JP2011072611A - Ophthalmologic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To appropriately perform the examination and observation of an examined eye even if the difference in wavelength between a first luminous flux and a second luminous flux is small. <P>SOLUTION: The ophthalmologic apparatus includes a first optical system for emitting/receiving the first luminous flux for examining a first ocular characteristic, and a second optical system for emitting/receiving the second luminous flux for examining a second ocular characteristic different from the first ocular characteristic or for observing the examined eye image. In the ophthalmologic apparatus for examining the examined eye, a first region to be used for transmission of one of the first luminous flux and second luminous flux is formed at a position different from a second region with a different characteristic than the first region to be used for reflecting the other luminous flux. The ophthalmologic apparatus also has a light path dividing member for dividing the first luminous flux and second luminous flux from each other according to the transmission or reflection. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an ophthalmologic apparatus for inspecting an eye to be examined.

  In an ophthalmologic apparatus for inspecting an eye to be examined, a first light beam for inspecting a first eye characteristic and a second eye characteristic different from the first eye characteristic or an eye image to be examined are observed. As an optical path branching member for branching the second light flux, a dichroic mirror is known in which a coating having a characteristic of transmitting light of a predetermined wavelength and reflecting other light is applied to one surface (see Patent Document 1). ).

JP 2007-105130 A

  However, when the wavelength difference between the first light beam and the second light beam branched by the dichroic mirror is small, it is difficult to completely branch them for each wavelength. For this reason, originally, even if an attempt is made to transmit most of the first light and reflect most of the second light, most of the second light is transmitted, resulting in the second eye characteristic. Examination, observation of an eye image to be examined, etc. cannot be performed suitably.

  In view of the above problems, the present invention provides an ophthalmologic apparatus that can suitably perform examination of an eye to be examined and observation of an eye image to be examined even when the wavelength difference between the first light flux and the second light flux is small. It is a technical issue to provide.

  In order to solve the above problems, the present invention is characterized by having the following configuration.

(1) a first optical system that projects and receives a first light beam for inspecting a first eye characteristic;
An ophthalmologic apparatus for inspecting an eye to be examined, comprising: a second optical system that projects and receives a second light beam for inspecting a second eye characteristic different from the first eye characteristic or observing an eye image to be examined In
A first region used for transmitting one of the first light beam and the second light beam, and a second region used for reflecting the other light beam having characteristics different from the first region. An optical path branching member that is formed at different positions and branches the first light flux and the second light flux by transmission and reflection is provided.
(2) In the ophthalmic apparatus according to (1),
The first optical system includes a projection optical system that projects slit light onto the subject's eye,
The second optical system includes an imaging optical system that captures a front image of the anterior segment of the eye to be examined;
One of the first region and the second region of the optical path branching member is formed in a slit shape at the center of the optical path branching member, and the other is formed at the peripheral portion of the optical path branching member. It is characterized by.
(3) In the ophthalmologic apparatus of (2),
The first region has a characteristic of transmitting at least most of the one light beam and most of the other light beam, and the second region has at least most of the other light beam and the one light beam. It has a characteristic of reflecting most of the light.
(4) In the ophthalmic apparatus according to (3),
The wavelength difference between the first light beam and the second light beam branched by the optical path branching member is λ = 100 nm or less.
(5) In the ophthalmic apparatus according to (4),
The optical path branching member is
The first region formed by a dichroic mirror coating having a wavelength characteristic that transmits at least most of the one light flux and most of the other light flux and reflects other light;
The second region formed by a dichroic mirror coating having a wavelength characteristic that reflects at least a majority of the other light flux and a majority of the one light flux and transmits other light;
It is characterized by having at least one of these.

