JP6654378B2 - Ophthalmic equipment - Google Patents

Description

  The present invention relates to an ophthalmologic apparatus.

  Cataract is an eye disease in which visual acuity gradually decreases due to clouding of a crystalline lens serving as a lens. Cataract surgery is generally performed on the subject's eye where the cataract has advanced. For example, in cataract surgery, an opaque lens is removed, and an intraocular lens (hereinafter, IOL) is inserted instead. The IOL includes a type having only a spherical degree, a toric IOL capable of correcting astigmatism, and a multifocal IOL capable of focusing both far and near. Prior to cataract surgery, measurement of eyeball information (such as the axial length) representing the structure of the eye to be examined is performed, and the frequency of IOL is determined from the obtained eyeball information.

JP 2012-161425 A

  To determine the IOL power, a plurality of intraocular distances such as the axial length of the eye and the anterior chamber depth are required. However, when these plural intraocular distances are measured in a wide measurement range, there is a problem that the measurement accuracy is reduced and the error of the obtained IOL power is increased.

  The present invention has been made to solve such a problem, and an object of the present invention is to provide an ophthalmologic apparatus capable of measuring an intraocular distance of a subject's eye with high accuracy.

The ophthalmologic apparatus according to the embodiment includes an interference optical system, a first focusing lens, a second focusing lens, a focusing control unit, and an intraocular distance calculation unit. The interference optical system divides light from the first light source into reference light and measurement light, irradiates the measurement light to the subject's eye, generates interference light between the returned light and the reference light, and generates the generated interference light. Is detected. The first focusing lens is movable along the optical path of the measurement light. The second focusing lens can be inserted into and removed from the optical path of the measurement light. The focusing control unit controls at least movement of the first focusing lens. The intraocular distance calculation unit calculates the first intraocular distance based on the first detection data of the interference light acquired by the interference optical system in a state where the second focusing lens is retracted from the optical path, and calculates the second focusing distance. The second intraocular distance is obtained based on the second detection data of the interference light obtained by the interference optical system while the lens is inserted in the optical path. Before the first detection data is acquired, the focus control unit, so that the position corresponding to the measurement result of the refractive power of the eye, or corresponding to the interference light you corresponds to the first region to be examined the intensity of the interference signal is to control the highest made by Uni first focusing lens. Before the second detection data is acquired, the focus control unit, by sea urchin first Go to intensity of the interference signal corresponding to the interference light you corresponds to the second site in different subject eye and the first portion is the highest Control the focus lens.

  According to the embodiment, it is possible to provide an ophthalmologic apparatus capable of measuring the intraocular distance of the subject's eye with high accuracy.

It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is the schematic which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment. FIG. 7 is a flowchart illustrating an operation example of the ophthalmologic apparatus according to the embodiment.

  An example of an embodiment of an ophthalmologic apparatus according to the present invention will be described in detail with reference to the drawings. In addition, the description content of the literature and any known technology cited in this specification can be used in the following embodiments.

  The ophthalmologic apparatus according to the embodiment is capable of performing objective measurement and subjective examination. Objective measurement is a measurement technique for acquiring information about an eye to be examined mainly by using a physical technique without referring to a response from the subject.

  Objective measurement includes measurement for acquiring the characteristics of the eye to be inspected and imaging for acquiring an image of the eye to be inspected. The objective measurement includes objective refraction measurement, corneal shape measurement, intraocular pressure measurement, fundus photography, optical coherence tomography (hereinafter, OCT), and the like.

  On the other hand, the subjective test is a measurement technique for acquiring information using a response from a subject. The subjective test includes a subjective refraction measurement such as a distance test, a near test, a contrast test, and a glare test, and a visual field test.

  The ophthalmologic apparatus according to the embodiment can execute at least one of an arbitrary subjective test and an arbitrary objective measurement. When the optical interference measurement can be performed, the optical interference measurement is used to acquire eyeball information representing the structure of the eye to be examined, such as the axial length of the eye, the corneal thickness, the anterior chamber depth, and the lens thickness. In addition, optical interference measurement can be used to acquire an image or analysis data of the eye to be inspected.

<Structure>
1 and 2 show a configuration example of an ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, an optotype projection system 4, an observation system 5, a reflex measurement projection system 6, a reflex system as an optical system for inspecting the eye E to be inspected. It includes a measuring light receiving system 7 and an intraocular distance measuring system 8. Further, the ophthalmologic apparatus 1000 includes the processing unit 9.

(Processing unit 9)
The processing unit 9 controls each unit of the ophthalmologic apparatus 1000. The processing unit 9 can execute various arithmetic processes. The processing unit 9 includes a processor. The functions of the processor include, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, an SPLD (Simple Programmable Programmable LPG), and the like). , FPGA (Field Programmable Gate Array) and the like. The processing unit 9 realizes a function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

(Observation system 5)
The observation system 5 captures a moving image of the anterior segment of the eye E. Light (infrared light) from the anterior segment of the eye E passes through the objective lens 51, passes through dichroic mirrors 52 and 53, and passes through the opening of the diaphragm 54. The light having passed through the aperture of the stop 54 passes through the half mirror 55, passes through the relay lenses 56 and 57, and is imaged by the imaging lens 58 on the imaging surface of the imaging element 59 (area sensor). The imaging element 59 performs imaging and signal output at a predetermined rate. The output (video signal) of the image sensor 59 is input to the processing unit 9. The processing unit 9 causes the display screen 10a of the display unit 10 to display the anterior ocular segment image E 'based on the video signal. The anterior eye image E ′ is, for example, an infrared moving image. The observation system 5 may include an illumination light source for illuminating the anterior segment.

(Z alignment system 1)
The Z alignment system 1 irradiates the eye E with light (infrared light) for performing alignment in the optical axis direction (front-back direction, Z direction) of the observation system 5. The light output from the Z alignment light source 11 irradiates the cornea K of the eye E, is reflected by the cornea K, and is imaged on the line sensor 13 by the imaging lens 12. When the position of the corneal vertex changes in the front-back direction, the projection position of light on the line sensor 13 changes. The processing unit 9 obtains the position of the vertex of the cornea of the eye E based on the projection position of the light on the line sensor 13, and executes the Z alignment based on this.

