JPH08103413A - Ophthalmological measuring instrument - Google Patents

Abstract

PURPOSE: To accurately recognize the cornea refracting state of an eye to be inspected by measuring detailed eye refracting power distribution in a pupil. CONSTITUTION: Alignment between the eye E to be inspected and an instrument is performed, and when such alignment is completed, measurement is started by depressing a measuring switch. In such a case, a target 6 puts on, and a luminous flux is projected on the eyeground Ef of the eye E to be inspected, and reflected light from the eyeground Ef is reflected on a polarizing beam splitter 2, and plural reflected images of ring shape are image-formed on an image pickup element 11 via a ring diaphragm 8 and a prism 9. Since the shape and size of the reflected image depends on the refracting state of the eye E to be inspected, an eye refracting power at every position is calculated by analying the reflected image, then, the eye refracting power distribution in the pupil can be found.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmologic measuring device for measuring the refractive power distribution in the pupil of an eye to be examined.

[0002]

2. Description of the Related Art Conventionally, as an off-salmometer or a keratometer, a target is projected on the cornea, and the corneal shape is assumed to be a toric surface from the shape of the reflected image by the cornea, and the strongest main meridian refractive power and the weakest main meridian. Devices for measuring the refractive power, the corneal astigmatic axis, etc. are known. Recently, as a corneal topography or photokeratoscope, a large number of ring-shaped targets are projected on the cornea, and the shape of the corneal reflection image of these targets is analyzed to measure the corneal shape in detail. The device is known.

On the other hand, an autorefractometer, which projects a predetermined target on the fundus of the eye to be inspected and measures the spherical refractive power, astigmatic refractive power, and astigmatic angle of the eye from the fundus reflection image, has become widely known. JP-A-5-310 by the applicant
Japanese Patent Laid-Open No. 75-75 discloses a device for measuring sphericity, astigmatic refractive power, and the like from a plurality of regions at different distances from the center of the pupil of the subject's eye.

Originally, a photokeratoscope projects a large number of ring-shaped visual targets toward the cornea of an eye to be examined, records reflection images of these visual targets by the cornea, and analyzes their shapes. Is used to measure the corneal shape and corneal refractive power distribution, but due to recent advances in computer hardware and software, what was conventionally analyzed from film is converted into a digital image from the video signal from the image sensor. Then, the measurement is performed by image processing by a computer.

Furthermore, with the recent increase in the number of cataracts, intraocular lens insertion surgery, refractive surgery, and other surgery affecting eye refraction, it is necessary to measure the refraction state before and after the surgery in more detail than before. Due to this increase, detailed measurements of the refractive state of the cornea before and after surgery in patients using a photokeratoscope have become popular.

[0006]

However, the conventional photokeratoscope can obtain information only on a part of the refractive elements of the cornea, and is not sufficient to represent the actual refractive state of the patient. That is, there is an autorefractometer for measuring the total refractive power of the human eye, but this is because only the refractive power, astigmatic refractive power, and astigmatic axis angle are displayed based on the prescription of the spectacle lens. There is a drawback that the amount of information is too small to express the state. Especially in refractive surgery, it is possible to correct spherical surfaces and astigmatism for refractive correction, but at present there is no device for measuring detailed eye refractive power, so correction of irregular astigmatism that is possible in principle is possible. There is a problem that it cannot be implemented.

A first object of the present invention is to solve the above-mentioned problems and to provide an ophthalmologic measuring apparatus which obtains a detailed eye refractive power distribution in the pupil to know an accurate refractive state of the eye to be examined. .

A second object of the present invention is to provide an ophthalmologic measuring apparatus which measures the eye refractive power distribution in the pupil and the corneal refractive power distribution by the same apparatus and knows the influence of the cornea on the eye refraction.

A third object of the present invention is to provide an ophthalmologic measuring apparatus for measuring the influence of refraction elements other than the cornea on eye refraction.

