with the scanning line in the Y direction perpendicular to the edge are obtained, and the points c and d are approximated by straight lines. .

The approximated straight line is given by equation (12 ').

[0083]

L ′ = {(Ld−Lc) / Ys} × Y + Lc

Such scanning is performed over the entire detection area (Xs; Ys), and similarly in the scanning in the Y direction, a correction value from which the influence of the bright spot is removed is obtained and stored.

Further, the X-direction scanning correction value and the Y-direction scanning correction value are compared one by one with respect to the light amount value of the pixel for the same coordinate, and the larger light amount value in the comparison result is determined as the final value at that coordinate. Remember. The result obtained by such a comparison is the image signal of the detection area (Xs; Ys) from which the bright spot has been removed. The detection area (Xs; Y) of the frame memory 16
s) The stored value of the portion is replaced with a corrected value obtained by the comparison, and the replaced value is stored in the frame memory 16 as a new corrected video. The corrected image from which the bright spots have been removed is displayed on the display 14 together with the image before the correction (see FIG. 19).

Here, the reason for selecting the larger light amount by comparing the X-direction scanning correction value and the Y-direction scanning correction value is a factor as a measurement error in the measurement, such as the influence of eyelashes,
The turbidity of the crystalline lens acts in a direction to reduce the amount of light. Therefore, the reason is that the larger the light amount, the closer to the true value.

Next, the detection area is enlarged to include the pupil sufficiently (X2; Y2) around the center of gravity of the bright point (FIG. 20B), and the detection area (X2; Y2) of the corrected image is changed to X. Scanning is performed in a direction (a direction parallel to the edge) or a Y direction (a direction perpendicular to the edge) to obtain a light amount distribution on the scanned line. The pupil diameter u is obtained from this light amount distribution.

As shown in FIGS. 12A, 12B and 12C, when the iris 20 is removed from the pupil 6 and the iris 20 is removed, the amount of light rapidly decreases (FIG. 18C). Therefore, when the change rate of the light amount distribution γ is obtained, the values protrude at the boundary points m and n between the pupil 6 and the iris portion 20. The pupil diameter u can be obtained by reading the coordinate positions of the boundary points m and n from the frame memory 16 and calculating the coordinates by the arithmetic processing unit 17.

Next, when the eyes are blinked, as shown in FIG. 13 (A), the eyelids hit the pupil 6, and the amount of light in the upper part of the pupil 6 where the eyelids fall is reduced. Therefore, in the light quantity distribution, the boundary position m 'of the eyelid appears to be the boundary position of the pupil 6. Therefore, when the pupil diameter u is calculated in the state of FIG. 13A, the pupil diameter u becomes smaller than the actual value.

FIGS. 12 (B) and 13 (B) show the light amount distribution as viewed from the vertical scanning lines, but the same light amount distribution can be obtained from the horizontal scanning lines. Therefore, the pupil diameter u obtained from the light amount distribution in the horizontal direction is a value that is not affected by blinking. The arithmetic processing unit 17 calculates the pupil diameter uV in the vertical direction and the pupil diameter uH in the horizontal direction, and further calculates the pupil diameter u in the vertical direction.
The ratio (uV / uH) between V and the pupil diameter uH in the horizontal direction is determined, and if this ratio is smaller than a predetermined value (ideally, 1), it is determined that blinking has occurred.

Blinking can also be detected using the luminous point centroids 21G, 21G '. Since the bright point centroids 21G and 21G 'are located at the center of the pupil 6, blinking can be determined by monitoring the distance between the bright point centroid position ρ and the boundary positions m and n of the pupil 6.

In the arithmetic processing unit 17, the line segment ρm and the line segment pn
Is calculated to determine the ratio between the two, and this ratio is monitored.

That is, when there is no blink, the line segment ρm / line segment ρn = 1, and when there is a blink, the line segment ρm ′.
/ Segment ρn <1. Note that blinking can be detected by integrating the light amount distribution curve up to the boundary points m, m ', and n, and comparing the integrated values in the same manner as described above.

In the present apparatus, the eye refractive power is obtained from the gradient of the light amount distribution as described above. However, if it is determined that there is a blink, the data is stored in the frame memory 16 without proceeding to the next step. For the other video signals, the above-described processing is repeatedly performed, and when it is determined that there is no blink, an eye refractive power calculation processing described below is performed.

