JPH06233741A - Ophthalmologic instrument having automatic fogging device and ophthalmoscopic measuring method - Google Patents

Abstract

PURPOSE:To provide the ophthalmologic device having automatic fogging devices and the ophthalmoscopic measuring method capable of accurately measuring both of the ocular refractive power and cornea shape with good accuracy by measuring the cornea shape without subjecting the eye to be examined to sight adjustment, maintaining the relaxation state of the eye to be examined and shortening the fogging time for measuring the ocular refractive power. CONSTITUTION:The ophthalmologic device having the automatic fogging device has refractive power detecting means 1, 5, 6, 7, 8, 9 for measuring the refractive power of the eye to be examined, the fogging devices 10 to 16 for moving the positions of fixed visual target images in the optical axis direction of the eye, a feedback control means for moving the positions of the fixed visual target images of the fogging devices in the direction for relaxing the sight adjusting power of the eye and a cornea shape measuring means for measuring the cornea shape of the eye 3 to be examined during the fogging operation by the fogging devices.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmologic apparatus and an ophthalmic measurement method for measuring the eye refractive power and corneal shape of an eye to be examined.

[0002]

2. Description of the Related Art In recent years, an ophthalmologic apparatus capable of continuously measuring the refractive power and the corneal shape of an eye to be examined has been developed. A combination of such an eye refractive power measuring device (refractometer) and a corneal shape measuring device (keratometer), in an ophthalmologic device called a so-called auto reflex keratometer, the refractive power is measured with the eye to be examined fixed and relaxed. There is a need to do. Therefore, Japanese Patent Publication 4-31690
As disclosed in the publication, an ophthalmologic apparatus having an automatic fog device for realizing a state where the eye to be inspected is surely relaxed has been proposed.

In the above-mentioned conventional ophthalmologic apparatus having an automatic cloudiness device, at the time of measuring the eye refractive power, the refractive power is measured in a state where the fixation target is in the cloudy state, the eye to be examined is fixed and relaxed, and then the cornea shape is measured. Occasionally, the fixation target is positioned at a position where the eye to be inspected can be clearly seen with reference to the measured eye refractive power, and the corneal shape is measured with the fixation target being focused on the eye.

[0004]

Generally, in an ophthalmologic apparatus having an automatic fog device, in order to avoid erroneous measurement when the fixation and relaxation of the eye to be inspected are insufficient and to improve the accuracy of the measured value, Refractive power and corneal shape are measured multiple times. However, in the above-mentioned conventional ophthalmologic apparatus, since the fixation target is positioned at a position clearly visible to the eye to be inspected during corneal shape measurement, the eye to be inspected is focused.
The eye to be examined is likely to fall into the state of visual acuity adjustment. Therefore, in the next eye refractive power measurement, the influence of the visual acuity adjustment remains and it takes time for the fog operation, which makes it difficult to measure the eye refractive power accurately and surely.

The present invention has been made in view of the above-mentioned problems, and the corneal shape is measured without adjusting the visual acuity of the subject's eye to maintain the relaxed state of the subject's eye to measure the eye refractive power. By reducing the fog time, it is possible to measure both the eye refractive power and the corneal shape accurately and reliably.
An object of the present invention is to provide an ophthalmologic apparatus having an automatic fog device and an ophthalmic measurement method.

[0006]

In order to solve the above-mentioned problems, in the present invention, a refractive power detecting means for measuring the refractive power of the eye to be inspected, and the position of the fixation target image are set to the optical axis of the eye to be inspected. And a feedback control unit for moving the position of the fixation target image of the clouding device in a direction of relaxing the visual acuity adjusting power of the eye to be inspected according to the output of the refractive power detecting unit. An ophthalmologic apparatus having an automatic clouding device, comprising: a corneal shape detecting unit for measuring a corneal shape of an eye to be inspected during a clouding operation by the clouding device.

Further, in the present invention, in an ophthalmologic measuring method for automatically measuring the refractive power and corneal shape of an eye to be inspected, preliminary measurement of the refractive power in a predetermined radial direction of the eye to be inspected,
Based on the preliminary measurement value, a fog operation for sequentially moving the fixation target image in a direction of relaxing the visual acuity of the eye to be inspected is performed, and the visual acuity of the eye to be inspected is relaxed during the fog operation. Provided is a method characterized in that a corneal shape is measured, and a formal measurement of refractive power is performed in a plurality of radial line directions of an eye to be examined, preferably in a total radial line direction.