[0010]

The ophthalmologic measuring apparatus according to the first aspect of the present invention for achieving the above object is a projection for projecting a light flux from a light source or a light flux from a visual target illuminated by the light source onto a fundus of an eye to be examined. In an ophthalmic measurement device having an optical system and a measurement optical system that receives reflected light from the fundus of the light source or the optotype with a photoelectric element, a plurality of concentric circles having different diameters arranged in the projection or measurement optical system. A circular aperture-shaped light flux is allowed to pass therethrough, and an arithmetic means for calculating the eye refractive power distribution in the pupil from the received light signal of the photoelectric element due to the reflected light from the fundus is provided.

The ophthalmologic measuring apparatus according to the second aspect of the present invention projects the light flux from the light source or the light flux from the first visual target illuminated by the light source onto the fundus of the eye to be inspected to form a plurality of concentric circles having different diameters. To the cornea of the eye to be inspected, and the eye refractive power measuring means for receiving the reflected light from the fundus of the light source or the first optotype with the first photoelectric element through the diaphragm that allows passage of only the circular light flux. Corneal shape measuring means for projecting a plurality of concentric annular second targets having different diameters and forming a reflection image of the second targets by the cornea on a second photoelectric element.
Arithmetic means for calculating the eye refractive power distribution in the pupil due to the received light signal of the first photoelectric element due to the reflected light from the fundus and the corneal refractive power distribution due to the received light signal of the second photoelectric element due to the reflected light from the cornea. It is characterized by having and.

Further, the ophthalmologic measuring apparatus according to the third invention projects a light flux from the light source or a light flux from the first visual target illuminated by the light source onto the fundus of the eye to be inspected to form a plurality of concentric circles having different diameters. To the cornea of the eye to be inspected, and the eye refractive power measuring means for receiving the reflected light from the fundus of the light source or the first optotype with the first photoelectric element through the diaphragm that allows passage of only the circular light flux. Corneal shape measuring means for projecting a plurality of concentric annular second targets having different diameters and forming a reflection image of the second targets by the cornea on a second photoelectric element.
The eye refractive power distribution in the pupil due to the received light signal of the first photoelectric element due to the reflected light from the fundus and the corneal refractive power distribution due to the received light signal of the second photoelectric element due to the reflected light from the cornea are further calculated. The present invention is characterized by including a calculating means for calculating the difference between the two distributions, and a display means for displaying the eye refractive power distribution, the corneal refractive power distribution, and the difference between the two distributions.

[0013]

In the ophthalmologic measuring apparatus of the first invention having the above-mentioned structure, the projection optical system projects the light flux from the visual target onto the fundus of the eye to be examined, and the reflected light from the fundus is received by the photoelectric element by the measuring optical system. . Arranged in the projection or measurement optical system is a diaphragm that passes only a plurality of annular light fluxes of different diameters centered on the pupil of the eye to be examined, and among the reflected light from the fundus, the light flux that passes through this diaphragm is received by the light receiving element. The light is received, and the eye refractive power distribution in the pupil of the eye to be inspected is calculated by the calculating means from this signal.

In the ophthalmologic measuring apparatus according to the second aspect of the present invention, the luminous flux from the visual target is projected onto the fundus by the eye refractive power measuring means, and a plurality of light beams reflected from the fundus are arranged in the projection or measurement optical system. The light flux that has passed through the annular diaphragms of different diameters is
Then, the light is received by the photoelectric element and the eye refractive power distribution in the pupil is calculated. Further, a plurality of annular targets having different diameters are projected onto the cornea by the cornea shape measuring means, the reflected light of the targets from the cornea is received by the second photoelectric element, and the corneal refractive power distribution is calculated from this signal. To do.

Further, in the ophthalmologic measuring apparatus according to the third aspect of the present invention, a target is projected onto the fundus by the eye refractive power measuring means, and among the reflected light from the fundus, a plurality of circles having different diameters are arranged in the projection or measurement optical system. The light flux that has passed through the annular diaphragm is received by the first photoelectric element, the eye refractive power distribution in the pupil is calculated, and displayed on the display means. In addition, the corneal shape measuring means projects an annular target having a plurality of diameters onto the cornea to reflect the reflected light from the cornea to the second position.
The photoelectric element receives light, and the corneal refractive power distribution is calculated from this signal and displayed on the display means. Further, the difference between the eye refractive power distribution and the corneal refractive power distribution is calculated and the difference between the two is displayed on the display means.