  According to the present invention, even when the wavelength difference between the first light flux and the second light flux is small, it is possible to suitably inspect and observe the eye to be examined.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a schematic configuration diagram showing an optical system of a corneal shape measuring apparatus (ophthalmic apparatus). The present optical system includes a kerato projection optical system 20 that projects an index for measuring a corneal shape onto a subject's eye cornea, a visible illumination optical system 80 that illuminates the anterior eye portion of the subject's eye with visible light, and an alignment projection optical system 50. An anterior ocular segment front imaging optical system 30 for imaging an anterior ocular segment front image, a fixation target projection optical system 40, and a second light source for measuring a second eye characteristic. The second measurement optical system 60 that projects the second measurement light and receives the reflected light thereof, and the anterior segment measurement optical system 90 that performs the measurement using the anterior segment cross-sectional image of the subject's eye are roughly classified. Is done. The following optical system is built in a housing (not shown). Further, the casing is three-dimensionally moved with respect to the subject's eye via an operation member (for example, a joystick) by driving a known alignment moving mechanism.

  The projection optical system 20 includes a ring-shaped light source 21 disposed around the measurement optical axis L1, and measures a corneal shape (curvature, astigmatic axis angle, etc.) by projecting a ring index R2 onto the eye cornea to be examined. (See FIG. 2 (a)). As the light source 21, for example, an LED that emits infrared light or visible light is used. In the projection optical system 20, it is sufficient if at least three or more point light sources are arranged on the same circumference centered on the optical axis L1, and an intermittent ring light source may be used. Further, it may be a placido index projection optical system that projects a plurality of ring indexes.

  The visible illumination optical system 80 includes four green light sources 81 that are arranged outside the light source 21 and are arranged around the measurement optical axis L1. The green light source 81 is a light source different from the light source 21 for measuring the corneal shape, and is used to illuminate the anterior segment with green light and capture an anterior segment image including a blue or purple corneal marking M ( (Refer FIG.2 (b)).

  The corneal marking M is an ink applied to the white eye portion for the operation of the intraocular lens for correcting astigmatism, and is a first corneal marking applied in accordance with the horizontal axis direction of the eye to be examined. As the light source 81, for example, a light source (for example, a green LED) that emits light in a wavelength region of 500 nm to 550 nm with a center wavelength of λ = 525 nm is used. However, the present invention is not limited to this, and a filter having a characteristic of transmitting only the green band may be provided in front of the white light source.

  The alignment projection optical system 50 is disposed inside the light source 21, has a projection light source 51 (for example, λ = 970 nm) that emits infrared light, and is used to project an alignment index onto the subject's eye cornea. And the alignment parameter | index projected on the cornea is used for position alignment (for example, automatic alignment, alignment detection, manual alignment, etc.) with respect to a subject's eye. In the present embodiment, the projection optical system 50 is an optical system that projects a ring index onto the subject's eye cornea, and as shown in FIG. 2, the ring index R1 is on the cornea of the subject's eye. Projected. The ring index R1 also serves as a Mayer ring. Further, the light source 51 of the projection optical system 50 also serves as anterior segment illumination for illuminating the anterior segment with infrared light from an oblique direction. The projection optical system 50 may further include an optical system that projects parallel light on the cornea, and the front-rear alignment may be performed by a combination with the finite light by the projection optical system 50.

  The anterior segment front imaging optical system 30 includes a dichroic mirror 33, an objective lens 47, a dichroic mirror 62, a filter 34, an imaging lens 37, and a two-dimensional imaging device 35, and captures an anterior segment front image of the eye to be examined. Used for.

  Here, the anterior ocular segment light reflected by the projection optical system 20, the visible illumination optical system 80, and the projection optical system 50 passes through the beam splitter 33, the objective lens 47, the dichroic mirror 62, the filter 34, and the imaging lens 37. An image is formed on the two-dimensional image sensor 35.

  That is, the imaging optical system 30 captures the anterior segment image A including the ring index (corneal reflection image) R2 formed on the cornea Ec by photographing the anterior segment image irradiated with the light from the light source 21. Can shoot. When the corneal marking M is applied to the anterior segment, the imaging optical system 30 captures the anterior segment image A including the corneal marking M by photographing the anterior segment image illuminated by the green light source 81. Can shoot.

  The dichroic mirror (beam splitter) 62 is used as an optical path branching member for branching the optical path of the projection optical system 90a and the optical path of the imaging optical system 30 (details will be described later). The filter 34 transmits infrared light from the light source 51 and green light from the light source 81 and is used to block other light.