[0008]

According to the present invention, based on the eye refractive power measurement value in the direction of the predetermined radial line of the eye to be examined, that is, the preliminary measurement value, a fixed fog value is added to this value in the direction toward the far point of the eye to be examined. Preliminary fog operation is performed while sequentially moving the target. Then, the corneal shape of the eye to be inspected is measured at an appropriate timing during the preliminary fog operation period, for example, immediately before the end of the preliminary fog operation period. Next, after the preliminary fog operation is completed, that is, when the preliminary measurement value becomes stable, the formal measurement of the eye refractive power of the eye to be inspected in the radial direction, preferably in the radial direction, is performed. Such measurement cycle is repeated a required number of times.

As described above, according to the present invention, since the corneal shape is measured in the pre-fog state, the visual acuity of the eye to be inspected is not applied during the corneal shape measurement, and the eye to be inspected is fixed and almost relaxed. To be done. Therefore, it is possible to shorten the cloud time without adversely affecting the cloud operation that is continuously performed.

[0010]

Embodiments of the present invention will be described with reference to the accompanying drawings. FIG. 1 is a diagram showing a configuration of an optical system of an ophthalmologic apparatus according to an embodiment of the present invention. The ophthalmologic apparatus of this embodiment includes a refractive power detector, a fog device, and a corneal shape detector. The measurement principle of the refractive power detector is based on the screening method, and the eye refractive power is measured by detecting the speed of movement of the shadow on the pupil. An objective eye refractive power detector using a screening method is disclosed, for example, in JP-A-55-86437.

The illustrated device comprises a light emitting diode 1 which emits infrared light. The image of infrared light emitted from the light emitting diode 1 is formed on the pupil of the eye 3 to be inspected by the action of the condenser lens 2. The light emitting diode 1 and the condenser lens 2 are surrounded by a chopper 4 made of a hollow cylinder. Chopper 4
A plurality of slit-shaped openings S are formed along the circumference. The longitudinal direction of the opening S is perpendicular to the paper surface of the figure.

The chopper 4 is constructed so as to be rotatable about the light emitting diode 1 by a drive system (not shown). The linear luminous flux transmitted through the slit-shaped opening S formed in the chopper 4 is reflected by the half mirror 5
Incident on. The half mirror 5 reflects infrared light from the light emitting diode 1 toward the eye 3 to be inspected and transmits light reflected from the eye 3 to be inspected.

The device shown in the drawing further comprises a measuring radial line rotation system 6 comprising a prism 6a and a mirror 6b. The measurement radial line rotation system 6 is for observing the astigmatic state of the eye 3 to be inspected, and by rotating this around the optical axis AX, the radial direction of the linear light beam incident on the eye 3 to be inspected is changed. Change. The reflected light from the subject's eye 3 is transmitted through the measurement radial line rotation system 6 and the half mirror 5 described above, and then the objective lens 7
Incident on. The image of the pupil plane of the subject's eye 3 that has passed through the objective lens 7 is formed on the light receiving unit 8 via the diaphragm 9. The diaphragm 9 has a rectangular opening whose longitudinal direction is perpendicular to the plane of the drawing,
This aperture is positioned almost on the focus of the objective lens 7.

The light receiving portion 8 includes a substrate 8a, photoelectric conversion elements 8b and 8c for measuring the refractive power, which are fixed on the substrate 8a, and a four-division photoelectric conversion element 8d for detecting a positional deviation. As is clear from the figure, the photoelectric conversion elements 8b and 8c
Are arranged in the scanning direction of the linear light beam on the eye 3 to be inspected. The four-division photoelectric conversion element 8d arranged between the photoelectric conversion elements 8b and 8c is a view of the light receiving unit 8 viewed from the direction of the objective lens 7, and the four photoelectric conversion elements 8d arranged as shown in FIG. It is composed of _{1 to} 8d ₄ . further,
The center O of the _four photoelectric conversion elements 8d _{1 to} 8d ₄ is adapted to coincide with the optical axis A of the objective lens 7.

As described above, the optical system of the refractive power detector is composed of the light emitting diode 1, the condenser lens 2, the chopper 4, the half mirror 5, the measuring radius line rotating system 6, the objective lens 7, the light receiving portion 8 and the diaphragm 9. Has been done.