(XY alignment system 2)
The XY alignment system 2 irradiates the eye E with light (infrared light) for performing alignment in a direction (horizontal direction (X direction), vertical direction (Y direction)) orthogonal to the optical axis of the observation system 5. . The XY alignment system 2 includes an XY alignment light source 21 provided in an optical path branched from the observation system 5 by the half mirror 55. The light output from the XY alignment light source 21 is reflected by the half mirror 55 and is applied to the eye E through the observation system 5. The light reflected by the cornea K is guided to the image sensor 59 through the observation system 5.

  The image of the reflected light (bright point image) is included in the anterior ocular segment image E '. The processing unit 9 displays the anterior eye image E ′ including the bright spot image Br and the alignment mark AL on the display screen 10a, as shown in FIG. When performing XY alignment manually, the user performs an operation of moving the optical system so as to guide the bright spot image Br in the alignment mark AL. When performing automatic alignment, the processing unit 9 controls a mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is canceled.

(Kerato measurement system 3)
The keratometer 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea K onto the cornea K. The kerato plate 31 is arranged between the objective lens 51 and the eye E to be inspected. A kerat ring light source 32 is provided on the back side (the objective lens 51 side) of the kerato plate 31. By illuminating the kerato plate 31 with light from the kerat ring light source 32, a ring-shaped light beam is projected on the cornea K. The reflected light (kerattling image) is detected by the imaging element 59 together with the anterior eye image. The processing unit 9 calculates a corneal shape parameter by performing a known operation based on the kerattling image.

(Target projecting system 4)
The optotype projection system 4 presents various optotypes, such as a fixation target and an optotype for subjective examination, to the eye E to be examined. Light (visible light) output from the light source 41 is applied to the optotype chart 42. The optotype chart 42 includes a transmissive liquid crystal panel, for example, and displays a pattern representing the optotype. The light transmitted through the optotype chart 42 passes through the focusing lens 43 and the VCC lens 44, is reflected by the reflection mirror 45, is reflected by the dichroic mirror 53, passes through the dichroic mirror 52, and passes through the objective lens 51. It is projected on the fundus oculi Ef. The light source 41 and the optotype chart 42 are integrally movable in the optical axis direction.

  When performing the subjective test, the processing unit 9 controls the optotype chart 42, the light source 41, and the VCC lens 44 based on the result of the objective measurement. The processing unit 9 causes the optotype chart selected by the examiner or the processing unit 9 to be displayed on the optotype chart 42. Thereby, the target is presented to the subject. The subject responds to the optotype. In response to the input of the response content, the processing unit 9 performs further control and calculation of a subjective test value. For example, in the visual acuity measurement, the processing unit 9 selects and presents the next visual target based on the response to the Landolt's ring and the like, and determines the visual acuity value by repeatedly performing this.

(Ref measurement projection system 6 and Reflex measurement light receiving system 7)
The reflex measurement projection system 6 and the reflex measurement light receiving system 7 are used for objective refraction measurement (reflection measurement). The reflex measurement projection system 6 projects a ring light beam (infrared light) for objective measurement onto the fundus oculi Ef. The reflex measurement light receiving system 7 receives the return light of the ring-shaped light beam from the eye E to be examined.

  The reflex measurement light source 61 is movable in the optical axis direction, and is disposed at a position optically conjugate with the fundus oculi Ef. The light output from the reflex measurement light source 61 passes through the condenser lens 62, is reflected by the reflection mirror 63, passes through the conical prism 64A and the relay lens 64B, passes through the ring-shaped light transmitting portion of the ring stop 64C, and forms a ring. It becomes a luminous flux. The ring light beam formed by the ring stop 64C is reflected by the reflection surface of the perforated prism 65, passes through the rotary prism 66, and is guided to the quick return mirror 67.

  The rotary prism 66 is used for averaging the light amount distribution of the ring-shaped light beam with respect to the blood vessel or the diseased part of the fundus oculi Ef. The quick return mirror 67 is used for switching between objective refraction measurement and axial length measurement. When performing objective refraction measurement, the reflection surface of the quick return mirror 67 is arranged on an optical path (branched optical path) branched from the optical path of the observation system 5 by the dichroic mirror 52. Thereby, both the optical path of the reflex measurement projection system 6 and the optical path of the reflex measurement light receiving system 7 are coupled to the optical path of the observation system 5. On the other hand, when measuring the axial length, the quick return mirror 67 is retracted from this branch optical path. Thereby, the optical path of the intraocular distance measurement system 8 is coupled to the optical path of the observation system 5.

  In objective refraction measurement, the ring-shaped light beam that has passed through the rotary prism 66 is reflected by the quick return mirror 67, reflected by the dichroic mirror 52, passed through the objective lens 51, and projected on the fundus Ef.

  The return light of the ring-shaped light beam projected on the fundus Ef passes through the objective lens 51, and is reflected by the dichroic mirror 52 and the quick return mirror 67. The return light reflected by the quick return mirror 67 passes through the rotary prism 66, passes through the hole of the perforated prism 65, passes through the relay lens 71 and the focusing lens 72, and passes through the imaging lens 73 to the image sensor 74. Is imaged on the imaging surface of. The output of the image sensor 74 is input to the processing unit 9. The processing unit 9 calculates the spherical power S, the astigmatic power C, and the astigmatic axis angle A of the subject's eye E by performing a known calculation based on the output from the image sensor 74.

  The processing unit 9 moves the reflex measurement light source 61 and the focusing lens 72 in the optical axis direction to a position where the reflex measurement light source 61 and the fundus oculi Ef are conjugate based on the calculated refraction value. Further, the processing unit 9 moves the focusing lens 85 of the intraocular distance measurement system 8 in the optical axis direction in conjunction with the movement of the focusing lens 72 and the reflex measurement light source 61. The processing unit 9 can also move the reflex measurement light source 61, the focusing lens 72 and the focusing lens 85, the light source 41, and the optotype chart 42 integrally.

(Intraocular distance measurement system 8)
The intraocular distance measurement system 8 performs optical interference measurement for measuring intraocular distance as eyeball information. When the optical interference measurement is performed, the quick return mirror 67 is retracted from the branch optical path. Further, the reflex measurement is performed before the optical interference measurement, and the position of the focusing lens 85 is adjusted so that the end face of the optical fiber 80a is conjugate with the fundus oculi Ef.

  As shown in FIG. 2, in the interferometer unit 80, light (infrared light, broadband light) L0 output from the interferometer light source 81 is measured light LS and reference light by a fiber coupler 82 guided through an optical fiber 80b. LR. The measurement light LS is guided to the collimator lens 84 through the optical fiber 80a. On the other hand, the reference light LR is guided to the reference light path length changing unit 90 through the optical fiber 80c.