  With respect to the projection optical system 40, a fixation target projection optical system 40 is formed in the reflection direction of the dichroic mirror 45.

  The second measurement optical system 60 includes a second measurement optical unit 61 configured to project the second measurement light onto the subject's eye and receive the reflected light, the dichroic mirror 45, the beam splitter 33 (for example, half Mirror, dichroic mirror).

  As the second measurement optical system 60, for example, an axial length measurement optical system that receives the interference light by the measurement light and the reference light and measures the axial length (the wavelength of the measurement light source is, for example, λ = 830 nm) An eye refractive power measuring optical system that receives reflected light projected on the fundus of the subject's eye and measures the eye refractive power (the wavelength of the measurement light source is, for example, λ = 870 nm) can be considered.

  The anterior ocular segment measurement optical system 90 includes a projection optical system 90a that projects slit light for forming a cross-sectional image of the anterior ocular segment onto the subject's eye E, and an anterior segment by slit light projected by the projection optical system 90a. An imaging optical system 90b that receives the reflected light and captures an anterior segment cross-sectional image.

  The projection optical system 90 a includes a light source 91, a condenser lens 92, a slit plate 93, a total reflection mirror 94, a dichroic mirror 62, an objective lens 47, and a dichroic mirror 33.

  As the light source 91, for example, a visible light source that emits light (blue light) in a wavelength region of about 470 nm and a center wavelength of about 470 nm is used. The slit plate 93 is disposed at a position conjugate with the anterior eye part (for example, near the top of the cornea), and in FIG. 1, a slit opening whose horizontal direction is the longitudinal direction is formed.

  The objective lens 47 condenses the light from the light source 91 on the cornea. The optical axis (projection optical axis) of the projection optical system 90a is coaxial with the measurement axis L1.

  The imaging optical system 90b includes a two-dimensional imaging element 97 and an imaging lens 96 that guides the reflected light from the anterior segment by the projection optical system 90a to the imaging element 97, and is based on the Shine-Pluke principle. An image is captured. That is, the imaging optical system 90b is arranged such that its optical axis (imaging optical axis) intersects with the optical axis of the projection optical system 90a at a predetermined angle, and the optical cross section of the projection image by the projection optical system 90a and the object to be examined The lens system including the cornea of the human eye (cornea and imaging lens 96) and the imaging surface of the imaging element 97 are arranged in a shine-proof relationship. A filter 99 that transmits only light (blue light) emitted from the light source 91 and used to capture the anterior eye section image is disposed in front of the lens 96 (the subject eye E side). Yes.

  Next, the control system will be described. The control unit 70 controls the entire apparatus and calculates measurement results. The control unit 70 includes a light source 91, a light source 51, a light source 21, a light source 81, an image sensor 35, an image sensor 97, a second measurement optical unit 61, a fixation target projection optical system 40, a visible illumination optical system 80, a monitor 71, and a memory. 75, etc. Here, the imaging signal output from the imaging element 35 is subjected to image processing by the control unit 70 and displayed on the monitor 71. Further, the control unit 70 detects the alignment state with respect to the subject's eye based on the imaging signal output from the imaging device 35.

  The operation of the apparatus having the above configuration will be described. FIG. 2 is a diagram illustrating an anterior ocular segment observation screen on which an anterior ocular segment image captured by the image sensor 35 is displayed. At the time of alignment, the light source 51 and the light source 21 are turned on. Here, as shown in FIG. 2A, the examiner performs vertical and horizontal alignment so that the electronically displayed reticle LT and the ring index R1 by the light source 51 are concentric. In addition, the examiner performs front-rear alignment so that the ring index R1 is in focus. A ring index R2 from the light source 21 is displayed outside the ring index R1.

  When alignment is performed as described above and a predetermined trigger signal is generated, the control unit 70 further turns on the green light source 81 and captures an anterior ocular segment image using the image sensor 35. Then, based on the imaging signal output from the imaging device 35, the control unit 70 acquires the anterior ocular segment image including the ring indexes R1, R2 and the corneal marking M as a still image and stores it in the memory 75 (FIG. 2). (See (b)). Note that the four bright spots G in FIG. 2B are corneal bright spot images by the light source 81. In the above, a series of measurements are performed simultaneously, but the corneal shape measurement and the corneal marking M imaging may be performed at different timings.

