JP2806430B2 - Eye refractive power measuring device - Google Patents

Description

Description: BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an eye refractive power measuring device, and more particularly to an eye refractive power measuring device useful for children to infants.

[Prior Art] Conventionally, as an eye refractive power measuring device, there are a so-called subjective ophthalmoscope for measuring eye refractive power based on a response of a subject, a so-called auto-refractometer for objectively measuring an eye to be examined, and the like. Devices are known.

However, when measuring infants with this kind of device, it is not possible to measure with a subjective ophthalmoscope because of the lack of cooperation of infants, and the position of the eye to be examined must be fixed with a general auto-refractometer. However, in the case of infants, it is difficult to fix the position of the eye to be examined, and the measurement is extremely difficult.

In order to eliminate these drawbacks, the so-called photorefraction method of illuminating the fundus of the subject's eye with strobe light, photographing the state of the luminous flux at the pupil of the subject's eye with a camera, and measuring the eye refractive power of the subject's eye from the result is used. A measurement has been proposed.

In this photorefraction method measurement, it is possible to measure sufficiently even if the optical axis of the eye to be examined is slightly shifted, and it is useful for measuring the eye refractive power of infants who have difficulty fixing the eye to be examined. It is supposed to be.

In such a photorefractive eye refractive power measuring apparatus, an attempt is made to obtain a measurement result in a moment, so that a measurement image must be obtained when the subject is not blinking. .

As a conventional method, the examiner looks at the subject's eyes on the monitor screen, confirms that the eyes are open, performs measurement, and further obtains images and measurement results obtained by the measurement. Had determined whether the examiner was blinking.

[Problems to be Solved by the Invention] However, in the above-described conventional method, measurement is performed once, arithmetic processing is performed, and the result and the measurement image are judged by the examiner, so that the measurement result is effective. If re-measurement is necessary without re-measurement, there is a problem in that re-measurement takes time and the burden on the subject is large.

Furthermore, the examiner must determine whether the measurement result is valid or invalid, and artificial errors are unavoidable, resulting in vague and incorrect accuracy.

The present invention has been made in view of the above circumstances, and provides an eye refractive index measuring device that can instantaneously determine whether or not a subject has blinked at the time of measurement, and can perform accurate determination without human error in the determination of blinking. It is something to offer.

Means for Solving the Problems According to the present invention, a light source image is projected on the fundus of the eye to be examined, and a light beam reflected from the fundus of the eye to be examined is received by a light receiving element arranged at a position substantially conjugate with the pupil of the eye to be examined. An eye-refractive-power measuring apparatus for measuring an eye refractive power of an eye to be inspected by a light beam is characterized in that a blink is detected from a boundary position of a pupil of the eye to be inspected based on a video signal of the light receiving element.

[Operation] The point where the change in the light amount is remarkable on the light amount distribution is the boundary position of the pupil, but when the eyes are blinked, the eyelids appear to have moved this boundary position on the light amount distribution. Therefore, blinking can be detected by monitoring the point where the light amount change is remarkable.

Embodiment An embodiment of the present invention will be described below with reference to the drawings.

The present applicant has proposed a useful eye refractive power measuring device in the above-mentioned Japanese Patent Application No. 63-238505, but this embodiment describes a case where the present invention is applied to the eye refractive power measuring device according to the patent application. I do.

 First, an eye refractive power measuring device according to the earlier application will be described.

In FIG. 1, reference numeral 1 denotes a projection system for projecting a light source image onto the fundus 7 of the eye 3 to be inspected, and 2 denotes a light receiving system for receiving a light beam 10 reflected by the fundus 7. The light receiving system 1 and the light receiving system 2 are arranged to face the subject's eye 3.

The projection system 1 includes a light source 4 and a half mirror 5 for reflecting a light beam 11 from the light source 4 toward the subject's eye 3. The projection system 1 transmits the light beam 11 from the light source 4 onto a fundus 7 through a pupil 6. To form an image of the light source 4 on the
The distance between the light source 4 and the eye 3 is set so that the image of the light source 4 is focused on the fundus 7 when the eye refractive power of the eye 3 is a reference diopter value (reference refractive power).