  The reference light path length changing unit 90 changes the light path length of the reference light LR. The reference light LR guided to the reference light path length changing unit 90 is converted into a parallel light beam by the collimator lens 91 and enters the beam splitter 92. A retinal / anterior chamber depth shutter 93 and a retinal / anterior chamber depth reference mirror unit 94 are provided in the transmission direction of the beam splitter 92, and a corneal shutter 95 and a corneal reference mirror unit 96 are provided in the reflection direction. Have been. The retinal / anterior chamber depth reference mirror unit 94 includes an imaging lens 94A and a retinal / anterior chamber depth reference mirror 94B. The cornea reference mirror unit 96 includes an imaging lens 96A and a cornea reference mirror 96B.

  The reference light LR is split into two light beams (for the retina / anterior chamber depth and for the cornea) by the 50:50 beam splitter 92. The retinal / anterior chamber depth shutter 93 is inserted into the optical path (retinal / anterior chamber depth reference light path) of the retinal / anterior chamber depth light beam between the beam splitter 92 and the retinal / anterior chamber depth reference mirror 94B. It is possible to escape. The corneal shutter 95 can be inserted into and removed from the optical path (corneal reference optical path) of the corneal light beam between the beam splitter 92 and the corneal reference mirror 96B. When the retinal / anterior chamber depth shutter 93 is retracted from the optical path, the retinal / anterior chamber depth luminous flux is imaged on the reflection surface of the retinal / anterior chamber depth reference mirror 94B by the imaging lens 94A. The light is reflected by the reference mirror 94B for anterior chamber depth, passes through the imaging lens 94A, and returns to the beam splitter 92. When the corneal shutter 95 is retracted from the optical path, the corneal light flux is imaged on the reflecting surface of the corneal reference mirror 96B by the imaging lens 96A, is reflected by the corneal reference mirror 96B, and passes through the imaging lens 96A. Then, the process returns to the beam splitter 92.

  On the other hand, the measurement light LS output from the interferometer unit 80 is converted into a parallel light beam by the collimator lens 84. The crystalline lens 89 is inserted into and removed from the optical path of the measurement light LS that has been converted into a parallel light flux. When the crystalline lens 89 is inserted in the optical path, the measuring light LS converted into a parallel light beam is deflected by the optical scanner 87b, passes through the focusing lens 85, the relay lens 86, and the crystalline lens 89, and is deflected by the mirror 87a. Is done. When the lens 89 is retracted from the optical path, the measurement light LS converted into a parallel light beam is deflected by the optical scanner 87b, passes through the focusing lens 85 and the relay lens 86, and is deflected by the mirror 87a. The measurement light LS deflected by the mirror 87a passes through the pupil lens 88, is reflected by the dichroic mirror 52, passes through the objective lens 51, and irradiates the eye E to be inspected. The return light of the measurement light LS from the eye E passes through the objective lens 51 and is guided to the interferometer unit 80 through the same path as the outward path. The optical scanner 87b includes, for example, one or more galvano mirrors, and changes the deflection direction of the measurement light LS under the control of the processing unit 9. The optical scanner 87b is arranged at a position optically conjugate with the pupil.

  The fiber coupler 82 causes the reference light passing through the reference light path length changing unit 90 to interfere with the return light of the measurement light LS. The interference light LC generated thereby is guided to the spectroscope 83 by the optical fiber 80d. The spectroscope 83 spatially separates the wavelength of the interference light LC, and detects these wavelength components with a line sensor. The processing unit 9 extracts information in the depth direction by performing a known signal processing such as FFT (Fast Fourier Transform) on the signal output from the spectroscope 83.

  In this example, the spectral domain OCT is applied, but other types of OCT can be applied. For example, when the swept source OCT is applied, a wavelength sweep light source (tunable light source) is provided instead of the low coherence light source (interferometer light source 81), and light detection such as a balanced photodiode is used instead of the spectroscope 83. A vessel is provided.

  The processing unit 9 can move the retinal / anterior chamber depth reference mirror unit 94 and the cornea reference mirror unit 96 so that the interference signal is arranged at a predetermined position in the depth direction. FIG. 3 shows an example of a change in the depth direction of the intensity of the interference signal obtained by the FFT. In a state where the interference signal SC0 indicated by the dotted line is obtained, the reference mirror unit 94 for retinal / anterior chamber depth is brought close to the beam splitter 92 as shown in FIG. 4 so that the interference signal SC0 falls within a predetermined range shown in FIG. (Corresponding to the retina) can be moved. In other words, by moving the imaging lens 94A and the reference mirror 94B for retinal / anterior chamber depth from the position shown by the dotted line to the position shown by the solid line, the interference signal SC0 can be moved within a desired range.

  By using the position of the corneal vertex detected using the Z alignment system 1, the distance (working distance) of the objective lens 51 to the eye E can be kept constant. Here, when the corneal shutter 95 is retracted from the optical path, an interference signal corresponding to the cornea K is also detected by the spectroscope 83 at the same time. The corneal reference mirror 96B is arranged at a position away from the cornea K by a predetermined distance d so as not to overlap the interference signal SC1 corresponding to the retina (FIG. 5). Thereby, as shown in FIG. 6, both the interference signal SC1 corresponding to the retina and the interference signal SC2 corresponding to the cornea can be obtained simultaneously in the measurement range R in the depth direction.

  As shown in FIG. 6, when the signal sensitivity SC changes in the measurement range R, the interference signal SC1 having a relatively weak signal is detected in the measurement range R1 having a relatively high sensitivity, and the interference signal SC2 having a relatively strong signal is relatively detected. It can be detected in the low-sensitivity measurement range R2. Thereby, the detection accuracy of both interference signals is improved.