The detection area (X 2;
Y2) is scanned in the Y direction (a direction perpendicular to the edge), and the light amount distribution on the scanned line is obtained. The number of scanning lines for obtaining the light amount distribution is a plurality of scanning lines that deviate to the scanning line −X side and + X side from the scanning line passing through the luminescent point barycenter (FIG.
(A)).

With respect to the obtained light quantity distribution, the average of the light quantity of each pixel at the same coordinate in the Y direction of each scanning line is calculated, and the average value is replaced and stored as a new light quantity value of the scanning line passing through the center of gravity of the bright spot. (See FIGS. 21B and 21C). FIG. 22 shows the light amount distribution obtained by this replacement. The averaged light amount distribution is displayed on the display 14 together with the images of both eyes (FIG. 19).
reference).

By displaying the averaged light amount distribution, the examiner can visually determine the eye refractive power of the subject's eye. Also, FIG.
Are averaged from the light intensity distribution indicated by the symbol, and corrected to the linear light intensity distribution for measurement shown in FIG. As shown in the figure, the curve near the boundary of the pupil is distorted, which is considered to be because light is scattered by the iris edge. Therefore, in order to correct, a portion near the pupil boundary α is removed to obtain a linear measurement light amount distribution. In order to obtain the light quantity distribution for measurement, for example, the least squares approximation method is used.

The straight line obtained by this approximation method is indicated by Z0 in FIG. 22, and Δf / f0 required for calculating the diopter value can be obtained from this straight line Z0. However, the averaged light amount distribution has a drop like ε due to the influence of eyelashes, turbidity of the crystalline lens, and the like. Therefore, in order to obtain a more accurate measurement light amount distribution, it is necessary to reduce the influence of the depression ε.

As one method, as shown in FIG. 23, a straight line Z0 'having a level lower than the straight line Z0 by ε' is used as a reference, and a value whose level is lower than the straight line Z0 '(see FIG.
3 is not used as data at the time of approximation, and a straight line Z obtained by further approximation is used as a light quantity distribution for measurement.

As another method, as shown in FIG. 24, the range lower than the straight line Z0 (the range indicated by ε '''' in FIG. 24) is replaced with the value of the straight line Z0, and the averaged light amount distribution is obtained. Is corrected, the corrected averaged light amount distribution is approximated by the least squares method, and this operation is repeated to obtain the measurement light amount distribution.

From the light quantity distribution for measurement, Δ
f / f0 is obtained, and the deviation .DELTA. of the diopter value of the eye to be measured can be obtained from Expression 9 and the diopter value D can be obtained from Expression 11.

As described above, the eye refractive power when the fixation target is specified,
The measurement of the pupil diameter and the distance between the pupils has been described.
The measurement of temporal changes in the eye refractive power, the pupil diameter, and the interpupillary distance of the eye to be measured when the distance of the fixation target collimated by the subject is changed will be described.

In this measurement, when the examiner operates the switch by the measurement start switch 19 indicating the start of measurement, the control unit 18 first turns on the first fixation target 35, and then turns on the second fixation target 35. The position is switched to the fixation target 36, and the index position presented to the subject is changed. Further, the control unit 18 controls the light receiving element 9 before and after changing the index position by operating a switch.
The video signal is acquired from the frame memory 16 by the above-described processing, and the data at each predetermined time interval of the first predetermined period and the data at each predetermined time interval of the second predetermined period after the index position is changed by the switch operation are calculated in the frame memory 16. Remember.

In the following, based on the above embodiment, the eye refractive power, interpupillary distance, and pupil diameter of the eye to be measured when the first fixation target 35 is switched from the first fixation target 35 to the second fixation target 36 (from far to near) instantaneously. The measurement of the change with time will be described with reference to FIG.

