JPH07136115A - Ophthalmologic measuring apparatus - Google Patents

Abstract

PURPOSE:To provide an ophthalmologic measuring apparatus which enables the obtaining of an interference signal with a better contrast without being affected by polarization characteristic and double refracting property of an eye ball. CONSTITUTION:A cornea distance measuring system 100 is provided to measure a cornea top position 120P by utilizing a geometric optics theory and an interference optical system 101 to measure the position of the eyeground 152 by utilizing a physical optics theory. The interference optical system 101 is provided with a beam splitter 135 and a luminous flux which is emitted from a measuring light source part is divided into a measuring light via the inside of an eye to be inspected and a control light via a mobile control mirror 176 to form a measuring light path 171 and a control light path 174 while the measuring light path 171 and the control optical path 174 are combined to form an interference light path 173. The interference light path 173 is provided with a photo detector 142 to receive an interference light of the measuring light reflected on the eyeground 152 and the control light reflected with the mobile control mirror 176. The measuring light path 171 is provided with a circular polarizer 191 and the control optical path 174 with a phase shifting element 192.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a corneal distance measuring system for measuring the position of a corneal apex using the geometrical optics principle, and for measuring the position of an intraocular measurement object using the physical optics principle. The present invention relates to an ophthalmic measurement device that includes an interference optical system and that measures the position of an intraocular measurement target.

[0002]

2. Description of the Related Art Conventionally, an ophthalmic measuring device has a corneal distance measuring system for measuring the position of the apex of the cornea by utilizing the geometrical optics principle and an intraocular measurement object utilizing the physical optics principle. It is known that an interferometric optical system for measuring the position is provided, and the length from the intraocular measurement object to the corneal vertex position is measured.

In this type of ophthalmic measuring apparatus, an intraocular measurement obtained by irradiating an intraocular measurement object with a measuring light beam in order to measure the position of the intraocular measurement object by utilizing an interference optical system. An interference signal is obtained by observing the reflected light flux from the object.

[0004]

By the way, when the eyeball (intraocular measurement object) of the eye to be inspected does not have abnormal refraction and polarization characteristics, the measurement light reflected by the intraocular measurement object and the eye to be examined correspond to each other. By directly interfering with the reference light reflected by the reference surface, it is possible to obtain an interference signal with good contrast.

However, the eyeball of the eye to be examined has birefringence. In this case, even if linearly polarized measurement light is used, the measurement light reflected by the intraocular measurement target becomes two polarized light beams of an ordinary ray and an extraordinary ray, and therefore, between these two polarized light beams. A phase difference occurs. Further, when the intraocular measurement object is the fundus, because of the optic nerve fibers, blood vessels, etc. existing in the retina, the crystalline lens and cornea existing in the middle are also fibrous or membranous, so the reflected light flux from the fundus is polarized. It becomes a luminous flux.

The presence of this type of polarization makes it possible to measure the polarization direction of the measurement light reflected by the intraocular measurement object and the polarization direction of the measurement light incident on the intraocular measurement object, especially when the measurement target is intraocular. When the amount of light reflected from the object is small, when the measurement light reflected by the intraocular measurement target and the reference light reflected by the reference surface corresponding to the eye to be examined are interfered, the contrast of the interference signal obtained from the light receiving element is As a result, the size of the living eye is not accurately measured. When the eye to be inspected has a disease such as a cataract eye, such a decrease in the contrast of the interference signal particularly occurs.

The applicant of the present invention previously filed Japanese Patent Application No. 4-81981.
No. (Title of invention; Eye length measuring device; April 3, 1992)
In, in consideration of the existence of birefringence in the eyeball of the eye to be examined, we have proposed an attempt to install a Babinet compensator in the optical path of the interference optical system, but it is possible to compensate even when the eyeball has polarization characteristics. Was not.