The light receiving system 2 includes an objective lens 8 and a light receiving element 9, and a light beam 10 from the fundus 7 passes through the half mirror 5 and is guided onto the light receiving element 9.

The light receiving element 9 includes an area CCD, an image pickup tube, or a combination thereof.
The light receiving surface 9a of the light receiving element 9 is arranged at a position conjugate with the pupil 6 of the subject's eye 3 with respect to the objective lens 8.

In the optical path of the light receiving system 2, an edge-shaped light shielding member 12 for shielding one side of the light flux 10 with the optical axis O of the objective lens 8 as a boundary is disposed at a position conjugate with the light source 4 with respect to the half mirror 5.

An arithmetic unit 13 is connected to the light receiving element 9. The arithmetic unit 13 calculates a diopter value from the light receiving state of the light receiving element 9 and the light quantity distribution, and outputs the result to the display 14. .

Next, the measurement of the eye refractive power in the eye refractive power measuring apparatus having the above configuration is performed as follows.

As shown in FIG. 2 (A), when the diopter value of the eye 3 to be examined is a negative diopter value compared to the reference diopter value, the image of the light source 4 is formed in front of the fundus 7, and this light beam causes Considering the light beam 10 reflected at one point on the optical axis among the illuminated fundus 7, the light beam 10 is condensed in front of the light shielding member 12, that is, on the side of the eye 3 to be examined, and is received by the objective lens 8. The upper half (hatched portion) of the light beam projected onto the element 9 is shielded. On the other hand, as shown in FIG. 2 (B), when the diopter value of the subject's eye is the reference diopter value,
Is focused on the light shielding member 12, and the light flux 10 is a light shielding member.
Unobstructed by 12.

As shown in FIG. 2C, when the diopter value of the eye 3 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 as described above. Similarly, the light beam 10 reflected by the fundus 7 is collected behind the light blocking member 12, that is, on the light receiving element 9 side, and the light beam 10 projected on the light receiving element 9 is a portion opposite to that of FIG. The light flux (the upper half in the figure) is shielded.

Thus, the light flux projected on the light receiving surface 9a changes its light quantity distribution state with respect to the reference diopter value depending on the magnitude of the diopter value of the eye to be inspected 3 and the sign thereof, and the diopter value is determined based on this light quantity distribution state.

The light receiving element 9 is for detecting the light amount distribution of the light beam formed on the light receiving surface 9a, and the arithmetic unit 13 is configured to detect the light amount distribution of the light beam formed on the light receiving surface 9a based on the signal from the light receiving element 9. Detects the light amount distribution, determines whether the eye refractive power of the subject's eye is positive or negative with respect to the reference diopter value, calculates the absolute value, outputs the calculation result to the display 14, and the display 14 calculates Display the results.

In the above embodiment, a half mirror is used as a light beam separating means. However, it is a matter of course that various light beam separating means such as a beam splitter and a polarizing prism are used.

3 (A) to 3 (E), a description will be given of a light quantity distribution state of a light beam formed on the light receiving surface 9a.

In order to simplify the explanation in FIGS. 3A to 3E, the optical axis of the light source 4 and the optical axis of the light receiving system are matched, and the light shielding member 12 and the objective lens 8 are matched. I have. For this reason, the light source 4 and the objective lens 8 are shown superimposed at the same position, and the light shielding member 12 is omitted.

Figure 3 (A) ~ (E) is the light receiving surface by all reflected light beam objective lens 8 from the shows the case where the refractive power D of the eye is negative with respect to the reference power D _0, the following description fundus It shall be projected on 9a.

Assuming that the distance between the light source 4 and the pupil 6 of the subject's eye is set to 1 and the refractive power of the subject's eye at which the image of this light source is focused on the fundus is the reference refractive power D ₀ It is.

In the case where the refractive power of the subject's eye in FIG. 3 (A) is D (<D ₀ ), the distance from one point S ₀ on the axis of the slit-like light source 4 having a length L in the direction perpendicular to the optical axis is shown. Indicates the projected light flux,
The image of the point S ₀ is once formed on S ₀ ′,
Projected as a blurred image. Region 7a where D ₀ -D is projected in accordance with increase becomes wider.

FIG. 3B shows the state of the light beam reflected from the light receiving system 2 and the fundus 7 of the eye to be examined.