On the other hand, the optical system of the fog device includes a fixation target 11 and a visible light source 10 for emitting visible light to illuminate the fixation target 11.
It has and. The fixation target 11 and the visible light source 10 are integrally held by a holding member 32, and the holding member 32 is reciprocally moved in the optical axis direction (direction shown by an arrow in the figure) by the action of a pulse motor described later. There is. The image of the fixation target 11 emitted by the visible light source 10 is reflected by a mirror 14 and then enters a lens 15 via a projection lens 12 and a diaphragm 13. The image of the fixation target 11 that has passed through the lens 15 is reflected by the half mirror 16 on the subject's eye 3
And is projected on the retina via the lens of the eye 3 to be inspected. The lens 15 is for positioning the diaphragm 13 at a position optically conjugate with the pupil of the eye 3 to be inspected. In other words, the action of the lens 15 keeps the size of the pupil optically constant even if the eye 3 to be inspected changes,
As a result, the depth of field can be made constant.

If the refractive state of the lens of the eye 3 to be inspected is constant, the position of the fixation target 11 on the retina of the eye 3 to be inspected is only one specific point on the optical axis. is there. That is, the position on the optical axis of the fixation target 11 on which an image is formed on the retina and the refractive power of the lens of the subject's eye 3 have a one-to-one correspondence. As described above, the optical system of the fog device includes the visible light source 10,
Fixation target 11, holding member 32, projection lens 12, diaphragm 1
3, a mirror 14, a lens 15, and a half mirror 16.

Finally, the optical system of the corneal shape detector is provided with a pair of optical axes of the projection optical system forming an angle θ symmetrical to the optical axis AX of the eye 3 to be inspected, and the light sources 37a and 37b are located on this optical axis.
And collimator lenses 38a and 38b are provided. Further, as is clear from FIG. 2 which is a view taken along the line AA of FIG. 1, the optical axis of the eye 3 to be inspected is also similarly included in a plane perpendicular to the paper surface of FIG. An optical axis of a pair of projection optical systems that forms an angle θ symmetrically with is provided, and the light sources 37c and 37d and the collimator lenses 38c and 38d are located on this optical axis.
Is provided. In other words, the four light sources 37a to 37d and the corresponding four collimator lenses 38a to 38d are positioned at equal intervals on the circumference centered on the optical axis AX of the eye 3 to be inspected and perpendicular to the optical axis. (See FIG. 2).

The light beams emitted from the respective light sources 37a to 37d are collimated by the corresponding collimator lenses 38a to 38d and then projected onto the cornea of the eye 3 to be examined.
In this way, each of the light sources 37a to 37d is positioned at the focal position of the corresponding collimator lens 38a to 38d.

The light reflected from the corneal surface of the subject's eye 3 is reflected by the half mirror 16 and transmitted through the half mirror 14.
After being reflected by the mirror 39, the light enters the objective lens 40. A diaphragm 41 is provided at the rear focal position of the objective lens 40. The reflected light passing through the objective lens 40 passes through the diaphragm 41 and then forms an image on the light receiving element 42. At this time, the distances h ₁ and h ₂ between the images respectively generated by the pair of projection optical systems described above correspond to the radius of curvature of the cornea in two orthogonal radial directions (for example, the horizontal direction and the vertical direction). If the cornea of the eye to be inspected is spherical, h ₁ =
h ₂ , but when it is a toric surface, h ₁ ≠ h ₂
Becomes An element such as a CCD can be used as the light receiving element 42, and the image intervals h ₁ and h ₂ , and thus the radius of curvature of the cornea, can be obtained from the signal output from the element such as the CCD according to the coordinates.

FIG. 3 is a diagram showing the configuration of the electrical processing system of the ophthalmologic apparatus according to this embodiment. The signal processing procedure of the apparatus according to the present embodiment will be described with reference to FIG. The photocurrents generated in the four received photoelectric conversion elements 8d _{1 to} 8d ₄ are converted into the corresponding four amplifiers 20d _{1 to} 20d.
_{At 4} it is converted to a low impedance voltage signal. The voltage signals output from the amplifiers 20d _{1 to} 20d ₄ are input to the adder / subtractor 21. The adder / subtractor 21 corresponds to the displacement of the corneal reflected light in the X direction (the direction of the arrow in the figure) from the outputs of the _four photoelectric conversion elements 8d _{1 to} 8d ₄ .
A signal, a Y signal corresponding to the positional deviation of the corneal reflected light in the Y direction (the direction of the arrow in the drawing), and a sum signal Z indicating the intensity of the corneal reflected light are output. The X and Y directions are the measurement optical axis A.
In a plane perpendicular to.