[0016]

DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described in detail based on the illustrated embodiments. FIG. 1 shows a configuration diagram of a first embodiment, in which an objective lens 1, a polarization beam splitter 2 for dividing passing light and reflected light into P component and S component, respectively, on an optical path in front of an eye E to be inspected, A diaphragm 3, which restricts the light flux passing through the pupil Ep of the optometry E, projection relay lenses 4, 5, an optotype 6, and a light source 7 which illuminates the optotype 6 from behind are sequentially arranged.
Is arranged at a position optically conjugate with the pupil Ep.

On the optical path in the reflection direction of the polarization beam splitter 2, as shown in FIG. 2, a ring diaphragm 8 having a plurality of concentric annular openings, and an inverted conical shape corresponding to the openings of the ring diaphragm 8. The prism 9 having the inclined surface, the measurement lens 10, and the image sensor 11 are sequentially arranged, and the ring diaphragm 8 is arranged at a position optically conjugate with the pupil Ep.

The projection relay lens 4 and the measuring lens 1
0 is connected to a driving means (not shown), and the optical axis direction is such that the visual target 6 becomes the fundus Ef according to the refractive power of the eye E and the reflection image from the fundus Ef becomes conjugate with the image sensor 11. It is possible to move to.

The alignment between the eye E to be inspected and the apparatus is performed by a sliding mechanism (not shown), and when the alignment is completed, the examiner presses the measurement switch to start the measurement. As a result, the light source 7 is turned on, and the luminous flux emitted from the light source 7 illuminates the target 6. The image of the optotype 6 is imaged at the focal position F of the objective lens 1 through the projection relay lenses 5 and 4, and this light flux passes through the pupil Ep to form the optotype image on the fundus Ef.

The light beam reflected from the fundus Ef passes through the objective lens 1 again from the pupil Ep, and the fundus Ef is considered to be a diffusing surface, so that the polarization component is not preserved and a part of the light beam is reflected by the polarization beam splitter 2. , To the ring diaphragm 8 having a plurality of openings. In the ring diaphragm 8, only the light beams passing through the pupil Ep and passing through the annular portions having different diameters corresponding to the respective apertures of the ring diaphragm 8 reach the prism 9, and the prism 9 causes the apertures of the ring diaphragm 8 to reach each aperture. Each light beam is separated by being deflected by the corresponding conical slope.
An image is formed on the image pickup element 11 by the measuring lens 10, and the reflection image from the fundus Ef is observed as a plurality of annular images, that is, ring images, as shown in FIG.

Further, the shape and size of the ring image are determined by the eye E to be examined.
The refractive power near the center of the pupil Ep can be obtained by measuring the shape of the center ring image, for example. Since the polarization direction of the component of the measurement light specularly reflected by the cornea Ec is preserved,
All of them do not pass through the polarization beam splitter 2 and enter the measurement system.

FIG. 4 shows a block circuit configuration used in this embodiment. The data bus 12 has an MPU 13, a ROM 14, a RAM 15 and an image RAM 1 for controlling all data.
6 is connected, and the output of the image sensor 11 is connected to the image RAM 16 via the A / D converter 17. Further, the data bus 12 has a measurement light source 18, a measurement switch 19,
A drive motor 20 that moves the projection relay lens 4, a drive motor 21 that moves the measurement lens 10, and a VRAM 22 are connected, and the output of the VRAM 22 is connected via a D / A converter 23 to a television monitor 24 such as a CRT display. There is.

When the examiner presses the measurement switch 19, the MPU
13 detects this, and the measurement light source 18 is turned on. At this time, the television signal from the image sensor 11 is A / D converter 17
It is converted into a digital signal by and is stored in the image RAM 16 as digital image information. MPU13 is ROM
According to the program stored in 14, the image RAM 16
The refractive power is calculated by extracting and analyzing the ring image projected on the fundus Ef from the image information of 1.