  In this embodiment, when measuring the intraocular distance of the eye E, the processing unit 9 moves the retinal / anterior chamber depth reference mirror unit 94 with the corneal reference mirror unit 96 fixed. This makes it possible to measure various intraocular distances of the eye E based on the corneal apex as a reference region. As shown in FIG. 5, when measuring the axial length, the reference mirror unit 94 for retinal / anterior chamber depth is moved so that an interference signal corresponding to the retina can be detected, and the distance between the corneal vertex and the fundus (retina) is measured. Find D1. When measuring the anterior chamber depth, the reference mirror unit 94 for retinal / anterior chamber depth is moved so as to detect an interference signal corresponding to the anterior crystalline lens, and a distance D2 between the apex of the cornea and the anterior crystalline lens is obtained. When measuring the lens thickness, the reference mirror unit 94 for retinal / anterior chamber depth is moved so that an interference signal corresponding to the posterior surface of the lens can be detected, and the distance (D2 + D3) between the vertex of the cornea and the posterior surface of the lens is calculated, and the distance (D2 + D3) is obtained. ) Is subtracted from the distance D2 to obtain the distance D3. When measuring the corneal thickness, an interference signal corresponding to the posterior surface of the cornea is detected to determine the distance between the vertex of the cornea and the posterior surface of the cornea.

(Configuration of information processing system)
The information processing system of the ophthalmologic apparatus 1000 will be described. 7 to 9 show examples of the functional configuration of the information processing system of the ophthalmologic apparatus 1000. FIG. 7 illustrates an example of a functional block diagram of an information processing system of the ophthalmologic apparatus 1000. FIG. 8 illustrates an example of a functional block diagram centered on the focus control unit 111A of FIG. FIG. 9 illustrates an example of a functional block diagram of the arithmetic processing unit 120 in FIG. The processing unit 9 includes a control unit 110 and an arithmetic processing unit 120. Further, the ophthalmologic apparatus 1000 includes a display unit 170, an operation unit 180, and a communication unit 190.

(Control unit 110)
The control unit 110 includes a processor and controls each unit of the ophthalmologic apparatus 1000. The control unit 110 includes a main control unit 111 and a storage unit 112. The main control unit 111 includes a focusing control unit 111A.

  As shown in FIG. 8, the focus control unit 111A controls the movement of the light source 41 and the optotype chart 42 by the movement mechanism 41B by outputting a control signal to the drive unit 41A that drives the movement mechanism 41B. The focus control unit 111A controls the movement of the focusing lens 72 by the movement mechanism 72B by outputting a control signal to the drive unit 72A that drives the movement mechanism 72B. The focus control unit 111A controls the movement of the reflex measurement light source 61 by the movement mechanism 61B by outputting a control signal to the drive unit 61A that drives the movement mechanism 61B. The focus control unit 111A controls the movement of the focusing lens 85 by the movement mechanism 85B by outputting a control signal to the drive unit 85A that drives the movement mechanism 85B.

  Further, the focus control unit 111A controls the insertion and removal of the crystalline lens 89 by the insertion and removal mechanism 89B by outputting a control signal to a driving unit 89A that drives the insertion and removal mechanism 89B. The crystalline lens 89 is an example of a “focus adjustment range changing unit” provided corresponding to the measurement target. The “focus adjustment range changing unit” moves the focus adjustment range of the focusing lens near the measurement target in order to perform high-precision focusing on the measurement target. Specifically, the movement amount of the focusing lens 85 alone is insufficient, and the focus of the intraocular distance measurement system 8 cannot be adjusted to the front surface or the rear surface of the lens. Therefore, when measuring the intraocular distance with respect to the crystalline lens such as the crystalline lens front surface and the crystalline lens rear surface, the focusing control unit 111A inserts the crystalline lens 89 into the optical path of the measurement light LS. Thereby, the focus adjustment range of the focusing lens 85 can be moved to the vicinity of the crystalline lens, and the intraocular distance with respect to the crystalline lens can be measured with high accuracy while focusing on the crystalline lens front surface or the crystalline lens rear surface. .

  The focusing lens 72, the reflex measurement light source 61, the light source 41, and the optotype chart 42 may be moved by a common moving mechanism (for example, the moving mechanism 72B). In this case, the focusing control unit 111A outputs a control signal to a driving unit (for example, the driving unit 72A) that drives the common moving mechanism, so that the focusing lens 72 and the reflex measurement light source using the common moving mechanism are output. 61 is controlled. Similarly, the focusing lens 85 may be moved integrally with the focusing lens 72 and the reflex measurement light source 61.

(Arithmetic processing unit 120)
The arithmetic processing unit 120 calculates, for example, an eye refractive power, an intraocular distance (an axial length, an anterior chamber depth, a lens thickness, a corneal thickness, etc.), an IOL power calculation, and an optical interference measurement image (OCT image). Performs various calculations, such as generation and analysis of optical interference measurement images. The arithmetic processing unit 120 includes an eye refractive power calculation unit 121, an intraocular distance calculation unit 122, and an IOL frequency calculation unit 123. The intraocular distance calculator 122 includes an axial length calculator 122A, an anterior chamber depth calculator 122B, a lens thickness calculator 122C, and a corneal thickness calculator 122D.

  In calculating the eye refractive power, the eye refractive power calculation unit 121 analyzes the shape of the output (ring image) from the reflex measurement light receiving system 7. For example, the eye-refractive-power calculating unit 121 obtains the position of the center of gravity of the ring image from the luminance distribution in the obtained image, obtains the luminance distribution along a plurality of scanning directions extending radially from the position of the center of gravity, and obtains the ring from this luminance distribution. Identify the image. Subsequently, the eye-refractive-power calculating unit 121 obtains an approximate ellipse of the specified ring image, and substitutes the major axis and the minor axis of the approximate ellipse into a known equation to obtain a spherical power S, an astigmatic power C, and an astigmatic axis angle. Ask for A. Alternatively, the eye-refractive-power calculating unit 121 can obtain the parameters of the eye-refractive power based on the deformation and displacement of the ring image with respect to the reference pattern.

  The eye refractive power calculation unit 121 can obtain at least the spherical power from the optical interference measurement result using the intraocular distance measurement system 8. For example, the eye-refractive-power calculating unit 121 specifies the position of the focusing lens 85 at which the detection signal of the interference light LC peaks due to the movement of the focusing lens 85, and specifies the position of the focusing lens corresponding to 0D. The equivalent spherical power is calculated based on the position of the focusing lens 85 at which the peak is reached.

  The eye refractive power calculation unit 121 calculates a corneal refractive power, a corneal astigmatism degree, and a corneal astigmatism axis angle based on the kerattling image acquired by the observation system 5. For example, the eye-refractive-power calculating unit 121 calculates a corneal curvature radius of a strong principal meridian or a weak principal meridian of the anterior cornea by analyzing a kerattling image, and calculates the above parameters based on the corneal curvature radius.