S1: At the start of measurement, the first fixation target 35
(1st position) is lit, and the person to be measured collimates an index (for example, 2 m) at a distant position. S2: The arithmetic unit 13 receives the light receiving signal received by the light receiving element 9 and stores the measurement target person (measured person) in the frame memory 16.
Are stored as anterior segment image data including both eyes. The anterior segment image data is displayed on a display 14 such as a monitor. S3: A scale for positioning and the like are simultaneously displayed on the display 14, and the displayed anterior ocular segment image is positioned (aligned) with reference to the scale and the like. S4: This alignment operation is repeated until a correct position is reached. When the position is correct, the measurement start signal from the measurement start switch 19 can be accepted. S5: A standby state for a measurement start signal indicating a change in index position is entered, and the measurement start signal is input. S6: The index presented by the control unit 18 is the first fixation target 3
5 (first position) is switched to the second fixation target 36 (second position (for example, 0.4 m)). S7: When the measurement start signal is input, the light receiving signal from the light receiving element 9 is applied to the arithmetic unit 1 at predetermined time intervals for a predetermined time.
3 is fetched, and the fetched data is stored in the frame memory 16.
To memorize. S8: The first index position data and the second index position data stored in the storage unit
Based on the index position data, the eye refractive power, pupil diameter, and interpupillary distance (PD) of both eyes before and after the change of the index position are calculated. S9: The following calculation result is displayed. The eye refractive power of both eyes is calculated using the light amount distribution of the pupil image in the first index position data and the second index position data. First
The pupil diameter of the left and right eyes is calculated from the size of the pupil image in the index position data and the second index position data. The positions of the centers of gravity of the left and right pupil images in the first index position data and the second index position data are obtained, and the interpupillary distance (PD) is calculated from the intervals. The display 14 displays the eye refractive power, pupil diameter, and interpupillary distance (PD) of both eyes before and after the change of the index position calculated by the calculation.

The indices are changed from the first fixation target 35 to the second fixation target 36.
FIG. 26 shows the state of temporal changes of the eye refractive power, the interpupillary distance, and the pupil diameter in the case of instantaneously switching from (far to near).

Also, the eye refractive power when the index is instantaneously switched from the second fixation target 36 to the first fixation target 35 (from near to far),
FIG. 27 shows the state of the pupil distance and the pupil diameter over time.

In any case, the adjustment function of the eye to be measured is started with a delay from the time of switching the index position, and reaches the final eye refractive power after a predetermined time.

As the measurement data, the following two types are obtained depending on the mode of switching the index.

Index switching: far → near Index position change: 2.0 m (far) to 0.4 m (near)
, The interpupillary distance decreases, the pupil diameter decreases, and the eye refractive power changes in the strong direction. Index switching: near to far Index position change: from 0.4m (near) to 2.0m (far)
, The interpupillary distance increases, the pupil diameter decreases, and the eye refractive power changes in a weaker direction.

FIG. 28 shows a second embodiment. In this embodiment, the fixation target system 31 includes a movable fixation target 39 which is movable, and the movable fixation target 39 is not shown. The drive unit moves on the transmission optical axis 37, and the drive unit is controlled by the control unit 18. In this embodiment, it is possible to measure temporal changes in the eye refractive power, interpupillary distance, and pupil diameter of the measurement target eye when the position of the fixation target is continuously changed.

One measuring method according to the second embodiment will be described with reference to FIG.

Measurement start S1: The movable fixation target 39 is presented at the first position and the distant position (for example, 2 m). S2: The arithmetic unit 13 receives the light receiving signal received by the light receiving element 9 and stores it in the frame memory 16 as anterior ocular segment image data including both eyes of the person to be measured (measured person). And
The anterior segment image data is displayed on a display 14 such as a monitor. S3: A scale for positioning and the like are simultaneously displayed on the display 14, and the displayed anterior ocular segment image is positioned (aligned) with reference to the scale and the like. S4: This alignment operation is repeated until the position is correct, and when the position is correct, the process proceeds to S5. S5: The measurement start signal indicating the change of the index position is in a standby state for input. When a measurement start signal is input by operating the measurement start switch 19, the process proceeds to S6. S6: A measurement start signal is input, and the control unit 18 moves the movable fixation target 39 presented from the first position to the second fixation target 36.
(To the second position (for example, 0.4 m)). Proceed to S7. S7: If the index position is moving to the second position, the process proceeds to S8, where the image of the anterior ocular segment is captured and stored. When the movable fixation target 39 changes to the second position, the process proceeds to S9. S9: Here, the data stored during the first predetermined period before the input of the measurement start signal in S2 is stored as the first index position data. S10: The image of the anterior segment after the change of the index position is captured and stored, and the process proceeds to S11. S11: It is determined whether a second predetermined period has elapsed. When the second predetermined period has not elapsed, the process returns to S10,
Until the second predetermined period elapses, an image of the anterior segment is captured and stored. When the second predetermined period has elapsed, the process proceeds to S12. S12: After the measurement start signal is input, the anterior segment image data of both eyes (including the data stored in S8) until the second predetermined period elapses is stored in the frame memory 16 as the second index position data. . S13: Based on the first index position data and the second index position data stored in the frame memory 16, the eye refractive power, the pupil diameter and the interpupillary distance (PD) of both eyes before and after the position change of the movable fixation target 39. Is calculated. The eye refractive power of both eyes is calculated using the light amount distribution of the pupil image in the first index position data and the second index position data. The pupil diameters of the left and right eyes are calculated from the sizes of the pupil images in the first index position data and the second index position data. The positions of the centers of gravity of the left and right pupil images in the first index position data and the second index position data are obtained, and the interpupillary distance (PD) is calculated from the intervals. S14: The display unit 14 displays the eye refractive power, pupil diameter, and interpupillary distance (PD) of both eyes before and after the change of the index position calculated by the calculation.
To display.