The present invention has been made in consideration of the above circumstances, and provides an ophthalmic measuring apparatus capable of obtaining an interference signal having a good contrast without being affected by the polarization characteristics and birefringence of the eyeball. The purpose is to

[0009]

Claim 1 according to the present invention
In order to solve the above problems, the ophthalmic measurement device described in (1), a measurement light source unit that emits a light beam for measurement, a light beam emitted from the measurement light source unit, and a measurement light that passes through the inside of the eye to be measured. An interference optical system including a beam splitter that divides the light into a measurement light path and a reference light path by splitting the light into a reference light that passes through a reference surface corresponding to the optometry, and that combines the measurement light path and the reference light path to form an interference light path. In the ophthalmic measurement device having a light receiving element for receiving the interference light by the measurement light reflected by the measurement object in the eye to be examined and the reference light reflected by the reference surface corresponding to the eye, the measurement light source unit Is a linearly polarized light beam, and a circular polarizer provided in the measurement optical path for making the circularly polarized light beam incident on the eye to be inspected, and a shifter provided in the reference optical path so that the polarization direction can be changed. To have And wherein the door.

In order to solve the above-mentioned problems, an ophthalmic measuring device according to a second aspect of the present invention uses a geometrical optical principle to measure a corneal apex position, and a corneal distance measuring system.
An interference optical system for measuring the position of the intraocular measurement target by using the physical optics principle is provided, and the interference optical system transmits the light beam emitted from the measurement light source unit to the measurement light passing through the inside of the subject's eye. A beam splitter is provided which divides the measurement light path and the reference light path by splitting into a reference light passing through the reference surface corresponding to the optometry and combines the measurement light path and the reference light path to form an interference light path. The light receiving element for receiving the interference light by the measurement light reflected by the intraocular measurement object and the reference light reflected by the reference surface corresponding to the eye is provided,
In an ophthalmic measurement device for measuring the length from the intraocular measurement object to the corneal vertex position, the light flux emitted from the measurement light source unit is linearly polarized light, and a circular polarizer is provided in the measurement optical path, and the reference is made above. A retarder is provided in the optical path.

[0011]

According to the present invention, the measuring light source section emits a linearly polarized light beam. A beam splitter installed in the interference optical system splits the light beam into measurement light passing through the inside of the subject's eye and reference light passing through the reference reflecting surface corresponding to the subject's eye. The measurement light is guided to the intraocular measurement object through the circular polarizer, the reference light is guided to the eye-equivalent reference surface through the retarder, and the measurement light reflected by the intraocular measurement object and the eye The reference light reflected by the corresponding reference surface is again combined by the beam splitter to become interference light. The light receiving element receives the interference light.

[0012]

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

In FIG. 1, 100 is a corneal distance measuring system,
Reference numeral 101 is an interference optical system, 102 is a ring-shaped light source projection unit that irradiates a cornea with a ring-shaped light beam, 103 is an eye to be inspected,
Reference numeral 104 is an objective lens.

The corneal distance measuring system 100 includes a first optical path 10
5, and has a second optical path 106. The first optical path 105 is roughly composed of a two-dimensional image sensor 107, an imaging lens 108, a half mirror 109, a diaphragm 110, a lens 111, a total reflection mirror 112, a lens 113, a half mirror 114, a dichroic mirror 115, and an objective lens 104. There is. The second optical path 106 includes a total reflection mirror 116,
Lens 117, total reflection mirrors 118 and 119, diaphragm 12
It is roughly composed of four.

The ring-shaped light source projection unit 102 comprises a ring-shaped light source and a pattern plate (not shown).
Illumination light having parallel meridional rays is projected onto the eye 103. When this illumination light is applied to the subject's eye 103, a ring-shaped virtual image 121 is formed on the cornea 120 of the subject's eye 103. Here, the wavelength of the illumination light of the ring-shaped light source projection unit 102 is 900 nm to 1000 nm.
nm. The dichroic mirror 115 plays a role of transmitting the illumination light and reflecting a light flux of a predetermined wavelength emitted from a measurement light source unit described later.