If the outputs of the amplifiers 20d _{1 to} 20d ₄ are v _{1 to} v ₄ , respectively, the X signal is (v ₁ + v ₂ )-
(V ₃ + v ₄ ), and the Y signal is (v ₁ + v ₄ ) − (v
₂ + v ₃ ). The three signals X, Y, and Z output from the adder / subtractor 21 are converted into DC voltages with their chopping frequency components suppressed by the low-pass filters 22a to 22c. Analog divider 23a, 23b
In order to prevent the coordinate signal from changing due to the difference in corneal reflectance, the X signal and the Y signal are each normalized.

In this way, the analog dividers 23a and 2
3b respectively normalized X coordinate signal and Y
The coordinate signal and the summation signal Z are continuously and alternately taken out by the analog switch 24. The extracted signal is A
After being converted into a digital signal in the -D converter 25, it is input to the computer 26. Computer 26
Drives the display circuit 36 to display the digitized X and Y coordinate signals in the AD converter 25.

On the other hand, the refractive power is detected by measuring the phase difference between the signals output from the two photoelectric conversion elements 8b and 8c. That is, since the fundus of the eye 3 to be inspected is scanned by the linear light flux by the rotation of the chopper 4,
When the eye 3 to be inspected is an emmetropic eye, the position of the slit 9 corresponds exactly to the neutralization point. Therefore, the luminous flux emitted from the opening of the slit 9 is uniformly brightened or darkened, so that the phases of the output signals of the two photoelectric conversion elements 8b and 8c become equal.

When the eye 3 to be inspected is not an emmetropic eye, bright and dark stripes corresponding to the refractive error state of each eye are emitted from the opening of the slit 9, and the photoelectric conversion element 8
The phases of the output signals b and 8c differ depending on the refractive error state of the eye to be examined. Thus, the photoelectric conversion elements 8b, 8
The refractive power of the eye to be inspected can be obtained from the phase difference between the output signals of c.

The outputs of the two photoelectric conversion elements 8b and 8c are
After being inputted to the buffers 27b and 27a, respectively, they are shaped into a square wave by the waveform shaping circuits 28b and 28a.
The outputs of the waveform shaping circuits 28b and 28a are converted into the number of pulses corresponding to the phase difference in the phase difference counter 29, and then input to the computer 26. Computer 26
Includes the AD converter 25 and the phase difference counter 2 described above.
Signals are alternately input from 9.

When the X signal and the Y signal each show almost zero level and the sum signal Z is higher than a predetermined level (this becomes an alignment signal), that is, when the eye to be inspected and the apparatus main body are aligned, A predetermined pulse is output as a drive signal to the drive circuit 31 of the stepping motor 30 according to the digital signal output from the phase difference counter 29. Here, the summation signal Z is taken into consideration because the X signal and the Y signal may show almost zero level even if the eye to be inspected and the apparatus body are largely displaced.

The stepping motor 30 is a visible light source 10.
And a member 32 that holds the fixation target 11 together is driven. As described above, the refractive power of the eye 3 to be inspected and the position of the fixation target 11 imaged on the retina have a one-to-one correspondence. In order to relax the eye 3 to be inspected, it is necessary to form the fixation target image slightly ahead of the retina so that the eye 3 to be inspected points to the far point. Therefore, in consideration of this point, a signal corresponding to the refractive power of the eye 3 to be examined (in the present embodiment, the photoelectric conversion element 8b,
The position of the holding member 32, that is, the position of the fixation target 11 is determined according to the signal corresponding to the phase difference of the output signal of 8c) (details will be described later).

After confirming that there is no displacement between the eye 3 to be inspected and the main body of the apparatus and that the eyelashes of the person to be inspected are not in the measurement optical path, the measurer turns on the measurement start switch 33 and turns on the computer 26. Input the measurement start signal. When the measurement start signal is input, the computer 26 activates the automatic fog device (details will be described later). When the fluctuation of the output of the phase difference counter 29 becomes small and the feedback system becomes stable, the computer 26 receives the output signal of the phase difference counter 29 and converts it into a frequency, and the CR of the CRT monitor 35.
Input to the T controller 34. In this way, the CRT monitor 35 displays the refractive power (power) of the subject's eye measured in a substantially relaxed state.