  The intraocular distance calculation unit 122 calculates one or more intraocular distances of the eye E based on the two interference light detection data acquired by the intraocular distance measurement system 8. The intraocular distance calculator 122 calculates the intraocular distance of the eye E based on the interval between the positions of two interference signals (for example, see FIG. 6) based on the two interference lights included in the detection data. The intraocular distance calculator 122 can calculate a plurality of intraocular distances of the eye E while inserting and removing the crystalline lens 89. The intraocular distance calculation unit 122 calculates an axial length and a corneal thickness (first intraocular distance) based on the detection data acquired in a state where the crystalline lens 89 is retracted from the optical path. Further, the intraocular distance calculation unit 122 calculates the anterior chamber depth and the lens thickness (second intraocular distance) based on the detection data obtained in a state where the lens lens 89 is inserted in the optical path. The crystalline lens may have a focal length combined with an existing lens (eg, a relay lens 86), which may be interchangeable with the relay lens 86.

  The intraocular distance calculation unit 122 can calculate a plurality of intraocular distances based on the reference region of the eye E to be examined. As the reference portion, a portion where the intensity of the return light of the measurement light LS from the eye E to be inspected is high is exemplified. The reference site includes the corneal vertex (front surface of the cornea) of the eye E, the retina, the inner limiting membrane, and the like. Thereby, even when the eye E moves and the position of the interference signal changes, it is possible to always calculate a plurality of intraocular distances with high accuracy by always using the interference signal of the reference part as a reference. it can.

  The axial length calculator 122A determines the axial length (intraocular distance D1) based on the interval between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the retina. The anterior chamber depth calculation unit 122B calculates the anterior chamber depth (intraocular distance D2) based on the interval between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the anterior lens surface. As the position of the interference signal corresponding to the corneal vertex when obtaining the anterior chamber depth, the position of the interference signal corresponding to the corneal vertex used when obtaining the axial length can be used. The lens thickness calculation unit 122C calculates the distance (D2 + D3) based on the distance between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the posterior surface of the lens, and calculates the distance D2 from the calculated distance (D2 + D3). The lens thickness (distance D3) is obtained by subtraction. The corneal thickness calculating unit 122D calculates the corneal thickness based on the interval between the position of the interference signal corresponding to the vertex of the cornea (front surface of the cornea) and the position of the interference signal corresponding to the posterior surface of the cornea.

  In the calculation of the IOL power, the IOL power calculation unit 123 calculates the kerato measurement result and at least one of the axial length, the anterior chamber depth, the lens thickness, and the corneal thickness obtained in the intraocular distance calculation unit 122 by a known calculation formula. To find the IOL frequency. Note that the IOL power calculation unit 123 may obtain the IOL power by substituting the calculation result of the eye refractive power and the calculation result of the axial length into a known calculation formula.

(Display unit 170, operation unit 180)
The display unit 170 displays information under the control of the control unit 110. The display unit 170 includes the display unit 10. The operation unit 180 is used for operating the ophthalmologic apparatus 1000 and inputting information. The operation unit 180 includes various hardware keys (joysticks, buttons, switches, and the like) and / or various software keys (buttons, icons, menus, and the like) presented on the display unit 170.

(Communication unit 190)
The communication unit 190 has a function of communicating with an external device. The communication unit 190 includes a communication interface according to a connection mode with an external device. As an example of the external device, there is a spectacle lens measuring device for measuring optical characteristics of a lens. The spectacle lens measuring device measures the power of the spectacle lens worn by the subject, and inputs the measurement data to the ophthalmologic apparatus 1000. The external device may be any ophthalmic device, a device (reader) for reading information from a recording medium, or a device (writer) for writing information on a recording medium. Further, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like.

  The interferometer unit 80 is an example of the “interference optical system” according to the embodiment. The interferometer light source 81 is an example of the “first light source” according to the embodiment. The focusing lens 85 is an example of the “first focusing lens” according to the embodiment. The crystalline lens 89 is an example of the “second focusing lens” according to the embodiment. The focusing lens 72 is an example of the “third focusing lens” according to the embodiment. The beam splitter 92 is an example of the “optical path dividing member” according to the embodiment. The retinal / anterior chamber reference mirror unit 94, its moving mechanism, and its driving unit are an example of the “optical path length changing unit” according to the embodiment. The reflex measurement projection system 6, the reflex measurement light receiving system 7, and the eye refractive power calculation unit 121 are examples of the “refractive power measurement unit” according to the embodiment. The reflex measurement light source 61 is an example of the “second light source” according to the embodiment.

<Operation example>
An operation of the ophthalmologic apparatus 1000 according to the embodiment will be described. An example of the operation of the ophthalmologic apparatus 1000 is shown in FIGS. FIG. 10 is a flowchart illustrating an operation example of the ophthalmologic apparatus 1000. FIG. 11 shows a flowchart of an operation example of the measurement of the axial length in S4 of FIG. FIG. 12 shows a flowchart of an operation example of the anterior chamber depth measurement in S5 of FIG. FIG. 13 shows a flowchart of an operation example of the lens thickness measurement in S6 of FIG. FIG. 14 shows a flowchart of an operation example of the corneal thickness measurement in S7 of FIG.

(S1)
When the examiner performs a predetermined operation on the operation unit 180 in a state where the subject's face is fixed to a face receiving unit (not shown), the ophthalmologic apparatus 1000 executes the alignment. Specifically, the main control unit 111 turns on the Z alignment light source 11, the XY alignment light source 21, and the light source 41. The processing unit 9 acquires an imaging signal of the anterior ocular segment image formed on the imaging surface of the imaging element 59, and causes the display unit 170 (the display screen 10a of the display unit 10) to display the anterior ocular segment image E '. . Thereafter, the optical system shown in FIG. The inspection position is a position where the eye E can be inspected. The subject's eye E is arranged at the inspection position via the above-described alignment (alignment by the Z alignment system 1 and the XY alignment system 2 and the observation system 5). The movement of the optical system is executed by the control unit 110 in accordance with an operation or instruction by a user or an instruction by the control unit 110. That is, movement of the optical system to the examination position of the eye E and preparation for performing objective measurement are performed.

  In addition, the main control unit 111 moves the reflex measurement light source 61 and the focusing lens 72, the focusing lens 85, the light source 41, and the optotype chart 42 in conjunction with each other, and moves to the origin, for example, the position of 0D along the optical axis. .