  Then, the control unit 70, based on the ring index image R2 in the anterior segment image stored in the memory 75, the corneal shape of the eye to be examined (for example, the corneal curvature in the strong main meridian direction and the weak main meridian direction, the corneal astigmatism axis) And the measurement result is stored in the memory 75. In the case of a corneal astigmatic eye, the index image R2 has an elliptical shape, and thus the control unit 70 obtains the astigmatic axis angle by detecting the major axis direction and the minor axis direction.

  Further, the control unit 70 detects the position of the corneal marking M in the anterior ocular segment image stored in the memory 75 and stores the detection result in the memory 75. More specifically, the control unit 70 detects the boundary position between the iris and the white eye in a ring shape by image processing, and calculates the luminance distribution outside the boundary by a predetermined amount (see the dotted line T in FIG. 2B). Ask. Then, as shown in FIG. 3, in the luminance distribution, the control unit 70 detects a portion where the luminance level is the lowest (luminance level Mi) with respect to the luminance level Ma in the white-eye portion, and performs marking based on this. The position C of M is specified. Thereby, the positions of two corneal markings M that are symmetrical with respect to the pupil center (or corneal center) are detected.

  FIG. 4 is a diagram showing anterior segment data used when an intraocular lens for correcting astigmatism is inserted into an eye to be examined. The control unit 70 creates anterior segment data as shown in FIG. 4 based on the measurement result and the detection result, and displays the anterior segment data on the monitor 71.

  The line K1 and the line B1 are electronically synthesized (superimposed) by an image process on the anterior segment image stored in the memory 75. The line K1 is an index for indicating the astigmatic axis direction of the eye cornea to be examined with respect to the corneal marking M. Line B1 is an index for indicating a reference axis for performing corneal marking in the astigmatic axis direction, and corresponds to corneal marking M.

  The control unit 70 obtains the display angle of the line K1 based on the astigmatic axis angle calculated as described above, and synthesizes the line K1 so as to pass through the center of the ring index R2 in the anterior segment image. Further, the control unit 70 combines the straight line (line B1) connecting the two corneal markings M with the anterior ocular segment image based on the positions of the two corneal markings M obtained as described above.

  Further, the control unit 70 calculates an angle between the corneal marking M and the astigmatic axis direction based on the calculation result of the astigmatism axis and the detection result of the corneal marking M, and the calculation result is calculated with respect to the anterior segment image. You may synthesize | combine (refer RE of FIG. 4). For example, in the image processing, the angle can be detected based on the rotation angle when the line B1 is rotated with reference to the center of the pupil and coincides with the line K1.

  The anterior ocular segment data created by the image processing as described above is stored in the memory 75. The control unit 70 can display and output the anterior segment data on the monitor 71, and can also perform printing output and data output by a printer. The output data based on the anterior segment data as shown in FIG. 4 is used when the second corneal marking is applied to the position corresponding to the astigmatic axis of the eye cornea to be examined.

  According to the anterior segment data as shown in FIG. 4, the operator can confirm the angle of the astigmatism axis with respect to the first corneal marking M applied to the reference axis, so the second corneal marking corresponding to the astigmatism axis can be confirmed. It can be applied to the appropriate position on the cornea. Therefore, the intraocular lens for correcting astigmatism can be easily placed at an appropriate position in the eye.

  In the above configuration, by capturing an anterior segment image including the corneal marking M using the green light source 81, the contrast between the anterior segment image and the corneal marking in the anterior segment data described above becomes clear. Marking is easily visible. This is because the ink color of the corneal marking is usually blue or purple, and if it is green light that does not interfere with these in the three primary colors (red, blue, green), there is no reflection by the ink and the contrast with the white eye increases. It is. Note that purple is a mixed color of red and blue. The inventors also conducted experiments with other light, but it was found that the blue corneal marking was poorly visible in the case of blue light, and that the purple corneal marking was poor in the case of red light.