When measuring the shape of the cornea, the output signal from the above-mentioned light receiving element 42 is input to the computer 26. From this signal, the computer 26 calculates the radius of curvature of the cornea in the two radial directions of the eye to be inspected that are orthogonal to each other.
Thus, the measured values of the corneal shape of the eye to be examined are displayed on the printer 35.

FIG. 4 is a diagram for explaining the operation of the apparatus according to the embodiment of the present invention. When the first measurement is performed on the eye 3 to be inspected, since there is no data regarding the refractive power of the eye 3 to be inspected, the eye 3 is fixed at a position that can be sufficiently far away from the eye 3, for example, +5 to +6 diopters. Mark 1
1 is initially placed. At this time, the fixation target 11 appears to be blurred far away to the majority of the eyes 3 to be examined. As described above, the reason why the fixation target 11 is initially arranged at a position that can be sufficiently distant to the eye 3 to be inspected is that the refractive power of the eye is likely to change in the near side, that is, in the adjustment direction, and the fixation target is moved to the near side. This is because if you move it from, the vision adjustment will occur.

Then, the light source for measurement, that is, the light emitting diode 1 is caused to emit light, and it is determined whether or not the eye refractive power can be measured. Specifically, the alignment between the apparatus main body and the eye 3 to be inspected is properly performed by the detected X coordinate signal and Y coordinate signal, and the intensity of the reflection signal from the eye 3 is determined by the level of the total sum signal Z. Make sure it is correct. If preliminary measurement is possible, at that moment (at the timing indicated by a in the figure), the measurement radial line rotation system 6 is fixed to the initial position of the apparatus, and the eye 3 in the radial direction (for example, horizontal direction) of the eye 3 to be inspected is fixed. The refractive power value (preliminary measurement value) is automatically measured.

Based on the preliminary measurement value thus measured, the feedback system of the apparatus is operated to move the fixation target 11 in the direction in which the eye 3 to be inspected points the far point. That is, in the present embodiment, the fixation target 11 is moved to a position (preliminary fog position) corresponding to a value (preliminary fog value) PF that is, for example, 0.75 diopter, which is a distance away from the preliminary measurement value. Let

Further, if the measurement is possible, the preliminary measurement (timings b to g in the present embodiment) is continuously performed automatically, and the preliminary fog operation by the above feedback system is repeated a plurality of times. In this way, since the fixation target 11 is far from the refraction state of the subject's eye by the preliminary cloud value PF, the subject's eye 3
Tries to capture this fixation target 11. That is, the visual acuity adjustment power of the eye 3 to be inspected is relaxed to follow the position change of the fixation target 11. As a result, the eye to be examined gradually relaxes and hardly follows the change in the position of the fixation target 11.
That is, the variation of the preliminary measurement value becomes small and becomes stable (timing g in the figure).

As long as the alignment between the main body of the apparatus and the eye 3 to be inspected is stable, the corneal shape measurement of the present invention can be performed at any timing during the above-mentioned preliminary fog period. Actually, the preliminary measurement value is stable and the alignment is stable, that is, immediately before the end of the preliminary fog operation in which the eye to be inspected is fixed and relaxed (for example, timing g in the figure). Is preferred.

The operator pushes the measurement SW at the moment when it is confirmed that the preliminary measurement values are stable and the alignment is stable (timing h in the figure), and the final fog operation (main cloud fog) for formal measurement is performed. Operation). This cloud operation is
The fixation target is located at a position (main cloud position) corresponding to a value obtained by adding 1.50 diopter as a value (main cloud fog value) MF that is more distant to some extent than the value obtained by adding the preliminary measurement fog value PF. 11 to move. When the preliminary clouding operation is repeated for a sufficient time and the degree of astigmatism of the eye 3 to be inspected is small, the above main clouding operation may be omitted and the formal measurement may be directly performed. However, when sufficient time is not taken for the preliminary cloud operation, or when the degree of astigmatism of the eye 3 to be inspected is large and the position of the fixation target is within the focus range of the eye 3 to be inspected, the visual acuity adjustment of the eye 3 to be inspected is performed. The force is not relaxed enough. For this reason, it is preferable that the subject's eye be more surely relaxed by performing a main clouding operation for moving the fixation target further away.