(S2)
The main control unit 111 causes kerato measurement to be performed. That is, the main control unit 111 turns on the kerattling light source 32. When light is output from the kerat ring light source 32, a ring-shaped light beam for measuring a corneal shape is projected on the cornea K. The eye-refractive-power calculating unit 121 calculates a corneal curvature radius by performing an arithmetic process on the image acquired by the imaging element 59, and calculates corneal refractive power, corneal astigmatism, and corneal astigmatism from the calculated corneal curvature radius. Calculate the shaft angle. In the control unit 110, the calculated corneal refractive power and the like are stored in the storage unit 112. The operation of the ophthalmologic apparatus 1000 shifts to S3 in response to an instruction from the main control unit 111 or a user operation or instruction to the operation unit 180.

(S3)
The main control unit 111 arranges the reflection surface of the quick return mirror 67 on the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52, and executes the reflex measurement. That is, the main control unit 111 projects the ring-shaped measurement pattern light beam for reflex measurement to the eye E as described above. A ring image based on the return light of the measurement pattern light beam from the eye E is formed on the image plane of the image sensor 74. The main control unit 111 determines whether a ring image based on the return light from the fundus oculi Ef detected by the imaging element 74 has been obtained. For example, the main control unit 111 detects the position (pixel) of the edge of the image based on the return light detected by the image sensor 74, and determines whether the width of the image (difference between the outer diameter and the inner diameter) is equal to or greater than a predetermined value. It is determined whether or not a ring image has been obtained by determining whether or not a ring can be formed based on a point (image) whose intensity is equal to or higher than a predetermined height.

  When it is determined that the ring image has been obtained, the eye-refractive-power calculating unit 121 analyzes the ring image based on the return light of the measurement pattern light beam projected on the eye E by a known method, and calculates the provisional spherical power S and The astigmatic power C is obtained. Based on the provisional spherical power and astigmatic power C, the reflex measurement light source 61, the focusing lens 72 (focusing lens 85), the light source 41 and the optotype chart 42 are moved to the positions of the equivalent spherical power (S + C / 2). After performing fog from that position, a ring image is acquired again as the main measurement, and the spherical power S, the astigmatic power C, and the astigmatic axis are obtained from the analysis result of the ring image obtained in the same manner as described above and the movement amount of the focusing lens. The angle A is determined. In the control unit 110, the position of the focusing lens 72 (the focusing lens 85), the calculated spherical power, and the like are stored in the storage unit 112. The operation of the ophthalmologic apparatus 1000 shifts to S4 in response to an instruction from the main control unit 111 or a user operation or instruction to the operation unit 180.

  When it is determined that a ring image cannot be obtained, first, the reflex measurement light source 61 and the focusing lens 72 are set in advance in the minus power side (for example, −10D) and the plus power in consideration of the possibility that the eye is an abnormally refractive eye. Move to the side (for example, + 10D), and detect a ring image at each position. If it is still determined that the ring image cannot be obtained, the operation of the ophthalmologic apparatus 1000 proceeds to S4. In the control unit 110, information indicating that the reflex measurement result was not obtained is stored in the storage unit 112.

(S4)
The main control unit 111 causes the reflecting surface of the quick return mirror 67 to retreat from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52, and executes the measurement of the axial length. In the measurement of the axial length, the crystalline lens 89 is retracted from the optical path of the measurement light LS. In the control unit 110, the calculated ocular axial length is stored in the storage unit 112. Details of the measurement of the axial length will be described later. The operation of the ophthalmologic apparatus 1000 proceeds to S5.

(S5)
The main control unit 111 executes anterior chamber depth measurement. In the anterior chamber depth measurement, a crystalline lens 89 is inserted in the optical path of the measurement light LS. In the control unit 110, the calculated anterior chamber depth is stored in the storage unit 112. Details of the anterior chamber depth measurement will be described later. The operation of the ophthalmologic apparatus 1000 proceeds to S6.

(S6)
The main control unit 111 executes the lens thickness measurement. In the lens thickness measurement, a lens 89 is inserted in the optical path of the measurement light LS. In the control unit 110, the calculated lens thickness is stored in the storage unit 112. Details of the lens thickness measurement will be described later. The operation of the ophthalmologic apparatus 1000 proceeds to S7.

(S7)
The main control unit 111 causes the corneal thickness measurement to be performed. In the corneal thickness measurement, the crystalline lens 89 is retracted from the optical path of the measurement light LS. In the control unit 110, the calculated corneal thickness is stored in the storage unit 112. Details of the corneal thickness measurement will be described later. The operation of the ophthalmologic apparatus 1000 proceeds to S8.

(S8)
The IOL power calculating unit 123 obtains the IOL power using at least one of the corneal refractive power (kerat value), eye axial length measurement, anterior chamber depth, crystalline lens thickness, and corneal thickness obtained in S1 to S7. In the control unit 110, the obtained IOL frequency is stored in the storage unit 112.

(S9)
The control unit 110 controls the optotype chart 42 based on a user's instruction to the operation unit 180 to display a desired optotype. Further, the control unit 110 moves the light source 41 and the optotype chart 42 to a position corresponding to the result of the objective measurement. The subject responds to the target projected on the fundus oculi Ef. For example, in the case of a visual target for measuring visual acuity, the visual acuity value of the subject's eye is determined based on the response of the subject. The selection of the target and the response of the subject to the target are repeatedly performed based on the judgment of the examiner or the control unit 110.

  Alternatively, the control unit 110 controls the VCC lens 44 based on the astigmatic state (astigmatic power and astigmatic axis angle) of the eye E obtained by the objective measurement so that the astigmatic state is corrected. The subject responds to the target projected on the fundus oculi Ef. It is also possible to control the VCC lens based on the response of the subject. For example, in the case of a visual target for measuring visual acuity, the visual acuity value of the subject's eye is determined based on the response of the subject. The selection of the target and the response of the subject to the target are repeatedly performed based on the judgment of the examiner or the control unit 110. The examiner or the control unit 110 determines the visual acuity value or the prescription value (S, C, A) based on the response from the subject, and the operation of the ophthalmologic apparatus 1000 ends (end).

  Next, the flow of the axial length measurement in S4 of FIG. 10 shown in FIG. 11 will be described.

(S11)
The main controller 111 turns on the interferometer light source 81.

(S12)
The main control unit 111 causes the corneal shutter 95 to be inserted into the corneal reference optical path.