In the above description, it is assumed that visible light is illuminated with green light, but light in a wavelength band that does not easily interfere with the ink color used for corneal marking (for example, the center wavelength is between λ = 500 and 600). If it is the structure which emits the light which has a wavelength), it will not restrict to this. That is, any structure that emits light having a wavelength characteristic complementary to the ink color used for corneal marking may be used. As the light source, a light source having high monochromaticity is preferable.
In the anterior segment illumination optical system 80 of the above embodiment, one kind of light source is used for photographing the corneal marking M, but the present invention is not limited to this, and two or more light sources having different center wavelengths are provided. You may make it switch to the light source which does not interfere with the color of a cornea marking.

  The visible illumination optical system 80 and the imaging optical system 30 are not limited to the above configuration, and are configured so that the imaging element 35 receives the anterior segment reflected light having a wavelength characteristic complementary to the corneal marking. It only has to be done. For example, a white light source may be provided in the visible illumination optical system 80, and a filter having characteristics of transmitting green light and infrared light and absorbing other light may be provided in the optical path of the imaging optical system 30.

  In the above description, the detection result RE is output. However, the present invention is not limited to this. If the angle information for determining the angle between the corneal marking and the astigmatic axis direction is displayed together with the anterior eye image. Good. For example, an angle scale (for example, a protractor) for confirming the angle with the line K1 with respect to the corneal marking M may be synthesized and displayed on the anterior segment image. In this case, it is preferable that the position of the marking M is 0 degree and the scale is given.

  The controller 70 is not limited to the above configuration, and the control unit 70 can rotate the line K1 on the screen of the monitor 71 based on an operation signal from a predetermined switch manually operated by the examiner, and the line K1 and the cornea You may make it measure the rotation angle of the line K1 when the marking M corresponds. Further, the control unit 70 may measure the rotation angle by making the line B1 on the monitor 71 rotatable.

  The detailed configuration of the dichroic mirror 62 will be described below. In the present embodiment, the wavelength difference between the wavelength used for the light source 91 and the wavelength used for the light source 81 is 100 nm or less. For example, a blue light source (light having a central wavelength of about 470 nm and a wavelength region of about 460 to 490 nm) is used as the light source 91, and a green light source (wavelength of about 500 to 550 nm with a center wavelength of about 525 nm is used) as the light source 81. Area light) is used.

  In the above configuration, even when a dichroic mirror that has a coating that transmits light of λ = 500 nm or less and reflects more than this is designed, it is difficult to completely separate light having a small wavelength difference. = Most of light (about 80%) of the light source 81 having a wavelength band near 500 nm is transmitted (see FIG. 5). For this reason, the anterior ocular segment image including the corneal marking M cannot be suitably captured.

  FIG. 6 is a schematic configuration diagram when the dichroic mirror 62 according to the present embodiment is viewed from the front direction and the lateral direction. The dichroic mirror 62 is made of a single glass substrate 301, and is formed with a first region 303 and a second region 305 that are coated with different wavelength characteristics.

  The first region 303 is formed in a slit shape in the central portion of the substrate 301, and the second region 305 is formed in the peripheral portion of the substrate 301 excluding the first region 303. The first region 303 is used to transmit the light emitted from the light source 91 toward the eye E. On the other hand, the second region 305 is used to reflect the anterior segment reflected light from the light source 21, the light source 51, and the light source 81 toward the image sensor 35.

  The first region 303 corresponds to the slit width when the slit light from the projection optical system 90a passes through the dichroic mirror 62, and is formed in the same size.

  FIG. 7 is a diagram illustrating an example of wavelength characteristics of the first region 303. The coating of the first region 303 transmits about 100% of light of λ = 460 to 490 nm used for the blue light source 91, but also transmits light having a wavelength difference small from that of blue light (λ = 470 ± 125 nm). Has characteristics. Therefore, most of the light of λ = 500 to 550 nm used for the green light source 81 is transmitted and a part thereof is reflected. The infrared light used for the light source 51 is reflected by about 100%.