The light reflected by the cornea 120 is reflected by the objective lens 1.
04, it is guided to the half mirror 114 via the dichroic mirror 115, and is branched into the 1st optical path 105 and the 2nd optical path 106. The reflected light guided to the first optical path 105 is once formed as a ring-shaped aerial image 122 by the lens 113, and further, the total reflection mirror 112 and the lens 11 are formed.
1, diaphragm 110, half mirror 109, imaging lens 10
The image is formed as a ring image i ₂ (see FIG. 2) on the two-dimensional image sensor 107 via 8. The image forming magnification of the ring image i ₂ is 0.5 times here. The reflected light guided to the second optical path 106 is reflected by the total reflection mirror 119, and is temporarily reflected by the objective lens 104.
The image is formed as 3, and the total reflection mirror 118 and the lens 11 are formed.
7, total reflection mirror 116, diaphragm 124, half mirror 1
The image is formed as a ring image i ₁ on the two-dimensional image sensor 107 via the imaging lens 108. The image forming magnification of the ring image i ₁ is set to be larger than the image forming magnification of the ring image i ₂ .

The diaphragm 110 includes a lens 111 and a lens 11.
3 is relayed near the rear focal position of the objective lens 104, the conjugate image 125 is formed at the rear focal position of the objective lens 104, and the optical system of the first optical path 105 is telecentric to the object side. The diaphragm 124 is a lens 117.
Is relayed to the front of the eye 103 (in front of the objective lens 104) by the conjugate image (real image) 12 here.
6 is formed at a location 25 mm to 50 mm in front of the eye 103 to be inspected.

The position of the apex 120P of the cornea using this corneal distance measuring system 100 is obtained based on the ring-shaped images i ₂ and i ₁ formed on the two-dimensional light receiving element 107, and the details thereof are described in Japanese Patent Application _No. Hei 10-135. 2-145107 (Title of Invention: Intraocular length measuring device: filing date May 31, 1990; JP-A-4-35)
No. 637), a detailed description thereof will be omitted.

Next, the interference optical system 101 will be described with reference to FIGS. 1, 3, and 4.

The interference optical system 101 comprises a measurement light source 130, a polarization beam splitter 190 which plays the role of a linear polarizer, and a lens 133, which constitute a measurement light source section. The measurement light source 130 has a low coherence length, and the coherence length is, for example, 0.05 mm to 0.
Use a thing of about 1 mm. The measurement light source 130 is driven by the laser driving unit 153.

The light beam Q emitted from the measurement light source 130 is linearly polarized (here, P wave) by the polarization beam splitter 190 as shown in FIG. The P-polarized light beam Q is converged on the pinhole 134 by the lens 133. The pinhole 134 serves as a quasi-point light source. The light flux Q that has passed through the pinhole 134 is guided to the beam splitter 135.

The beam splitter 135 splits the light flux Q emitted from the measurement light source unit into a measurement light passing through the inside of the eye to be examined and a reference light passing through the reference surface corresponding to the eye to be examined, and the measurement light path 1
71 and the reference light path 174 are formed, and the measurement light path 171 and the reference light path 174 are combined to form an interference light path 173.
(See FIGS. 1 and 4).

A lens 136, a focusing lens 137, a dichroic mirror 115, an objective lens 104, and a quarter-wave plate 191 are provided in the measurement optical path 171. A collimator lens 138 and a total reflection mirror 1 are provided in the reference optical path 174.
72, a quarter-wave plate 192 as a retarder, and a movable reference mirror 176 as a reference surface corresponding to the eye to be inspected. The pinhole 140 and the lens 14 are provided in the interference optical path 173.
1, an analyzer 193, and a light receiving element 142 are provided.

The lens 136 has a beam splitter 135.
Plays a role of collimating the light flux reflected by. The light beam collimated by the lens 136 is guided to the focusing lens 137 as measurement light. Focusing lens 13
Numeral 7 is movable in the optical axis direction and serves as a refractive power correction optical system for the eye 103 to be inspected. Reference numeral 200 is a drive motor for the focusing lens 137.

The measurement light passing through the focusing lens 137 passes through the dichroic mirror 115 and the objective lens 104,
The axis of the polarization direction is guided to the quarter-wave plate 191 fixed at 45 °. The quarter-wave plate 191 functions as a circular polarizer,
The measurement light that has passed through the focusing lens 137 is guided to the subject's eye 103 as right-handed circularly polarized light, and is converged on the fundus 152 as an intraocular measurement target.