When the above main cloud fog operation is completed, the measurement radial line rotating system 6 is rotated once to formally measure the eye refractive power in all radial directions. From the measured values obtained, for example, the strongest refractive power,
Weakest refractive power, radial line corresponding to strongest and weakest refractive power, spherical power S, astigmatic power C and astigmatic axis angle A, respectively.
The X data is calculated by a computer. Thus, the first measurement cycle is completed after the preliminary cloud period P1 that extends from the start of the preliminary measurement to the input of the measurement SW, the main cloud period P2 in which the main cloud operation is performed, and the official measurement period P3.
After a while after the first measurement cycle, the second measurement cycle is started.

At the start of the second measurement cycle, there is already data on the degree of astigmatism of the subject's eye 3 which was officially measured in the first measurement cycle. Therefore, unlike the first measurement cycle, the initial position of the fixation target 11 can be determined in consideration of the astigmatism information of the eye 3 to be inspected. Obtain the spherical power S and the astigmatic power C from the previous official measurement values,
A position somewhat closer to the farthest point position of the eye 3 to be inspected, for example, a position corresponding to the equivalent spherical surface value S + C / 2 is obtained. A position obtained by adding a preliminary fog value PF (0.75 diopter in this embodiment) in a direction pointing from this position to the far point of the eye to be inspected is set as an initial position, and the fixation target 11 is moved to this initial position. At this moment, the first preliminary measurement is automatically performed at the moment when preliminary measurement becomes possible (timing indicated by i in the figure).

Next, the change amount ΔDH = DH1-DH0 of the first preliminary measurement value DH1 with respect to the formal measurement value DH0 in the radial direction (for example, the horizontal direction) is calculated, and this change amount ΔDH is calculated from the initial position. The fixation target 11 is moved to a position distant by a predetermined distance, and the second preliminary measurement is performed at the next preliminary measurement timing (j in the figure). A change amount ΔDH = DH2−DH0 of the second preliminary measurement value DH2 is calculated, and the fixation target 11 is moved to a position away from the initial position by a distance corresponding to the change amount ΔDH. After that, this process is repeated to perform the preliminary clouding operation.

Also, depending on the configuration, two radial lines that intersect at right angles,
For example, an apparatus configuration in which the horizontal refractive power and the vertical refractive power are obtained as preliminary measurement values is also conceivable. In this case, if the horizontal component and the vertical component obtained by formal measurement are DH0 and DV0 respectively, and the horizontal component and the vertical component obtained by preliminary measurement are DHn and DVn respectively, the horizontal component in each measurement is obtained. And average values DA0 and DAn of the vertical component are given by the following equation.

DA0 = (DH0 + DV0) / 2 DAn = (DHn + DVn) / 2 Average value DA of both components in formal measurement and preliminary measurement
Using 0 and DAn, the change amount ΔDA of the average value is given by the following equation. ΔDA = DAn−DA0 The calculated change amount ΔDA may be used instead of the above ΔDH.

As described above, in the preliminary measurement according to the present invention, not only the measurement in one radial line direction but also the measurement in a plurality of radial line directions is possible, and the measurement in the predetermined radial line direction unique to the apparatus is possible. I do. As described above, in the above-described preliminary cloud operation, the astigmatism information of the eye to be inspected obtained in the previous formal measurement can be reflected in the cloud operation, so the preliminary cloud period P4
Is significantly shortened and the relaxed state of the eye to be inspected can be reliably realized. Even during the preliminary fog operation, the corneal shape measurement can be performed again in a state where the alignment between the apparatus body and the eye 3 to be inspected is stable.

The main cloud fog operation and the formal measurement operation after the second measurement cycle are basically the same as the operation of the first measurement cycle, and the description thereof will be omitted. Thus, the measurement cycle is repeated the required number of times, and the operation of the apparatus of the present invention is completed.

In the present embodiment, the main cloud fog operation is performed by moving the fixation target to a position corresponding to a value obtained by adding the main cloud fog value MF to the value obtained by adding the preliminary cloud fog value PF to the preliminary measurement value. Is going. This main cloud operation is not essential to the present invention as described above. Therefore, if the subject is an infant or has eye problems and it is difficult to fixate for a long time, the operator omits the main cloud operation and immediately performs formal measurement after completing the preliminary cloud operation. It is also possible to reliably measure the eye refractive power.

[0045]

[Effect] As described above, in the ophthalmologic apparatus and the ophthalmic measurement method having the automatic fog device of the present invention, the cornea shape is measured without adjusting the visual acuity of the eye to be inspected. Is maintained. Therefore, the fog time for measuring the eye refractive power can be shortened, and both the eye refractive power and the corneal shape can be measured accurately and reliably.