The following four types of measurement data are obtained depending on the mode of movement of the index.

Index switching: far → near Index switching: near → far Index moving: far → near Index moving: near → far

FIG. 31 shows how the eye refractive power, the interpupillary distance, and the pupil diameter change with time when the movable fixation target 39 is moved from the first position to the second position.

FIG. 32 shows how the eye refractive power, the interpupillary distance, and the pupil diameter change with time when the movable fixation target 39 is moved from the second position to the first position.

Another measurement method according to the second embodiment will be described with reference to FIG. According to the other method, when the switch operation of the measurer indicating the start of measurement is performed, the image data before the change is captured without changing the index position until the first predetermined period has elapsed. Then, after the first predetermined period has elapsed, the index position presented to the measurer is changed, the image data during the index position change and during the second predetermined period after the index position change is stored, and both before and after the index position change are stored. The eye refractive power, pupil diameter and interpupillary distance of the eye are continuously measured, and the eye refractive power, pupil diameter and interpupillary distance of both eyes before and after the change of the index position are displayed. This will be described below.

Measurement start S1: The movable fixation target 39 is presented at the first position and the distant position (for example, 2 m). S2: The arithmetic unit 13 receives the light receiving signal received by the light receiving element 9 and stores it in the frame memory 16 as anterior ocular segment image data including both eyes of the person to be measured (measured person). And
The anterior segment image data is displayed on a display 14 such as a monitor. S3: A scale for positioning and the like are simultaneously displayed on the display 14, and the displayed anterior ocular segment image is positioned (aligned) with reference to the scale and the like. S4: This alignment operation is repeated until the position is correct, and when the position is correct, the process proceeds to S5. S5: The measurement start signal indicating the change of the index position is in a standby state for input. When a measurement start signal is input by operating the measurement start switch 19, the process proceeds to S6. S6: A measurement start signal is input, and an image of the anterior segment is captured for a first predetermined period before the movable fixation target 39 moves. S8: After a lapse of a predetermined period, the control unit 18 moves the movable fixation target 39 from the first position to the second position (for example, 0.4 m). S9: If the index position is moving to the second position, S10
Then, the image of the anterior segment is captured and stored. If the movable fixation target 39 changes to the second position, the process proceeds to S11. S11: The image of the anterior segment after the index position change is captured and stored, and the process proceeds to S11. S12: It is determined whether the second predetermined period has elapsed. If the second predetermined period has not elapsed, the process returns to S11, and the image of the anterior segment is captured and stored until the second predetermined period has elapsed. After the input of the measurement start signal, the anterior segment image data of both eyes (including the data stored in S10) until the second predetermined period elapses is stored in the frame memory 16 as the second index position data. When the second predetermined period has elapsed, S13
Proceed to. S13: Based on the first index position data and the second index position data stored in the frame memory 16, the eye refractive power, the pupil diameter and the interpupillary distance (PD) of both eyes before and after the position change of the movable fixation target 39. Is calculated. It is desirable that the first predetermined period and the second predetermined period are set as follows. Even if the index position is changed, the factors of the eye refractive power, the pupil diameter, and the distance between the pupils of the eye to be measured do not change instantaneously but change after a certain delay period. In consideration of this, the first predetermined period is set to be long enough to measure the steady state before the change of the index position of the eye to be measured, and the second predetermined period is measured for the delay period, the change period, and the steady state. Need to be long enough.
Generally, the second predetermined period is often set longer than the first predetermined period. For example, the first predetermined period can be set to 0.5 seconds and the second predetermined period can be set to about 1.5 seconds.