  FIG. 8 is a diagram illustrating an example of the wavelength characteristics of the second region 305. The coating of the second region 305 reflects about 80% of light of λ = 500 nm to 550 nm used for the green light source 81 and reflects about 100% of infrared light used for the light source 51 and the like. In this case, the light has a reflection characteristic with respect to green light (λ = 525 ± 125 nm) having a small wavelength difference. Therefore, most of the anterior segment reflected light from the blue light source 91 is reflected and part of it is transmitted. The infrared light used for the light source 51 and the like is reflected by about 100%.

  In the above configuration, the first region 303 transmits most of the reflected light from the green light source 81, but is only a part of the reflected light, and most of the reflected light is reflected by the second region 305 and received by the image sensor 35. Therefore, the anterior ocular segment image including the corneal marking M can be favorably captured.

  On the other hand, the second region 305 hardly transmits the light from the blue light source 91, but the passage region of the slit light from the slit plate 93 is almost the same as the first region 303 and thus has little influence.

  FIG. 9 is a diagram illustrating an example of the wavelength characteristics of the filter 34. The coating of the filter 34 transmits light of λ = 500 nm to 550 nm used for the green light source 81 and infrared light used for the light source 51 and the like.

  The reason why the transmittance of the green band is considerably smaller than the infrared band (can be expressed numerically) is to block visible disturbance light (for example, a fluorescent lamp) in addition to the difference in sensitivity characteristics of the image sensor 35. This is to cope with. Since the green band transmittance is reduced, it is preferable to increase the output of the green light source 81.

  Further, the filter 34 has transmission characteristics with respect to blue light, but there is no particular problem because it does not interfere with the photographing of the anterior segment cross-sectional image, the corneal curvature measurement, and the corneal marking photographing.

  If it carries out as mentioned above, the light with few wavelength differences can be effectively branched and combined by providing the effective area from which a wavelength characteristic differs mutually. Therefore, it is possible to suitably perform both the imaging of the anterior segment cross-sectional image and the imaging of the anterior segment including the corneal marking M.

  In the above description, the dichroic mirror coating is performed on the glass substrate 301. However, the present invention is not limited to this. For example, only the surface antireflection coating may be applied to the first region 303 so that all light is transmitted. Further, the second region 305 may be subjected to total reflection mirror coating to transmit all light. In this case, it is necessary to coat the filter 34 with visible disturbance light removal coating corresponding to a wide wavelength band.

  In the above configuration, a single glass plate is used as the coated substrate. However, the present invention is not limited to this, and the prism may be coated.

  As shown in FIG. 10, the filter 34 may be configured such that a filter 34G for corneal marking imaging and a filter 34R for alignment and kerato index imaging are switched and arranged.

  A measurement using the photographing optical system 30 in the apparatus having the above configuration will be briefly described. When alignment with the measurement optical axis L1 for the subject's eye using the anterior ocular segment front imaging optical system 30 is performed and a trigger signal for performing anterior segment cross-section imaging is issued, the control unit 70 causes the light source 91 to Lights up. The light from the light source 91 is collected by the condenser lens 92 and passes through the slit 93 to become slit light. The slit light is reflected by the dichroic mirror 94, passes through the dichroic mirror 62, is made into a substantially parallel light beam by the objective lens 47, is reflected by the beam splitter 33, and is collected on the anterior eye part. The slit cross-sectional image formed on the anterior eye part is imaged by the image sensor 97 via the filter 99 and the lens 96. And the control part 70 analyzes the cross-sectional image data acquired by the image pick-up element 97, and calculates the eye characteristic (corneal thickness, anterior chamber depth) of an anterior eye part. Then, the anterior segment cross-sectional image and the measurement result are displayed on the monitor 71.

  In the above configuration, the optical path branching member is used to branch the optical path of the projection optical system that projects the slit light onto the eye of the subject and the optical path of the imaging optical system that captures the front image of the anterior segment of the subject's eye. However, the present invention can also be applied to other optical systems.