When the clockwise circularly polarized measuring light is reflected by the fundus 152, if the eyeball does not have birefringence, it becomes counterclockwise circularly polarized light as shown in FIG. The counterclockwise circularly polarized measuring light becomes S-wave linearly polarized light when passing through the quarter-wave plate 191. That is, the polarization direction of the measurement light incident on the eye 103 and the polarization direction of the measurement light reflected by the fundus 152 are deviated by 90 °. The focusing lens 137 has a function of collimating the measurement light reflected by the fundus 152, and the collimated measurement light is relayed to the pinhole 140 via the lens 136 and the beam splitter 135. The pinhole 140 is provided at a conjugate position with respect to the reflecting surfaces of the pinhole 134 and the beam splitter 135, and the measurement light reflected by the fundus 152 is pinned even if the optical axis of the objective lens 104 is slightly deviated from the subject's eye 103. It can pass through the hole 140.

The light flux that has passed through the beam splitter 135 is guided to the collimator lens 138 as reference light. The reference light is made into a parallel light flux by the collimator lens 138, reflected by the total reflection mirror 172, and guided to the quarter-wave plate 192. The axis of the polarization direction of the quarter-wave plate 192 is set to 45 °. The quarter wave plate 192 functions as a retarder.

The reference light is made into clockwise circularly polarized light by the quarter-wave plate 192 and guided to the movable reference mirror 176. The movable reference mirror 176 is moved so that the optical path length of the reference optical path 174 and the measuring optical path length of the measuring optical path 171 are the same.

The reference light reflected by the movable reference mirror 176 becomes counterclockwise circularly polarized light based on the reflection. This counterclockwise circularly polarized reference light is converted into S by the quarter-wave plate 192.
It becomes a linearly polarized wave. The S-wave reference light passes through the beam splitter 135, is reflected by the beam splitter 135, is combined with the S-wave measurement light, and becomes interference light. The interference light is relayed to the pinhole 140, and the interference light passing through the pinhole 140 is condensed by the lens 141 and converged on the light receiving element 142 through the analyzer 193.

When the movable reference mirror 176 is moved and the optical path difference between the reference optical path 174 and the measurement optical path 171 becomes equal to or less than the coherent length, the reference light and the measurement light interfere with each other, and the moving speed of the movable reference mirror 176 and the measurement. An interference signal corresponding to the oscillation wavelength of the light beam emitted from the light source 130 is obtained by the light receiving element 142. This interference signal changes sinusoidally every time the optical path difference between the reference optical path 174 and the measurement optical path 171 changes by one wavelength of the oscillation wavelength of the measurement light source 130, and the optical path length between the reference optical path 174 and the measurement optical path 171 changes. When they are equal,
The strongest interference is obtained. That is, the optical path length of the reference optical path 174 when the strongest interference is obtained is equal to the optical path length of the measurement optical path 171, and the position of the movable reference mirror 176 at this time is the fundus 152 relative to the reflecting surface of the beam splitter 135.
Will be in the same position as. However, since the eyeball has birefringence, it is impossible to predict what polarization state the reflected light from the fundus 152 will enter even if the eyeball is circularly polarized.

When the measurement light having a polarization state different from the polarization state of the measurement light Q incident on the fundus 152 and the linearly polarized reference light reflected by the movable reference mirror 176 are interfered with each other, two polarizations having a phase difference are obtained. Since the phase components due to are mixed, the contrast of the interference signal is reduced as compared with the case where there is no birefringence.

Here, when the reference light having the linear polarization component of the P wave is made incident on the quarter wavelength plate 192, it
When the axis of the polarization direction of the wave plate 192 is rotated by θ ° from the axis of linear polarization of the P wave, it is reflected by the movable reference mirror 176 and returns to the quarter wave plate 192 again to return to the quarter wave plate 19.
The reference light flux that has passed through 2 becomes a reference light flux having a linear polarization component that is rotated by θ ° that is twice the axis of the linear polarization of the P wave.