As shown in FIG. 3 (B), considering the light flux from a point I- _n at the end of the projection area on the fundus 7 of the eye to be examined, an image I- _n 'of this point is considered.
Is imaged at a position 1 'away from the pupil of the eye to be examined, and this light beam is projected via the objective lens 8 onto a light receiving element 9 arranged at a position conjugate with the pupil 6 of the eye to be examined. The relational expression between l 'and the refractive power D of the eye to be examined is as follows.

On the other hand, assuming that the pupil diameter of the subject's eye is u, the spread width Δ of the light flux emitted from one point on the fundus is as shown in FIG. From the equations (1) and (2). Thus, as the difference between the refractive power D of the eye 3 to be examined and the reference 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 irrespective of the refractive power of the eye 3 to be inspected.
Assuming that the diameter of the pupil 6 of the eye to be examined is u and the magnification of the objective lens 8 is β, the region of the diameter of βu on the light receiving element 9 (the refractive power of the eye to be examined) Is unaffected by the light beam.

Further, after the imaging from the light beam is similarly examined eye pupil 6 'image I _n to the position of' l from the I _-n symmetrical point I _n with respect to the optical axis, the same area on the light receiving element 9 projected onto βu. Light source 4
As a point light source, when that there is no light blocking member 12 is, those points I _-n from these fundus _{7, ... I 0, ... I} n, the integral of the light beam from determining the light intensity distribution on the light receiving element 9 It is.

Here, in order to consider the light amount distribution on the light receiving element 9, the light flux incident on 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. In consideration of the above, the light beam incident on this position is limited to the light beam in the range of oblique line A in FIG. 3 (C).
Similarly, considering the light flux incident on the position _Pn symmetrical to the P- _n position with respect to the optical axis, the light flux is limited to the light flux in the range of the hatched line A '. When an edge-shaped light-blocking member 12 that blocks one light beam A ′ of the optical axis is arranged at a distance of 1 from the pupil 6 of the eye to be examined (a position conjugate with the light source 4), P ₋ light beam incident on the position of the _n is not blocked by the light shielding member 12, the light beam toward the upper position from the position of the P _-n is gradually shading, half of the light beam is blocked by the center P ₀ position, P _n In this position, all the light beams are blocked. Therefore, the edge-shaped light shielding member 12
As a result, the light becomes darker on the light receiving element 9 as it goes upward, and the light quantity distribution has a constant slope where the light quantity becomes 0 at the point _Pn .

In FIGS. 3A to 3C described above, only the light flux emitted from one point on the optical axis of the light source 4 is shown. However, one point S _-n at the end of the light source 4 (where the size of the light source is L) Considering the luminous flux from the point (-L / 2 coordinate position), the result is as shown in FIG. 3 (D). Light beam from the point S _-n are projected from I _-n point on the fundus 7 shown in FIG. 3 (D) in the region of I _n points, this I _-n
Point, the reflected light from I _n points, after forming an image of, I _n '' I _n at a distance of 'l from the eye pupil 6 in the same manner as described above, the diameter of βu on the light receiving element 9 Is projected on the area of.
Here, of the luminous flux emitted from the point S- _n at the end of the light source 4,
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. 3 (D).

Further, the S consider the light beam from one point S _n of the point symmetrical with the light source 4 _-n, of which Figure 3 Given the light beams incident on the point P _-n on the light receiving element 9 C of (E) It becomes the light flux in the shaded area. 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. 4 (A) shows the respective light beams incident on the position of P- _n on the light receiving element 9 superimposed on the basis of this concept, and shows the light beams emitted from the position of _Sn on the light source. Of which P _-n
Is incident on the area B (FIG. 3 (D)).
), The light flux also moves upward as the position on the light source goes upward, and at the light source position S ₀ on the axis, it becomes a light flux in the area A (see FIG. 3 (C)), and the light beam C region at the position of S _n (see FIG. 3 (E)). Therefore, the light quantity at the point P- _n on the light receiving element 9 can be considered as the sum of these light fluxes.