  In other words, the first optical system that projects and receives the first light beam for inspecting the first eye characteristic, and the second eye characteristic different from the first eye characteristic or the eye image to be examined is observed. And a second optical system that projects and receives the second light flux, and can be applied to an ophthalmologic apparatus for examining the eye to be examined. In this case, the first region used for transmitting one of the first light beam and the second light beam, and the second region used for reflecting the other light beam, which have different characteristics from the first region. The optical paths of the first optical system and the second optical system are branched by using optical path branching members that are formed at different positions and branch the first and second light beams by transmission and reflection.

  In the above embodiment, the dichroic mirror 62 is provided with the first region 303 formed by the dichroic mirror coating having a wavelength characteristic that transmits blue light and green light and reflects infrared light. However, the present invention is not limited to this. is not. That is, a first region formed by a dichroic mirror coating having a wavelength characteristic that transmits most of at least one light beam and most of the other light beam and reflects other light, at least most of the other light beam and one of the other light beams What is necessary is just to have at least one of the said 2nd area | region formed by the dichroic mirror coating of the wavelength characteristic which reflects most light beams and permeate | transmits other light.

It is a schematic block diagram of the optical system and control system in this apparatus. It is a figure which shows the anterior ocular segment observation screen on which the imaged anterior segment image was displayed. It is the figure which showed the luminance distribution in a to-be-tested eye image. It is the figure which showed the anterior eye part image and its data which are used in astigmatism correction intraocular lens insertion. This is an example of a dichroic mirror in which a coating that transmits light of λ = 500 nm or less and reflects more light is applied to the entire surface. It is a schematic block diagram when the dichroic mirror which concerns on a present Example is seen from a front direction and a horizontal direction. It is a figure which shows the example of the wavelength characteristic of a 1st area | region. It is a figure which shows the example of the wavelength characteristic of a 2nd area | region. It is a figure which shows the example of the wavelength characteristic of a filter. It is the figure which showed the structure in arrangement | positioning switching with the filter for corneal marking imaging | photography, and the filter for alignment and kerato index imaging | photography.

20 kerato projection optical system 30 anterior ocular segment imaging optical system 34 filter 35 imaging device 40 fixation target projection optical system 50 alignment projection optical system 60 second measurement optical system 62 dichroic mirror 70 control unit 71 monitor 75 memory 80 visible illumination optical System 81 green light source 90 anterior ocular segment measurement optical system 90a projection optical system 90b imaging optical system 303 first region 305 second region

Claims (5)

A first optical system that projects and receives a first light beam for inspecting a first eye characteristic;
An ophthalmologic apparatus for inspecting an eye to be examined, comprising: a second optical system that projects and receives a second light beam for inspecting a second eye characteristic different from the first eye characteristic or observing an eye image to be examined In
A first region used for transmitting one of the first light beam and the second light beam, and a second region used for reflecting the other light beam having characteristics different from the first region. An ophthalmologic apparatus comprising: an optical path branching member that is formed at different positions and branches the first light flux and the second light flux by transmission and reflection. The ophthalmic device according to claim 1.
The first optical system includes a projection optical system that projects slit light onto the subject's eye,
The second optical system includes an imaging optical system that captures a front image of an anterior segment of an eye to be examined.
One of the first region and the second region of the optical path branching member is formed in a slit shape at the center of the optical path branching member, and the other is formed at the peripheral portion of the optical path branching member. Ophthalmic device characterized by. The ophthalmic apparatus according to claim 2.
The first region has a characteristic of transmitting at least most of the one light beam and most of the other light beam, and the second region has at least most of the other light beam and the one light beam. An ophthalmic apparatus characterized by reflecting most of the characteristics. The ophthalmic device according to claim 3.
An ophthalmologic apparatus, wherein a wavelength difference between the first light beam and the second light beam branched by the optical path branching member is λ = 100 nm or less. The ophthalmic device according to claim 4.
The optical path branching member is:
The first region formed by a dichroic mirror coating having a wavelength characteristic that transmits at least most of the one light flux and most of the other light flux and reflects other light;
The second region formed by a dichroic mirror coating having a wavelength characteristic that reflects at least a majority of the other luminous flux and a majority of the one luminous flux and transmits other light;
An ophthalmologic apparatus having at least one of the above.

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