Therefore, in order to maximize the contrast of the interference signal obtained by the interference between the measurement light reflected by the fundus 152 and the reference light, the 1/4 wavelength plate 192 is rotated around its optical axis by the pulse motor M _1. So that only the interference component due to the two light beams is obtained while rotating
The pulse motor M ₂ rotates the analyzer 193 around its optical axis. The pulse motors M ₁ and M ₂ are controlled by the control circuit 15
7 is driven synchronously.

Next, details of the signal processing will be described with reference to FIG.

The measurement light reflected by the fundus 152 is weaker than the reference light, and has a large light amount difference. But,
Since both light fluxes are interfered with each other and measured as an interference signal, a noise component or the like based on the dark current of the light receiving element 142 can be removed, and the signal component can be efficiently detected.
Therefore, the amplifier 150 amplifies only the AC component of the interference signal of the light receiving element 142.

The interference signal C ₄ obtained at this time has an AC waveform centered on 0 V as shown in FIG. 6, but is buried in random noise such as shot noise. For this reason,
As it is, it is difficult to detect the position of the movable reference mirror 176 at the time when the interference signal C ₄ is obtained.

However, the frequency f of the interference signal C ₄ is
Is the moving speed V of the movable reference mirror 176 and the measurement light source 1
If the transmission wavelength λ _{0 of} 30 is known, it can be calculated by the following formula.

F = 2 · V / λ ₀ Here, if the moving amount of the movable reference mirror 176 is set appropriately and the moving speed V during measurement is considered to be constant, a bandpass filter (center frequency at the frequency f) ( BPF) 17
By using 9, it is possible to extract only the interference signal C ₄ from the random noise.

When the position of the movable reference mirror 176 is plotted on the abscissa and the output voltage of the light receiving element 142 is plotted on the ordinate, the interference signal C ₄ shown in FIG. 6 is obtained from the bandpass filter 179. The interference signal C ₄ is input to the full-wave rectifier circuit 180 and shaped into the rectified waveform C ₅ shown in FIG. 7. The rectified waveform C ₅ is input to the smoothing circuit 181, and the smoothed waveform C ₆ shown in FIG. 8 is obtained.

The smoothed waveform C ₆ is the peak hold circuit 18
2 is input to the comparison circuit 183 via the A / D
It is input to the converter 189. Peak hold circuit 1
Reference numeral 82 holds a voltage lower than the smoothed waveform C ₆ by ΔV as a peak voltage and outputs the held voltage. That is, the peak hold circuit 182 outputs the waveform C ₇ as shown in FIG. The comparison circuit 183 has the waveform C ₆ and the waveform C.
₇ is compared, the output changes from L to H at the position X ₀ where the waveform C ₇ becomes larger than the waveform C ₆ , and the step signal C ₈ is output.

Here, if ΔV is sufficiently smaller than the output peak level V of the smoothed waveform C ₆ , the amount of deviation from the original peak position X _p of the inversion position X ₀ of the output signal of the comparison circuit 183 is determined. It may be considered that d is sufficiently small, and the movable reference mirror 17 when the output signal of the comparison circuit 183 is inverted.
The position X ₀ of 6 may be regarded as the position of the movable reference mirror 176 at the time when the strongest interference occurs.

The output signal of the comparison circuit 183 is input to the latch circuit 184 and the control circuit 157. The movable reference mirror 176 is driven by the unit drive unit 185, and the position data can be detected by the position detection circuit 186. The latch circuit 184 includes a movable reference mirror 176.
The position data of the position detection circuit 186, which indicates the amount of movement of, is latched.

The position detection circuit 186 has a structure in which, for example, the output signal of an encoder that outputs a pulse train in accordance with the rotation of the motor of the unit drive section 185 is counted, and the movement amount of the movable reference mirror 176 is detected from the counted number. do it. Further, the output signal of the linear encoder directly set on the movable reference mirror 176 may be counted.

Therefore, the latch circuit 184 receives the interference signal C.
The position data of the movable reference mirror 176 when ₄ appears most strongly is stored. The position data is input to the calculation unit 129, and the distance from the reference position to the intraocular measurement object 152 is measured. Moreover, since the distance from the reference position to the corneal apex 120P can be measured by the corneal distance measuring system 100, the size of the living eye can be measured from both measurement results.