Here, a light shielding member is provided at a position of a distance 1 from the pupil 6 of the eye to be examined.
FIG. 4B is a schematic diagram showing the light amount at the point P- _n on the light receiving element 9 when 12 is arranged. FIG. 4 (B) shows how the light beam is blocked by the light blocking member 12 as the position on the light source changes. The horizontal axis in FIG. 4 (B) indicates the coordinate position on the light source, and the vertical axis indicates the light amount.
Considering the luminous flux from each point on the light source, -L /
The light beam from the point 2 (L is the size of the light source) to the point 0 is not blocked by the light blocking member 12, but is gradually blocked after passing the coordinate point 0, and the light flux is all Is to be blocked. Here, FIG. 4 (B) 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 no light is shielded. This corresponds to the light amount value at the point P- _n . This area value T is as follows.

Similarly, other points on the light receiving element will be considered. FIG. 5 (A) shows the light beam incident on the center point P ₀ on the light receiving element in the same manner as FIG. 4 (A), and P out of the light beam from the point S _−n on the light source. _The light flux incident on the point _{0 is} a shaded area of B ₀ , the light flux from the point S ₀ on the light source is the shaded area of A ₀ , and the light flux from the point S _n on the light source is the light flux of the shaded area C _0. is intended, the amount of light incident on the center of the light receiving element 9 will correspond to the area T ₀ of the hatched region of FIG. 5 (B). That is, considering the light flux incident on the center point of the light receiving element from each point of the light source, -Δ /
The luminous flux is not blocked until the position of 2, the luminous flux is gradually blocked after passing -Δ / 2 position, and all the luminous flux is blocked at the position of Δ / 2, and this area value is calculated in the same manner as above. Then, the following values are obtained.

Similarly, FIGS. 6 (A) and 6 (B) show the state of the light beam incident on the point _n on the light receiving element and the light amount value at this point. Figure 6 (A), the shaded region of the light beam incident on the point of the inner P _n of the light beam from the point S _-n on the light source B ', hatched A "in terms of the center S ₀ on the light source The luminous flux from the point P- _n on the area and the light source is shown as a luminous flux in the hatched area C ". In this case, as shown in FIG. 6 (B), considering a light beam incident from each point of the light source to a point P _n of the light receiving element,
From the position of -L / 2 on the light source to the position of -Δ, the light beam is not blocked, and after passing the -Δ position, the light beam is gradually blocked, and all the light beams are blocked at the position of 0, When this area value is calculated, the following value is obtained.

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

In the above description, the description has been made on the assumption that the spread width Δ on the light blocking member 12 when considering the light flux emitted from one point of the fundus is smaller than 1/2 of the size L of the light source. It is.

However, if Δ> L / 2, that is, the reference diopter value D ₀
When the deviation ΔD of the diopter value of the subject's eye with respect to is not less than a predetermined amount, a linear change as shown in FIG. 10 is not shown. This will be described with reference to FIGS. 4 to 6. As described above, when Δ> L / 2, FIG.
FIGS. 5 (B) and 6 (B) are FIGS. 11 and 12, respectively.
As shown in FIG. 13 and FIG. 13, this change in light amount does not show a linear change as shown in FIG.

Next, when the refractive power of the subject's eye shown in FIG. 2 (B) is the reference value, and when the refractive power of the subject's eye shown in FIG. 2 (C) is more positive than the reference value, the same as described above. The light amount distribution on the light receiving element 9 can be considered. In this case, when the refractive power of the eye to be examined is a reference value, as shown in FIG. As shown in FIG. 9, the distribution is reverse to that shown in FIG.

The diopter value (refractive power) is the slope of the light amount distribution described above.
And the direction of the slope represents 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 / f ₀ , From the above equation (4), the spread Δ of the light beam, that is, the amount of blur Δ Therefore, from equation (8) Equation (10) gives the deviation ΔD of the diopter value of the subject's eye with respect to the reference diopter value D ₀ . Are proportional. Therefore, from the light intensity distribution , The deviation Δ of the diopter value of the eye to be examined can be obtained, and the diopter value D can be obtained by the following equation.

D = D ₀ + ΔD (11) As described above, the diopter value of the eye to be inspected can be obtained from the light amount distribution of the light beam reflected from the fundus. Note that the light amount distribution described above is schematically represented, and in practice,
The change in the amount of light corresponding to each part of the eyeball shown in FIG.
14 (B), the light amount distribution shown in FIG. 14 (B) shows the light amount distribution at the reference diopter value), that is, the projection ρ of the light amount at the bright spot 21 due to the reflection of the cornea, or the pupil. 6
There is a drop ρ in the amount of light at the iris 20 part outside the range.