When the refractive power of the eye E to be inspected is myopia or hyperopia, the drive motors 20 and 21 are driven to move the projection relay lens 4 and the measuring lens 10 in a predetermined direction by a predetermined amount, and on the image pickup device 11. After focusing the eye fundus image, the image is captured again in the image RAM 16 and the refractive power is calculated. The calculation result is converted into a predetermined format and VRAM2
2 is converted into a video signal by the D / A converter 23 and is displayed on the television monitor 24 provided inside the main body. The MPU 13 controls all the data via the data bus 12.

In FIG. 4, all the circuits are displayed as if they are incorporated in the apparatus, but in reality, the measurement light source 18, the measurement switch 19, etc., relating to image capturing, the MPU 13, the RAM 15, and the television monitor. The structure may be separated from the part for exchanging data by a general-purpose computer via communication means such as 24. By adopting such a separated structure, it is possible to add software, update software, etc., and to provide more expandability.

FIG. 5 shows an explanatory view of the method of calculating the refractive power,
The refractive power is calculated by finding the distance between any one point of the ring image and the center of the screen. The intersections of the straight line L with an arbitrary angle θ and the ring images R1, R2, R3 are obtained, and the refractive power is calculated based on the values of the distances D1, D2, D3 from the origin O of each intersection.
When this is obtained for the angle θ from 0 ° to 360 °,
The distribution of refractive power on the pupil Ep can be calculated. However, the sizes of the ring images R1, R2, and R3 are calibrated in advance with a model eye or the like.

FIG. 6 shows the refractive power distribution displayed on the television monitor 24, which is displayed in the form of topography in which portions having the same refractive power have the same color and the same density. This display method is extremely effective for qualitatively understanding a large amount of measurement data. Now, as shown in FIG. 5, the ring image R
If R1, R2 and R3 are elliptical and the refracting power at each meridian is constant, they are expressed as shown in FIG. 6, and the calculation of these refracting power distributions and the calculation of topography are M
PU13 does. Although FIG. 6 shows the change in the refractive power as the change in density, it is also possible to more clearly display the degree of change by using the change in color or the like.

FIG. 7 is a block diagram of the second embodiment, in which a half mirror 30, a projection objective lens 31, and an eye to be inspected which transmits 50% of the light flux and reflects 50% of the light beam on the optical path in front of the eye E to be inspected. A perforated diaphragm 32 having a shape as shown in FIG. 8 arranged at a position conjugate with the pupil Ep of E, a prism 33 having elements corresponding to each aperture of the perforated diaphragm 32, a projection relay lens 34, and a light source 35 are sequentially arranged. Has been done.

Each element of the prism 33 is composed of a flat surface having a predetermined angle so as to deflect the light beam incident on each aperture of the perforated diaphragm 32 in a predetermined direction. The fundus oculi Ef are illuminated in a state of being separated corresponding to each of the 32 openings. Further, in the reflection direction of the half mirror 30, the measurement objective lens 36 and the diaphragm 3 arranged at a conjugate position with the pupil Ep of the eye E to be examined.
7, the measuring lens 38, and the image pickup element 39 are sequentially arranged.

The light beam emitted from the light source 35 is imaged at the focal position of the projection objective lens 31 by the projection relay lens 34. At this time, a plurality of concentric circles are formed by the prism 33 and the aperture stop 32 arranged in the optical path. The fundus Ef of the eye E to be examined is illuminated in a state in which the point light source is arranged. This illumination light flux is reflected by the fundus Ef, each point image serves as a secondary light source and is emitted from the pupil Ep, and 50% of the light flux is reflected by the half mirror 30. Then, this light flux passes through the measurement objective lens 36, is regulated by the diaphragm 37, and is projected onto the image pickup element 39 by the measurement lens 38.

In the case of this embodiment, contrary to the first embodiment,
The plurality of light source images arranged concentrically form the fundus Ef of the eye E to be examined.
The reflected light from the fundus oculi Ef is taken out concentrically from the center of the pupil Ep, reaches the measurement optical system, and is imaged on the image sensor 39 as fundus reflection images of a plurality of light sources. In this case, the projection magnification of the fundus oculi Ef onto the image pickup device 39 is made smaller than that in the first embodiment, so that it is not necessary to provide a movable part such as the projection relay lens 4 in FIG. ing. The light source image projected on the fundus oculi Ef has a shape as shown in FIG. 9, and the shape of the signal from the image pickup element 39 on the television monitor is the same as that in FIG.