However, the actual measurement is 1 as a retarder.
Measurement is performed after the work of adjusting the rotations of the quarter wave plate 192 and the analyzer 193 is performed. The measurement result is displayed on the display unit 164.

Here, in order to remove the influence of the slight movement of the eye 103 to be inspected, both the measurements need to be performed at the same time, but the output signal of the comparison circuit 183 is used as the start signal of the corneal distance measuring system 100 to control it. Simultaneous measurement can be performed by taking in the data of the ring images i1 and i2 of the two-dimensional image sensor 107 to the frame memory 163 at the same time that the circuit 157 detects the start signal.

A bandpass filter 179, a full-wave rectifier circuit 180, a smoothing circuit 181, a peak hold circuit 182,
The waveform shaping circuit 178 having the comparison circuit 183 functions as the start signal generation unit 178 of the corneal distance measurement system 100.

Next, the quarter-wave plate 192 and the analyzer 193 are provided.
The rotation control will be described.

From the quarter wave plate operating unit 194 to the control circuit 1
When the rotation drive signal is sent to 57, the control circuit 157 drives the pulse motors M ₁ and M _2, and the quarter wave plate 192 and the analyzer 193 are rotated. The rotation speeds of the quarter-wave plate 192 and the analyzer 193 are not synchronized with the moving speed of the movable reference mirror 176 and the moving speed of the focusing lens 137.

That is, one stroke period of the movable reference mirror 176 (the period required for the movable reference mirror 176 to move from one end to the other end of the movable range) and the focusing lens 1.
It is necessary to make a difference in one stroke period of 37 (the period required for moving the focusing lens 137 from one end to the other end of the movable range).

If the one-stroke period of the movable reference mirror 176 is sufficiently shorter than the one-stroke period of the focusing lens 137 or vice versa, that is, if the difference is increased, the measurement time is increased. It can be shortened.

When the axis of the quarter-wave plate 192 is rotated by 0 ° to 90 °, the movable reference mirror 176 reflects again the linearly polarized light of the reference light before entering the quarter-wave plate 192 and is reflected again. The direction of the linearly polarized light of the reference light after returning to the quarter-wave plate 192 and passing through the quarter-wave plate 192 is rotated about 0 ° to 180 ° around the optical axis.

Therefore, if the polarization state of the measurement light reflected by the fundus 152 is elliptically polarized light, the light receiving element 142 can be simply rotated by rotating the ¼ wavelength plate 192 and the analyzer 193 so as to match the major axis of the ellipse. Therefore, an interference signal having a good contrast can be obtained. As a result, the maximum amount of reflected light of the measurement light from the fundus 152 can be dealt with regardless of the polarization direction.

Therefore, the quarter wave plate 192 is set to 0 ° to 90 °.
, The analyzer 193 is rotated from 0 ° to 180 °, and the interference signal output from the light receiving element 142 is passed through the amplifier 150, the bandpass filter 179, the full-wave rectifier circuit 180, and the smoothing circuit 181 to the A / D converter 189. To A /
The data is converted by the D converter 189 and the control circuit 15
7, the interference signal data is accumulated, and the rotation angle of the 1/4 wavelength plate 192 and the analyzer 193 that maximize the amount of received light is extracted from the interference signal data (when the contrast of the interference signal is the best). The quarter-wave plate 192 and the rotation angle of the analyzer 193 are extracted), and the quarter-wave plate 192 and the analyzer 19 are extracted.
These are preset to the rotation angle position of 3. And
The control circuit 157 will then proceed to the actual dimensioning of the living eye.

Reference numeral 160 is a level display circuit for displaying the peak hold level, 162 is a gate array to which data is input from the two-dimensional image sensor 107, reference numeral 163 is a frame memory, and reference numeral 170 is a monitor television.