In the present invention, the state of the light quantity distribution is monitored, and when there is a change in the light quantity distribution, it is determined that blinking has occurred.

In addition, the deviation ΔD of the diopter value from the light amount distribution described above.
Is not affected by the bright spot. Since the bright spot affects the measurement result of the eye refractive power, it is preferable to remove the influence of the bright spot during the measurement.

Hereinafter, the removal of the influence of the bright spot will be described.

FIG. 16 is a block diagram schematically showing an embodiment of the present invention. In the figure, 15 is the optical system of the eye refractive power measuring device described above,
9 is a light receiving element, 13 is a computing unit, 14 is a display, 16 is a frame memory for storing the image of the light receiving element 9 and the result of the arithmetic processing unit, 17 is an arithmetic processing unit, 18 is a frame memory 16, and an arithmetic processing unit 17 And a control unit 19 for issuing a synchronization command and a sequence command.

Hereinafter, the embodiment will be described with reference to FIGS. 17 to 26.

First, the examiner observes the subject's eye image displayed on the display unit 14. FIG. 18 (A) shows a screen on the display 14, and reference indicators 22R and 22L indicating a predetermined area are displayed on the display 14.
And the image of the eye to be examined is displayed. At the center of the pupil of the binocular image of the eye to be inspected, a bright spot image formed by the light beam reflected by the cornea of the eye to be examined among the light beams from the light source 4 is formed. The examiner sets the measurement start switch 19 after confirming that the binocular image is included in the indices 22R and 21L, that the approximate alignment adjustment is completed, and that the subject is aiming straight. Turn ON. By turning ON this measurement start switch 19,
The video signal from the light receiving element 9 is taken into the frame memory 16 and stored. A plurality of video signals are automatically stored in the frame memory 16 at predetermined time intervals by one operation of the measurement start switch 19.

The time interval for capturing the plurality of video signals is set in advance to a time slightly longer than the time (0.2 seconds) at which a normal person blinks. As a result, even if the first image signal has blinking as described later, the image after blinking is stored in the next captured image signal. It can measure the refractive power, and has the advantage of not having to perform re-measurement after photographing.

If a plurality of images are stored, the measurement can be performed from each of the plurality of image signals. By averaging the measurement results, more accurate measurement can be performed.

The arithmetic processing unit 17 performs arithmetic processing based on the video stored in the frame memory 16 in the following steps.

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

In the image stored in the frame memory 16, both eyes correspond to a predetermined area (corresponding to the above-mentioned areas of the indexes 22R and 22L).
For example, the right eye is imaged so as to be included in (X ₁ ; Y ₁ ). FIG. 18 (B) is an enlarged view of this area.

In the range of the (X ₁ ; Y ₁ ) area of the frame memory 16, each pixel of the light receiving element 9 compares the light amounts to determine a point 21 p having the highest light amount value. This point 21p is a point having the brightest light amount in the bright spot image. FIG. 18C is an enlarged view of the area around the bright spot. Next, a predetermined area (J _X ; J _Y ) is set around the brightest point 21p. 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) of the figure of the bright spot image formed by the set of these points is obtained. Calculate 21G.

Next, a predetermined area (to be described later) (X _S : Y _S ) for erasing a luminescent spot is set around the luminescent spot centroid position 21G. 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 around the brightest point 21p will cause the bright spot image to protrude from this area. Although there is a possibility, there is no such a possibility when the center of the luminescent spot is 21G as described above.

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.

When the positions 21G and 21G 'of the luminous point centroids for both eyes are obtained, the distance W between the luminous point centroid positions and the inclination θ of the straight line connecting the luminous points are obtained (see FIG. 19). By calculating the distance W between the two bright spots, the distance between the eyes of the subject, that is, the pupil distance can be detected. By calculating the inclination, it is detected how many times the subject is inclined with respect to the apparatus. This inclination amount can be used as a correction angle when measuring the astigmatic axis.

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.