FIG. 10 shows a block circuit configuration diagram, in which a connector 41 on the side of the measuring device main body 40 is provided with the image pickup device 39 and the output terminals of the measuring switch 42.
Is a general-purpose personal computer 44 via a cable 43.
Is connected to the connector 46 of the expansion board 45. The expansion board 45 converts the video signal into a digital signal A
It has a / D converter 47 and is connected to an internal storage device of the personal computer 44 via an expansion bus 48.

The video signal of the image pickup device 39 and the switch signal of the measurement switch 42 are transmitted from the connector 41 to the cable 4
Expansion board 4 of personal computer 44 through
5, the video signal is A / D converted by the A / D converter 47.
It is converted and stored as a digital image in the internal storage device of the personal computer 44 via the expansion bus 48.

The method for measuring the refractive power distribution is the same as in the first embodiment, but in this embodiment, since the light source image is discretely formed on the fundus, the angle direction corresponding to the porous diaphragm 32 is changed. I can only get information about. However, if 36 holes are provided on one circle, information at every 10 ° can be obtained, and by supplementing this with the above information, detailed refractive power distribution display can be performed. If this display is performed on the operation display of the personal computer, it is not necessary to prepare a dedicated display device.

FIG. 11 is a block diagram of the third embodiment, in which a photokeratoscope and a refractive power distribution measuring device are combined. In front of the eye E to be examined, a half mirror 50,
Objective lens 51, polarization beam splitter 52, diaphragm 5
3, a projection relay lens 54, a visual target 55, and a light source 56 for illuminating the visual target 55 are sequentially arranged. Further, a mirror 57, a ring diaphragm 58, a prism 59, a measuring lens 60, and an image pickup device 61 are sequentially arranged in the reflecting direction of the polarization beam splitter 52, and these are substantially the same as those in the first embodiment of FIG. An optical system for measuring the refractive power distribution of is constructed.

A ring-shaped lens 62 and a ring-shaped illumination light source 63 are provided between the eye E to be inspected and the half mirror 50.
Is arranged. In the incident direction of the half mirror 50,
The imaging lens 64, a wavelength selection mirror 65 that reflects the emission wavelength of the illumination light source 63 and transmits visible light, a mirror 66, a movable lens 67, a fixation target 68 of a predetermined shape, and this fixation target 68.
A light source 69 for illuminating the light is sequentially arranged, and in the reflection direction of the wavelength selection mirror 65, an imaging lens 70, a diaphragm 71 which is inserted into the optical path when measuring the cornea shape, and an image pickup element 72 are arranged. The measuring optics of the scope are configured.

By inserting the diaphragm 71 in the optical path, the magnification of the ring image projected on the image sensor 72 is always kept constant even if there is a slight error in the working distance between the apparatus and the eye E to be examined. It is like this. Further, the fixation target 68 illuminated by the light source 69 is a target for preventing the subject from diverting his or her line of sight during measurement, and the movable lens 67 allows an arbitrary target corresponding to the refractive state of the subject. It is arranged at an optical position and is controlled so that it can be clearly recognized even by a subject having refractive error. Further, as in the case of a normal autorefractometer, it is also possible to move in a cloudy manner in order to eliminate mechanical myopia.

The light beam emitted from the light source 56 illuminates the visual target 55 and is once focused by the projection relay lens 54 near the focal point of the objective lens 51. Further, this light beam passes through the pupil Ep of the eye E to be examined and the fundus Ef. Image on. The light flux from the fundus Ef passes through the objective lens 51 again, and the polarization beam splitter 5
2, reflected by the mirror 57, deflected by the ring diaphragm 58 and the prism 59, separated, and projected onto the image pickup device 61 by the measurement lens 60.

On the other hand, in the photokeratoscope, the light flux from the light source 63 is projected onto the cornea Ec as illumination light from a plurality of ring-shaped light sources by the ring-shaped lens 62, and this corneal reflection image is the anterior segment of the eye E to be examined. Together with the imaging lens 64,
An image is formed on the image sensor 72 via the 70 and the wavelength selection mirror 65.