According to another aspect of the present invention, since the astigmatism information of the eye to be inspected obtained by the formal measurement can be reflected in the fog operation, the fog operation time is shortened and the eye to be inspected is sufficiently relaxed. The eye refractive power can be measured accurately and reliably in the closed state.

[Brief description of drawings]

FIG. 1 is a diagram showing a configuration of an optical system of an ophthalmologic apparatus according to an embodiment of the present invention.

FIG. 2 is a view on arrow AA of FIG.

FIG. 3 is a diagram showing a configuration of an electric processing system of the ophthalmologic apparatus according to the present embodiment.

FIG. 4 is a diagram illustrating a basic operation of the ophthalmologic apparatus according to the present embodiment.

[Explanation of reference numerals] 1 light emitting diode 2 condenser lens 4 chopper 6 measuring diameter line rotating system 8 light receiving part 8d photoelectric conversion element 10 visible light source 11 fixation target 12 projection lens 37 light source 38 collimator lens 40 objective lens 41 diaphragm 42 light receiving element

Claims (7)

[Claims] 1. A refracting power detecting means for measuring a refracting power of an eye to be inspected, a fog device for moving a position of a fixation target image in an optical axis direction of the eye to be inspected, and an output of the refracting power detecting means. According to the feedback control means for moving the position of the fixation target image of the fog device in the direction of relaxing the visual acuity adjustment force of the eye to be inspected, and measuring the corneal shape of the eye to be inspected during the fog operation by the fog device. An ophthalmologic apparatus having an automatic fog device, comprising: 2. An ophthalmologic measuring method for automatically measuring the refractive power and corneal shape of an eye to be inspected, the refractive power is preliminarily measured in a predetermined radial direction of the eye to be inspected, and the eye to be inspected based on the preliminary measurement value. Performing a fog operation of sequentially moving the fixation target image in a direction of relaxing the visual acuity, measuring the corneal shape of the eye to be inspected while the visual acuity of the eye to be inspected is relaxed during the fog operation,
A method characterized by performing formal measurement of refractive power in a plurality of radial directions of an eye to be inspected. 3. The method according to claim 2, wherein the corneal shape measurement is performed immediately before the end of the fog operation. 4. In an ophthalmologic measuring method for automatically measuring the refractive power and corneal shape of an eye to be inspected, a first preliminary measurement of the refractive power is performed in a predetermined radial direction of the eye to be inspected, and the first preliminary measurement value is obtained. A first fog operation for sequentially moving the fixation target image in a direction in which the visual acuity adjustment force of the eye to be inspected is relaxed.
The corneal shape of the eye to be inspected is measured while the eye's visual acuity is relaxed during the cloud operation, and the first formal measurement of the refractive power is performed in the plural radial directions of the eye to be inspected. The second preliminary measurement of the refractive power is performed in the direction, and based on the astigmatism information of the subject's eye obtained from the formal measurement value and the change amount of the second preliminary measurement value with respect to the formal measurement value in the predetermined radial direction. A second fog operation in which the fixation target is sequentially moved in a direction of relaxing the visual acuity adjustment power of the eye to be inspected is performed, and the corneal shape of the eye to be inspected in a state in which the visual acuity adjustment force of the eye to be inspected is relaxed during the second fog operation. And a second formal measurement of the refractive power of the eye to be inspected in a plurality of radial directions. 5. The spherical power (S) and the astigmatic power (C) of the eye to be examined are obtained from the first official measurement value, and the position corresponding to the spherical power (S) and the sum of the spherical power and the astigmatic power (S + C). ) To the position corresponding to the position corresponding to (a) is moved by a predetermined distance in the direction in which the visual acuity adjusting force of the eye to be inspected is relaxed, and the initial position of the fixation target image is defined as the initial position. 5. The method according to claim 4, wherein the second fog operation is performed by sequentially moving the second preliminary measurement value according to the change amount of the second preliminary measurement value with respect to the official measurement value. 6. The method according to claim 5, wherein the selected position is a position corresponding to an equivalent spherical surface value of the eye to be inspected, which is calculated from the first official measurement value. 7. The formal measurement is performed by further moving the fixation target image by a predetermined distance in a direction in which the visual acuity adjusting force of the eye to be inspected is relaxed. Method.