In the following, the right eye will be described. In the steps described below, the same calculation process is performed not only for the right eye but also for the left eye.

When the center of luminous point is determined, as described above, FIG. 20 (B)
A detection area (X _S ; Y _S ) near the bright spot centered on the bright spot centroid is set as shown in FIG. A point a that intersects the boundary of the detection area (X _S ; Y _S ) with a scanning line in the X direction parallel to the edge;
The light quantity at the point b is obtained, and the points a and b are near each other by a straight line.
A straight line connecting the points a and b is the detection area ( _XS ;
Y _S ) shows the amount of light in which the influence of the bright spot on the scanning line in the X direction at Y _S is removed (see FIG. 20 (C), where δ in FIG. 20).
The light intensity distribution indicated by the numeral indicates a light intensity distribution curve obtained by scanning the pupil portion in the X direction).

Thus to a point, wherein the approximate straight line between point b L = a _{{(L b -L a) /} X S} × X + L a ... (12).

It carried over; (Y _S X _S) throughout the detection area of such scanning area; for (X _S Y _S) obtains the correction value obtained by removing the influence of the bright spot is stored.

Next, the light amounts at points c and d intersecting the boundary of the detection area (X _S ; Y _S ) 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, L '= {(L d} -L c) / Y S} × Y + L c ... (12' becomes).

Such scanning is performed over the entire detection area (X _S ; Y _S ), 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 stored as the final value at that coordinate. The result obtained by such a comparison is the image signal of the detection area (X _S ; Y _S ) from which the bright spot has been removed. The stored value of the detection area (X _S ; Y _S ) portion of the frame memory 16 is replaced with a corrected value obtained by the comparison, and the replaced value is replaced with a new corrected image as a new corrected image.
To memorize.

The corrected image from which the bright spots have been removed is displayed on the display 14 together with the image before the correction.

Here, the comparison of the X-direction scanning correction value and the Y-direction correction value selected the larger light amount because of factors as measurement errors in the measurement, such as the effects of eyelashes and turbidity of the crystalline lens. Acts in the direction of reducing 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 (X ₂ ; Y ₂ ) around the center of gravity of the bright point (FIG. 22 (B)), and the corrected image is detected in the detection area (X ₂ ; Y ₂ ). In the X direction (direction parallel to the edge) or the Y direction (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. 14 (A), (B) and (C), when the iris portion is deviated from the pupil portion, the light amount sharply decreases (FIG. 20 (C)). 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 these boundary points m and n from the frame memory and calculating them by the processing unit 17.

In the present embodiment, the light from the light source is projected with a sufficiently wide light without restricting the light, and the light is restricted by the pupil of the eye to be inspected. If a stop smaller than the diameter of a normal human pupil is arranged at a position conjugate to the pupil and the light beam is always restricted by this stop diameter, it is not necessary to detect the pupil diameter of the eye to be examined. In the above description, the light amount distribution on one scanning line is detected in order to detect the pupil diameter. However, if the light amount distribution is detected over the entire area of the pupil, it is possible to detect the turbidity of a transparent body such as a crystalline lens. It is possible to know a disease such as a cataract and a site thereof.

Next, when blinking, as shown in FIG. 15 (A), the eyelid hits the pupil 6, and the amount of light in the upper part of the pupil 6 where the eyelid touches decreases. Therefore, in the light quantity distribution, the boundary position m 'of the eyelid appears to be the boundary position of the pupil 6. Therefore, if the pupil diameter u is calculated in the state of FIG. 15 (A), it becomes smaller than the actual value.

FIGS. 14 (B) and 15 (B) show the light amount distribution as viewed in the vertical scanning line, but a similar light amount distribution can be obtained in the horizontal scanning line. 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 u _V in the vertical direction and the pupil diameter u _H in the horizontal direction, and further calculates the ratio (u _V / u _H ) between the pupil diameter u _V in the vertical direction and the pupil diameter u _{H in the} horizontal direction. If the 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 and 21G '. The luminous point centroids 21G and 21G 'are pupils 6
Can be determined by monitoring the distance between the center of gravity ρ of the bright spot and the boundary positions m and n of the pupil 6.