(S13)
The main control unit 111 retracts the retinal / anterior chamber depth shutter 93 from the retinal / anterior chamber depth reference optical path.

(S14)
The main control unit 111 retracts the reflection surface of the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Accordingly, an optical path of the measurement light LS is formed between the interferometer unit 80 and the eye E, and the optical interference measurement path is opened.

(S15)
The main control unit 111 determines whether there is a reflex measurement result based on the information stored in the storage unit 112 in S3 of FIG. When it is determined that there is a reflex measurement result (S15: Y), the operation of the ophthalmologic apparatus 1000 proceeds to S16. When it is determined that there is no reflex measurement result (S15: N), the operation of the ophthalmologic apparatus 1000 proceeds to S18.

(S16)
When it is determined that there is a reflex measurement result (S15: Y), the focusing control unit 111A performs measurement of the axial length from the position of the focusing lens 72 (focusing lens 85) stored in the storage unit 112 in S3. Is determined, and the focusing lens 85 is moved to the determined position. That is, in the measurement of the axial length in S4, the position of the focusing lens 85 is determined from the position of the focusing lens 72 obtained in focusing on the eye E to perform the reflex measurement in S3. Specifically, since the reflex measurement is performed in a state where the eye to be inspected E is fogged, during the reflex measurement, the lens moves by a predetermined distance ΔD from the position of the focusing lens 72 obtained in focusing on the eye to be inspected E. Is done. Therefore, the position of the focusing lens 85 moved in S16 is a position moved by a distance (-ΔD) from the position of the focusing lens 85 (focusing lens 72) at the time of reflex measurement. The moving part of the reflex measurement system (the reflex measurement light source 61 and the focusing lens 72) and the focusing lens 85 of the intraocular distance measurement system 8 may be integrally movable or may be individually movable. . When moving together, the focusing lens 85 is already at the cloud fog position at the time of reflex measurement in S3, so that only the cloud fog needs to be returned. If they are moved individually, or if they are integrated and have different reference positions or magnifications, they move as described above.

(S17)
The main control unit 111 moves the retinal / anterior chamber depth reference mirror unit 94 so that the position of the interference signal corresponding to the retina becomes a predetermined position.

(S18)
When it is determined that there is no reflex measurement result (S15: N), the main control unit 111 moves the retinal / anterior chamber depth reference mirror unit 94 such that the position of the interference signal corresponding to the retina becomes a predetermined position. I do.

(S19)
The focus control unit 111A moves the focus lens 85 so that the intensity of the interference signal corresponding to the retina becomes highest.

  As described above, when there is a reflex measurement result (that is, when the position of the focusing lens 85 is known), the focusing state is set first (S16), so that the interference signal corresponding to the retina can be detected. It will be easier. On the other hand, when there is no reflex measurement result (that is, when the position of the focusing lens 85 is unknown), focusing on the retina is enabled by first detecting an interference signal corresponding to the retina. .

(S20)
The main control unit 111 retracts the corneal shutter 95 from the corneal reference optical path. This makes it possible to simultaneously detect an interference signal corresponding to a corneal vertex and an interference signal corresponding to a retina (see FIG. 6).

(S21)
The axial length calculation unit 122A calculates the axial length based on the distance between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the retina, which can be simultaneously detected in S20. Thus, the flow of the axial length measurement is completed (end).

  As described above, the eye axis length is calculated using the interval between the positions of two interference signals included in the detection data acquired in a state where the retina is focused not on the corneal vertex where the reflection intensity of the return light of the measurement light LS is strong. Is required. This makes it possible to determine the axial length with high accuracy.

  Next, the flow of the anterior chamber depth measurement in S5 of FIG. 10 shown in FIG. 12 will be described.

(S31)
The main controller 111 turns on the interferometer light source 81.

(S32)
The main control unit 111 causes the corneal shutter 95 to be inserted into the corneal reference optical path.

(S33)
The main control unit 111 retracts the retinal / anterior chamber depth shutter 93 from the retinal / anterior chamber depth reference optical path.

(S34)
The main control unit 111 retracts the reflection surface of the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Thereby, the optical interference measurement path is opened. When the optical interference measurement path is already open, S34 is unnecessary.

(S35)
The focusing control unit 111A causes the crystalline lens 89 to be inserted into the optical path (optical interference measurement path) of the measurement light LS. When the crystalline lens 89 is inserted, the position of the focusing lens moves to a predetermined position. Thereby, the focus adjustment range of the focusing lens 85 moves from the vicinity of the retina (fundus) to the vicinity of the crystalline lens.

(S36)
The main controller 111 moves the retinal / anterior chamber depth reference mirror unit 94 such that the position of the interference signal corresponding to the front surface of the crystalline lens becomes a predetermined position.

(S37)
The focusing control unit 111A moves the focusing lens 85 so that the intensity of the interference signal corresponding to the front surface of the crystalline lens becomes the highest.

(S38)
The main control unit 111 retracts the corneal shutter 95 from the corneal reference optical path. This makes it possible to simultaneously detect an interference signal corresponding to the corneal vertex and an interference signal corresponding to the front surface of the crystalline lens.

(S39)
The anterior chamber depth calculation unit 122B calculates the anterior chamber depth based on the interval between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the front surface of the crystalline lens, which can be simultaneously detected in S38. Thus, the flow of the anterior chamber depth measurement ends (end).

  As described above, the focus adjustment range due to the movement of the focusing lens 85 is moved to the vicinity of the crystalline lens, and the positions of two interference signals included in the detection data acquired in a state where the focusing lens 85 is focused not on the corneal vertex but on the anterior crystalline lens. Is used to determine the anterior chamber depth. Thereby, it becomes possible to obtain the anterior chamber depth with high accuracy.

  Next, the flow of the lens thickness measurement in S6 of FIG. 10 shown in FIG. 13 will be described.

(S41)
The main controller 111 turns on the interferometer light source 81.

(S42)
The main control unit 111 causes the corneal shutter 95 to be inserted into the corneal reference optical path.

(S43)
The main control unit 111 retracts the retinal / anterior chamber depth shutter 93 from the retinal / anterior chamber depth reference optical path.

(S44)
The main control unit 111 retracts the reflection surface of the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Thereby, the optical interference measurement path is opened. When the optical interference measurement path is already open, S44 is unnecessary.