The shape of the corneal reflection image of a plurality of ring-shaped targets projected on the cornea Ec was measured, and the partial deformation of the cornea Ec,
By quantifying so-called irregular astigmatism and measuring the corneal refractive power distribution, it is possible to graphically display the total refractive power and the corneal refractive power at the same time as shown in FIG. 6, and the effect of the change in the total refractive power on the cornea. Can be measured.

Further, according to this embodiment, by analyzing the shape and size of the corneal reflection image projected on the image pickup device 72, it becomes possible to measure the corneal shape in detail.
Since the refractive index distribution measuring device is combined, it is necessary to calculate and display the distribution of the change in the refractive power due to the refractive element other than the cornea, from the difference between the refractive power distribution due to the cornea Ec and the total refractive power distribution. You can Therefore, finer correction can be performed during refractive surgery, for example, the effect on the total refractive power of the intraocular lens after insertion can be measured, and detailed treatment can be performed to restore visual acuity after surgery. be able to.

In the electric circuit of this embodiment, the light source for the photokeratoscope controllable in FIG. 4, the actuator for inserting the diaphragm 71 into the optical system when measuring the cornea shape, and the movable lens 67 for the fixation target. A motor or the like for driving the motor can be controlled under the MPU.

[0043]

As described above, in the ophthalmologic measuring apparatus according to the first aspect of the present invention, the eye refracting power in the pupil of the eye to be examined is calculated by providing the plurality of annular diaphragms having different diameters to calculate the eye refracting power. Since the distribution can be measured to know the refraction state of the subject in detail, it is possible to provide data for corrective surgery for irregular astigmatism.

Further, since the ophthalmologic measuring apparatus according to the second aspect of the present invention can measure the corneal refractive power distribution as well as the eye refractive power distribution by the same device, the eye refractive power distribution in the eye corneal of the subject causes The impact can be easily determined.

Furthermore, the ophthalmologic measuring apparatus according to the third aspect of the present invention obtains the difference between the eye refractive power distribution and the corneal refractive power distribution,
It is possible to know the influence on the eye refraction by the refraction elements other than the cornea in the eye refractive power distribution, the refraction state of the eye to be inspected is found in more detail, and the measurement result is qualitatively provided by providing the display means. It is possible to display and instantly grasp the refractive distribution state.

[Brief description of drawings]

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

FIG. 2 is a front view of a ring diaphragm.

FIG. 3 is an explanatory diagram of a reflected image on the image sensor.

FIG. 4 is a block circuit configuration diagram.

FIG. 5 is an explanatory diagram of a measurement principle of a refractive power distribution.

FIG. 6 is an explanatory diagram of a refractive power distribution display on a television monitor.

FIG. 7 is a configuration diagram of a second embodiment.

FIG. 8 is a front view of a multi-hole diaphragm.

FIG. 9 is an explanatory diagram of a reflected image on the image sensor.

FIG. 10 is a block circuit configuration diagram.

FIG. 11 is a configuration diagram of a third embodiment.

[Explanation of symbols]

 2, 52 Polarizing beam splitter 6, 55 Visual target 7, 35, 56, 63, 69 Light source 11, 39, 61, 72 Image sensor 13 MPU 14 ROM 16 Image RAM 22 VRAM 24 Television monitor 44 Personal computer 65 Wavelength division mirror 68 Fixation target

Claims (17)