[0120]

As described above, according to the present invention, the three elements of the eye refractive power, the pupil diameter, and the distance between the pupils can be simultaneously measured, and the three eyes of the eye to be measured when the position of the fixation target is changed.
It has an excellent effect that a change with time of an element can be measured.

[Brief description of the drawings]

FIG. 1 is a schematic configuration explanatory view showing an embodiment of the present invention.

FIG. 2 is a schematic block diagram showing an embodiment of the present invention.

FIGS. 3A, 3B, and 3C are explanatory diagrams illustrating a difference in a state of a light beam due to a difference in a diopter value of an eye to be measured.

4 (A), (B), (C), (D), and (E) are explanatory diagrams showing states of light beams received and reflected from the fundus of the eye to be measured.

5A is an explanatory diagram showing a state of a reflected light beam at each point of a light source reaching a light receiving element, and FIG. 5B is an explanatory diagram showing a change in light amount of each light beam when the light beam is blocked by a light blocking member.

FIG. 6A is an explanatory diagram showing a state of reflected light beams at respective points of a light source reaching a light receiving element, and FIG. 6B is an explanatory diagram showing a change in light amount of each light beam when the light beams are blocked by a light blocking member.

FIG. 7A is an explanatory diagram showing a state of a reflected light beam at each point of a light source reaching a light receiving element, and FIG. 7B is an explanatory diagram showing a change in light amount of each light beam when the light beam is blocked by a light blocking member.

FIG. 8 is an explanatory diagram showing a light amount distribution state on a light receiving surface corresponding to a diopter value.

FIG. 9 is an explanatory diagram showing a light amount distribution state on a light receiving surface corresponding to a diopter value.

FIG. 10 is an explanatory diagram showing a light amount distribution state on a light receiving surface corresponding to a diopter value.

FIG. 11 is an explanatory diagram when a diopter value is obtained from a light quantity distribution state.

12A is a diagram showing a normal eyeball state, FIG. 12B is a diagram showing a light amount distribution in this state, and FIG. 12C is a diagram showing a previous light amount change rate.

13A is a diagram illustrating a blinking state, FIG. 13B is a diagram illustrating a light amount distribution in this state, and FIG. 13C is a diagram illustrating a previous light amount change rate.

FIG. 14 is a block diagram shown in the first embodiment.

FIG. 15 is a flowchart showing eye refractive power measurement in the first embodiment.

16A is a diagram of an imaging screen of the ophthalmologic measurement apparatus, FIG.
(B) is an enlarged view of an eye portion to be measured, and (C) is a view showing a bright spot image.

FIG. 17 is a diagram illustrating an imaging screen of the ophthalmologic measurement apparatus.

18A is an enlarged view of an eye portion to be measured as in FIG. 16B, FIG. 18B is a view showing a range including a bright point, and FIG. 18C is a view parallel to an edge passing through the bright point. (D) is a light amount distribution diagram of a scanning line in a direction perpendicular to the edge.

FIG. 19 is a diagram of a display screen of the display device.

20A is an enlarged view of a measurement target eye part as in FIG. 16B, FIG. 20B is a view showing a scanning region including a pupil,
(C) is a diagram showing a light amount distribution of a scanning line in a direction perpendicular to the edge.

FIGS. 21A, 21B, and 21C are explanatory diagrams for obtaining an averaged light amount distribution. FIGS.

FIG. 22 is a diagram showing a relationship between a light amount distribution and an approximate straight line.

FIG. 23 is an explanatory diagram showing a method of obtaining an approximate straight line.

FIG. 24 is an explanatory diagram showing a method of obtaining an approximate straight line.

FIG. 25 is a flowchart showing a first measurement method.

FIG. 26 is a diagram showing a change in state such as the eye refractive power of the measurement target eye when the index is instantaneously switched from far to near.