The size of the living eye is determined based on the position from the device optical system to the apex of the cornea and the position from the device optical system to the intraocular measurement object. For details, see Japanese Patent Application No. 2-1451075. Since it is described in the issue, the explanation is omitted. Regarding the details of measurement and calculation, Japanese Patent Application No. 3-2799697 (Title of the invention; Eye length measuring device with diopter adjustment function; filed on October 25, 1991; withdrawn due to domestic priority) and Japanese Patent Application No. 4-286109 (Invention name: Living eye size measuring device with refractive power correction function; Japanese Patent Application No. 3)
-Priority application for domestic priority based on No. 279697; Heisei 4
The description is omitted here.

The present invention is not limited to this,
The cornea 120 may be formed by another method, for example, a light source having a long coherence length of the measurement light source 130 of the interference optical system and capable of changing the wavelength.
The present invention can also be applied to a living eye size measuring device that measures the distance from P to the intraocular measurement object 152.

[0058]

Since the present invention is configured as described above, reflected light can be reliably obtained from an intraocular measurement object without being affected by the polarization characteristics and birefringence of the eyeball. It is possible to measure the size of the living eye.

[Brief description of drawings]

FIG. 1 is an optical diagram of an ophthalmic measurement apparatus according to an embodiment of the present invention.

FIG. 2 is an explanatory diagram showing a double ring image formed on a two-dimensional image sensor.

FIG. 3 is a schematic diagram showing a polarization state of a light beam incident on an eye to be inspected and a movable reference mirror.

FIG. 4 is a schematic diagram showing polarization states of reflected light beams from an eye to be inspected and a movable reference mirror.

FIG. 5 is a block circuit diagram of the ophthalmic measurement apparatus of the present invention.

FIG. 6 is a waveform diagram showing an interference signal.

FIG. 7 is a rectified waveform diagram of an interference signal.

FIG. 8 is a waveform diagram in which a rectified waveform of an interference signal is smoothed.

9 is an explanatory diagram for detecting the peak hold of the waveform shown in FIG. 7. FIG.

[Explanation of symbols]

 130 Measurement Light Source 135 Beam Splitter 171 Measurement Optical Path 173 Interference Optical Path 174 Reference Optical Path 190 Polarizing Beam Splitter (Linear Polarizer) 191 1/4 Wave Plate (Circular Polarizer) 192 1/4 Wave Plate (Phase Shifter) 193 Analyzer

Claims (4)

[Claims] 1. A measurement light source unit that emits a light beam for measurement, and a light beam emitted from the measurement light source unit is divided into a measurement light beam that passes through the inside of the eye and a reference light beam that passes through a reference surface corresponding to the eye. Then, an interference optical system including a beam splitter that forms a measurement optical path and a reference optical path, and combines the measurement optical path and the reference optical path to form an interference optical path, and is reflected by the measurement object in the eye to be inspected. In the ophthalmic measuring device having a light receiving element for receiving the interference light by the measured light and the reference light reflected by the reference surface corresponding to the eye to be inspected, the measurement light source unit emits a linearly polarized light beam, For ophthalmology, characterized by having a circular polarizer provided in the measurement optical path for being incident on the optometry as a circularly polarized light beam, and a retarder provided in the reference optical path so that the polarization direction can be changed. measuring device. 2. A corneal distance measuring system that measures a corneal apex position using a geometrical optical principle, and an interference optical system that measures a position of an intraocular measurement target using a physical optical principle, In the interference optical system, the luminous flux emitted from the measurement light source unit is divided into a measurement light passing through the inside of the eye to be inspected and a reference light passing through the reference surface corresponding to the eye to be inspected to form a measurement optical path and a reference optical path, and A beam splitter that forms a coherent optical path by combining the measuring optical path and the reference optical path is provided, and the coherent optical path is reflected by the measurement light reflected by the intraocular measurement target and the reference surface corresponding to the eye. A light receiving element for receiving the interference light due to the reference light is provided, and in the ophthalmic measuring device for measuring the length from the intraocular measurement object to the corneal apex position, the light flux emitted from the measurement light source unit is linearly polarized light. Yes,
A circular polarizer is provided in the measurement optical path, and a phase shifter is provided in the reference optical path. 3. The ophthalmic measuring device according to claim 1, wherein an analyzer is provided between the beam splitter and the light receiving element. 4. The ophthalmic measurement device according to claim 1, wherein the retarder and the analyzer are rotatable about an optical axis.