[Claims] 1. A projection optical system for projecting a light flux from a light source or a light flux from a visual target illuminated by the light source onto a fundus of an eye to be inspected, and a reflected light from the fundus of the light source or the visual target is received by a photoelectric element. In an ophthalmologic measuring device having a measuring optical system to do, a diaphragm for passing only a plurality of concentric annular light fluxes having different diameters arranged in the projection or measuring optical system, and the photoelectric conversion by reflected light from the fundus. An ophthalmologic measuring apparatus comprising: an arithmetic means for calculating an eye refractive power distribution in a pupil from a light reception signal of the element. 2. A first deflector having a plurality of annular apertures having different diameters at a position substantially conjugate with a pupil of an eye to be inspected in the projection or measurement optical system and deflecting light fluxes passing through the apertures at different angles. The ophthalmologic measuring apparatus according to claim 1, wherein the optical deflecting member is provided. 3. A plurality of openings on a plurality of circles having different diameters at positions substantially conjugate with the pupil of the eye to be inspected in the projection or measurement optical system, and light beams passing through the openings have different angles. The ophthalmologic measuring apparatus according to claim 1, further comprising a second light deflecting member that deflects the light. 4. The ophthalmologic measuring apparatus according to claim 1, further comprising display means for displaying the eye refractive power distribution calculated by the calculation means. 5. The ophthalmologic measuring apparatus according to claim 2, wherein the first light deflecting member is a prism formed of a part of a conical shape having different apex angles corresponding to the plurality of annular openings. 6. The ophthalmologic measuring apparatus according to claim 3, wherein the second light deflecting member is a prism in which each element is formed by a plane having a different angle corresponding to each opening. 7. The CRT built in the main body as the display means.
The ophthalmic measurement device according to claim 4, which is a display. 8. The ophthalmologic measuring apparatus according to claim 4, wherein the display means is a display of a personal computer connected to the main body by a cable. 9. A diaphragm for projecting a light flux from a light source or a light flux from a first optotype illuminated by the light source onto a fundus of an eye to be examined and passing only a plurality of concentric annular light fluxes having different diameters. Through the light source or the fundus of the first optotype by the first photoelectric element to receive the refractive power measuring means, and a plurality of concentric circles having different diameters on the cornea of the eye to be examined. Corneal shape measuring means for projecting an annular second optotype to form a reflection image of the second optotype by the cornea on a second photoelectric element, and the first optoelectronic element by reflected light from the fundus of the eye. An ophthalmologic measuring device for calculating an eye refractive power distribution in the pupil based on the received light signal and a corneal refractive power distribution based on the received light signal of the second photoelectric element due to reflected light from the cornea. . 10. A first deflector having a plurality of annular apertures having different diameters at a position substantially conjugate with a pupil of an eye to be inspected in the projection or measurement optical system and deflecting light fluxes passing through the apertures at different angles. The ophthalmic measuring device according to claim 9, wherein the optical deflecting member is provided. 11. The projection or measurement optical system has a plurality of openings on a plurality of circles of different diameters at positions substantially conjugate with the pupil of the eye to be inspected, and the light fluxes passing through the respective openings have different angles. The ophthalmologic measuring apparatus according to claim 9, further comprising a second light deflecting member that deflects the light. 12. The ophthalmic measurement apparatus according to claim 9, further comprising display means for displaying the eye refractive power distribution and the corneal refractive power distribution calculated by the computing means. 13. The ophthalmologic measuring apparatus according to claim 10, wherein the first light deflection member is a prism formed of a conical portion having different apex angles corresponding to the plurality of annular openings. 14. The ophthalmologic measuring apparatus according to claim 11, wherein the second light deflecting member is a prism in which each element is formed by a plane having a different angle corresponding to each of the openings. 15. The CRT built in the main body as the display means.
The ophthalmic measurement device according to claim 12, which is a display. 16. The ophthalmic measurement apparatus according to claim 12, wherein the display means is a display of a personal computer connected to the main body by a cable. 17. A diaphragm for projecting a light flux from a light source or a light flux from a first visual target illuminated by the light source onto a fundus of an eye to be examined, and passing only a plurality of concentric annular light fluxes having different diameters. Through the light source or the fundus of the first optotype by the first photoelectric element to receive the refractive power measuring means, and a plurality of concentric circles having different diameters on the cornea of the eye to be examined. Corneal shape measuring means for projecting an annular second optotype to form a reflection image of the second optotype by the cornea on a second photoelectric element, and the first optoelectronic element by reflected light from the fundus of the eye. Calculating means for calculating an eye refractive power distribution in the pupil by the received light signal and a corneal refractive power distribution by the received light signal of the second photoelectric element by reflected light from the cornea, and further calculating a difference between these distributions; Eye refractive power distribution and corneal refractive power distribution and both of these An ophthalmologic measuring device comprising: a display unit that displays the difference in distribution.