The arithmetic processing unit 17 calculates ▲ and ▼ to determine the ratio between the two, and monitors this ratio. That is, when there is no blink, ▼ /／ = 1, and when there is a blink, ▲ / ▲ <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 this apparatus, the eye refractive power is obtained from the inclination of the light amount distribution as described above. However, if it is determined that there is a blink, other images captured in the frame memory 16 do not proceed to the next step. The above-described processing is repeatedly performed on the signal, and when it is determined that there is no blink, the following calculation processing of the eye refractive power is performed.

The detection area (X ₂ ; Y ₂ ) is scanned in the Y direction (direction perpendicular to the edge) with respect to the corrected image, and a light amount distribution on the scanned line is obtained.

The scanning lines for obtaining the light amount distribution are a plurality of scanning lines that are shifted from the scanning line passing through the center of gravity of the bright spot to the scanning line −X side and + X side (FIG. 23A).

With respect to the obtained light amount distribution, the average of the light amounts of the respective pixels at the same coordinates in the Y direction of each scanning line is calculated, and the average value is replaced and stored as a new light amount value of the scanning line passing through the center of gravity of the bright spot (No.
See Figures 23 (B) and (C). FIG. 24 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 (see FIG. 21).

By displaying the averaged light amount distribution, the examiner can visually determine the eye refractive power of the eye to be examined. Further, the light amount distribution is averaged from the light amount distribution shown in FIG. 21 and corrected to a linear measurement light amount distribution 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. On the other hand, there is a phenomenon that when a subject undergoes mydriasis with eye drops, the light amount level increases near the boundary of the pupil. Therefore, for correction, a portion near the pupil boundary α is removed to obtain a linear measurement light amount distribution. For obtaining the light quantity distribution for measurement, for example, the least squares approximation method is used.

Straight line obtained by the approximation method is shows in FIG. 24 in Z _0, required diopter value calculated by the straight line Z ₀ Delta] f /
f ₀ can be obtained. 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. 25, the straight line Z ₀
On the other hand, a straight line Z ₀ ′ whose level is lower by ε ′ is used as a reference, and values lower than the straight line Z ₀ ′ (in the range indicated by ε ″ in FIG. 250) are not used as data for approximation. Then, the straight line Z obtained by further approximation is used as the light quantity distribution for measurement.

As another method, as shown in FIG. 26, the range lower than the straight line Z ₀ (the range indicated by ε in FIG. 26) is replaced with the value of the straight line Z ₀ to correct the averaged light amount distribution. And
The corrected averaged light amount distribution is approximated by the least squares method, and this scanning is repeated to obtain a measurement light amount distribution.

The Δf / f ₀ is obtained from the light quantity distribution for measurement, and the diopter value D of the eye to be inspected can be obtained from the equations (10) and (11).

The calculation of the diopter value is performed for each of a plurality of video memories, and the calculated values are averaged to improve the accuracy.

Although the diopter value for the right eye is obtained by the above-described operation, the same operation is performed for the left eye to obtain the diopter value.

[Effects of the Invention] As described above, according to the present invention, it is possible to instantaneously determine whether or not a measurement result is blinking, and it is not necessary for the examiner to make a determination on blinking. Becomes

[Brief description of the drawings]