FIG. 27 is a diagram showing a state change of the eye to be measured, such as eye refractive power, when the index is instantaneously switched from near to far.

FIG. 28 is a schematic configuration explanatory view showing a second embodiment of the present invention.

FIG. 29 is a flowchart showing a second measurement method.

FIG. 30 is a flowchart showing a third measurement method.

FIG. 31 is a diagram showing a state change such as an eye refractive power of the eye to be measured when the index is gradually moved from far to near.

FIG. 32 is a diagram illustrating a change in state of the eye to be measured, such as eye refractive power, when the index is gradually moved from near to far.

[Explanation of symbols]

 Reference Signs List 1 irradiation optical system 2 light receiving optical system 3 eye to be measured 4 light source 6 pupil 9 light receiving element 13 arithmetic unit 14 display 15 measuring optical system 16 frame memory 17 arithmetic processing unit 18 control unit 19 measurement start switch 31 fixation target system 35 1 fixation target 36 2nd fixation target

Claims (7)

[Claims] 1. A light source unit that emits an illumination light beam that illuminates the fundus of both eyes of a subject, an illumination optical system that irradiates the illumination light beam from the light source unit to the fundus of both eyes of the subject, and an illumination light beam Irradiates a part of the reflected light flux from the fundus of both eyes of the measurement subject irradiated with the light so that the light quantity distribution changes according to the eye refractive power at a position substantially conjugate with the pupil of the measurement target eye. A light-receiving optical system including a light-shielding unit disposed in the optical path, a light-receiving unit disposed at a position substantially conjugate with the pupil of the eye to be measured, and receiving a light beam received from the light-receiving optical system; A storage unit for storing; an index system for changing an index presenting position from a first index position to a second index position different from the first index position according to an operation of a measurer; Based on the light receiving signal of the light receiving unit obtained before and after the change of the index position, the index position An ophthalmologic measurement apparatus comprising: a calculation unit that obtains data on an interpupillary distance, an eye refractive power, and a pupil diameter of a measurement target eye before and after a change. 2. The method according to claim 1, wherein the index system includes a plurality of indices having different positions, and one of the indices is alternatively presented. The storage unit stores the index before and after the index is switched. The ophthalmologic measuring apparatus according to claim 1, wherein the ophthalmologic measuring apparatus is configured to store a light receiving signal of the light receiving unit. 3. The index system according to an operation of a measurer,
It is configured to present the index to the subject at different positions,
The storage unit stores a light receiving signal of the light receiving unit during a first predetermined period before the time when the index system presents the index to the subject at a different position and during a second predetermined period after the time. The ophthalmologic measurement apparatus according to claim 1, wherein the ophthalmology measurement apparatus is configured as follows. 4. The indicator system according to an operation of a measurer,
The position where the index is presented to the person to be measured is changed after a first predetermined period elapses, and the storage unit receives the light of the light receiving unit during the first predetermined period, the index position change period, and the second predetermined period. The ophthalmologic measuring apparatus according to claim 1, wherein the ophthalmologic measuring apparatus is configured to store the signals. 5. The index system according to an operation of a measurer,
The storage unit is configured to control the presenter to present the indices at different positions, and the storage unit is configured to perform the second operation before the time when the index system presented the indices at different positions to the examinee by the control unit. 2. The ophthalmologic measurement apparatus according to claim 1, wherein the ophthalmologic measurement apparatus is configured to store a light receiving signal of the light receiving unit during one predetermined period, an index change period after that time, and a second predetermined period. 6. The arithmetic unit, based on a light receiving signal of the light receiving unit continuously obtained in a period from a first predetermined period before the change of the index position to a lapse of a second predetermined period after the change,
2. The ophthalmologic measurement apparatus according to claim 1, wherein the ophthalmologic measurement apparatus is configured to obtain data on an interpupillary distance, an eye refractive power, and a pupil diameter of the eye to be measured before and after the index position change. 7. The data of an interpupillary distance, an eye refractive power, a pupil diameter of an eye to be measured before and after the change of the index position obtained by the arithmetic unit, or the index position obtained by the arithmetic unit in addition to these data. The ophthalmologic measurement apparatus according to claim 2, further comprising a display unit configured to display a change in data of an interpupillary distance, an eye refractive power, and a pupil diameter of the measurement target eye during a second predetermined period after the change.