FIG. 1 is a basic schematic diagram of an eye refractive power measuring device in which the present invention is implemented, and FIGS. 2 (A), (B), and (C) are explanatory diagrams showing a difference in a state of a light beam due to a difference in diopter value of an eye to be examined. , Third
(A), (B), (C), (D), and (E) are explanatory diagrams showing states of light reception and a light beam reflected from the fundus of the subject's eye.
FIGS. 5 (A) and 6 (A) are explanatory diagrams showing the state of reflected light flux at each point of the light source reaching the light receiving element, and FIGS. 4 (B), 5 (B) and 6 ( FIG. 7B is an explanatory view showing a change in the amount of light of each light beam when the light beam is blocked by the light blocking member.
FIG. 9, FIG. 9 is an explanatory diagram showing a light amount distribution state on the light receiving surface corresponding to the diopter value, FIG. 10 is an explanatory diagram for obtaining a diopter value from the light amount distribution state, FIG. 11, FIG.
FIG. 13 is an explanatory diagram showing a change in the amount of light of each light beam when the light is shielded by the light shielding member when the spread width Δ on the light shielding member is larger than half the size of the light source, and FIG. FIG. 14 (B) is a diagram showing an eyeball state, FIG. 14 (B) is a diagram showing a light amount distribution in this state, FIG. 14 (C) is a diagram showing the previous light amount change rate,
FIG. 15 (A) is a diagram showing a blinking state, FIG. 15 (B) is a diagram showing a light amount distribution in this state, FIG. 15 (C) is a diagram showing a previous light amount change rate, and FIG. Is a block diagram showing an embodiment of the present invention, FIG. 17 is a flowchart in the embodiment,
FIG. 18 (A) is a diagram of an imaging screen of the eye refractive power measuring device,
FIG. 18 (B) is an enlarged view of the subject's eye, and FIG. 18 (C).
FIG. 19 is a diagram showing a bright spot image, FIG. 19 is a diagram showing the relationship between the measuring apparatus and both eyes, FIG. 20 (A) is an enlarged view of the eye to be examined as in FIG. 18 (B), and FIG. B) is a diagram showing a range including a bright spot, and FIG.
FIG. 20 (C) is a light intensity distribution diagram of a scanning line parallel to an edge passing through a bright point, FIG. 20 (D) is a light intensity distribution diagram of a scanning line in a direction perpendicular to the edge, and FIG. 21 is a display. FIG. 22 (A) is an enlarged view of an eye portion to be examined as in FIG. 18 (B), FIG. 22 (B) is a view showing a scanning region including a pupil, and FIG.
FIG. 22 (C) is a diagram showing a light amount distribution of a scanning line in a direction perpendicular to the edge, FIGS. 23 (A), (B) and (C) are explanatory diagrams for obtaining an averaged light amount distribution, and FIG. Is a diagram showing the relationship between the light quantity distribution and the approximate value straight line, and FIGS. 25 and 26 are explanatory diagrams each showing how to obtain the approximate straight line. 1 is a projection system, 2 is a light receiving system, 3 is an eye to be inspected, 4 is a light source, 5 is a half mirror, 8 is an objective lens, 9 is a light receiving element, 13 is a calculator, 14 is a display, 16 is a frame memory, 17 Denotes an arithmetic processing unit, and 18 denotes a control unit.

Continuation of front page (72) Inventor Noriyuki Nagai 75-1 Hasunuma-cho, Itabashi-ku, Tokyo Inside Topcon Corporation (56) References JP-A-62-236530 (JP, A) JP-A-60-92732 (JP, A) JP-A-59-186539 (JP, A) JP-A-59-28946 (JP, A) JP-A-58-75528 (JP, A) JP-A-57-175346 (JP, A) JP-A Sho-56 -156136 (JP, A) JP-A-52-11694 (JP, A) (58) Fields investigated (Int. Cl. ⁶ , DB name) A61B 3/00-3/18

Claims (4)

(57) [Claims] An image of a light source is projected onto the fundus of an eye to be inspected, and a light beam reflected from the fundus of the eye to be inspected is received by a light receiving element arranged at a position substantially conjugate with a pupil of the eye to be inspected. An eye-refractive-power measuring apparatus configured to detect a blink from a boundary position of a pupil of a subject's eye based on a video signal of the light receiving element. 2. A light quantity distribution on a line passing through a bright point formed by a corneal reflected light flux is determined, and a boundary position is detected from two points where the light quantity change is remarkable in the light quantity distribution. 2. The eye refractive power measurement device according to claim 1, wherein the eye refractive power measurement device is configured to detect. 3. A light quantity distribution on a horizontal line passing through a bright point is determined, and a distance between the two points is calculated, and a distance between the two points is calculated. 2. The eye refractive power measurement according to claim 1, wherein a point is obtained, a distance between the two points is calculated, and a blink is detected by comparing the distance between the two points in the horizontal direction and the distance between the two points in the vertical direction. apparatus. 4. A method according to claim 1, wherein two points of remarkable change in light amount are obtained from a light amount distribution on a vertical line passing through the bright point, a distance between the bright point and the two points is calculated, and the calculated two distances are compared. 2. The eye refractive power measuring device according to claim 1, wherein the eye refractive power measuring device is configured to detect the following.