(S45)
The focusing control unit 111A causes the crystalline lens 89 to be inserted into the optical path (optical interference measurement path) of the measurement light LS. When the crystalline lens 89 has already been inserted into the optical path, S45 is unnecessary.

(S46)
The main controller 111 moves the retinal / anterior chamber depth reference mirror unit 94 so that the position of the interference signal corresponding to the posterior surface of the lens becomes a predetermined position.

(S47)
The focusing control unit 111A moves the focusing lens 85 so that the intensity of the interference signal corresponding to the rear surface of the crystalline lens becomes the highest.

(S48)
The main control unit 111 retracts the corneal shutter 95 from the corneal reference optical path. This makes it possible to simultaneously detect an interference signal corresponding to the corneal vertex and an interference signal corresponding to the posterior surface of the crystalline lens.

(S49)
The lens thickness calculating unit 122C calculates the distance between the corneal vertex and the posterior surface of the lens based on the interval between the position of the interference signal corresponding to the corneal vertex and the position of the interference signal corresponding to the posterior surface of the lens, which can be simultaneously detected in S48. Ask.

(S50)
The lens thickness calculator 122C calculates the lens thickness by subtracting the anterior chamber depth determined in S39 from the distance between the corneal vertex and the posterior surface of the lens determined in S49. This is the end of the lens thickness measurement flow (end).

  As described above, the focus adjustment range by the movement of the focusing lens 85 is moved to the vicinity of the crystalline lens, and the positions of the two interference signals included in the detection data acquired in a state where the focusing lens 85 is focused not on the corneal vertex but on the posterior surface of the crystalline lens The lens thickness is determined using the interval of. Thereby, it becomes possible to obtain the thickness of the crystalline lens with high accuracy.

  Next, the flow of corneal thickness measurement in S7 of FIG. 10 shown in FIG. 14 will be described.

(S61)
The main controller 111 turns on the interferometer light source 81.

(S62)
The main control unit 111 retracts the corneal shutter 95 from the corneal reference optical path.

(S63)
The main controller 111 causes the retinal / anterior chamber depth shutter 93 to be inserted into the retinal / anterior chamber depth reference optical path.

(S64)
The main control unit 111 retracts the reflection surface of the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Thereby, the optical interference measurement path is opened. When the optical interference measurement path is already open, S64 is unnecessary.

(S65)
The focusing control unit 111A retracts the crystalline lens 89 from the optical path of the measurement light LS.

(S66)
The main control unit 111 moves the focusing lens 85 so that the intensity of the interference signal corresponding to the posterior surface of the cornea becomes highest.

(S67)
Since the interference signal corresponding to the corneal vertex and the interference signal corresponding to the posterior corneal surface can be simultaneously detected, the corneal thickness calculating unit 122D determines the position of the interference signal corresponding to the corneal vertex and the interference corresponding to the posterior corneal surface. The corneal thickness is calculated based on the distance from the position of the signal. This is the end of the flow of the corneal thickness measurement (end).

  As described above, the corneal thickness is obtained using the interval between the positions of the two interference signals included in the detection data acquired in a state where the corneal vertex is focused on the posterior surface of the cornea instead of the apex. As a result, the corneal thickness can be determined with high accuracy.

  As described above, the ophthalmologic apparatus 1000 according to the embodiment measures a plurality of intraocular distances of the eye E while inserting and removing the crystalline lens 89.

[Action / Effect]
The operation and effect of the ophthalmologic apparatus 1000 according to the embodiment will be described.

  The ophthalmologic apparatus according to the embodiment includes an interference optical system (for example, the interferometer unit 80), a first focusing lens (for example, the focusing lens 85), a second focusing lens (for example, the crystalline lens 89), and focusing control. (For example, a focus control unit 111A) and an intraocular distance calculation unit (for example, an intraocular distance calculation unit 122). The interference optical system divides light (light L0) from the first light source (interferometer light source 81) into reference light (reference light LR) and measurement light (measurement light LS), and divides the measurement light into an eye to be inspected (eye to be inspected). E) to generate interference light (interference light LC) between the return light and the reference light, and detect the generated interference light. The first focusing lens is movable along the optical path of the measurement light. The second focusing lens can be inserted into and removed from the optical path of the measurement light. The focusing control unit controls at least movement of the first focusing lens. The intraocular distance calculation unit is configured to perform a first intraocular distance (for example, an axial length, a cornea, etc.) based on first detection data of interference light acquired by the interference optical system in a state where the second focusing lens is retracted from the optical path. Thickness), and a second intraocular distance (eg, anterior chamber depth, lens thickness) based on the second detection data of the interference light acquired by the interference optical system in a state where the second focusing lens is inserted in the optical path. Ask for.

  According to such a configuration, the intraocular distance is obtained by inserting and removing the second focusing lens with respect to the optical path of the measurement light generated by the interference optical system. Can be set short, and it is possible to obtain an interference signal in a state where the retina and the vicinity of the front and rear surfaces of the lens are focused respectively, so that a signal with a high S / N ratio can be obtained. Thus, the intraocular distance can be obtained with high accuracy, and the IOL frequency can be obtained with high accuracy based on the obtained intraocular distance.

  Further, in the ophthalmologic apparatus according to the embodiment, the intraocular distance calculation unit determines a position of a signal corresponding to a reference part (for example, a corneal vertex (front surface of the cornea)) included in the first detection data and another first part (for example, the retina). The first intraocular distance is obtained based on the position of the signal corresponding to the posterior corneal surface, and the position of the signal corresponding to the reference region included in the second detection data and another second region (for example, the front surface of the lens, the posterior surface of the lens) ) May be obtained based on the position of the signal corresponding to (2).

  According to such a configuration, even when the eye to be examined has moved and the position of the interference signal has changed, a plurality of intraocular distances can always be obtained with high accuracy by always using the interference signal of the reference portion as a reference. Can be calculated.

  In the ophthalmologic apparatus according to the embodiment, the reference site may be the anterior cornea or the retina.

  According to such a configuration, the intraocular distance of the eye to be inspected can be obtained based on a portion where the reflection intensity of the return light of the measurement light is high, so that highly accurate measurement is possible.

  In the ophthalmologic apparatus according to the embodiment, the focusing control unit controls the first focusing lens based on a signal corresponding to the first part before the first detection data is obtained, and the second detection data is Before the acquisition, the first focusing lens may be controlled based on a signal corresponding to the second portion.

  According to such a configuration, it is possible to control the first focusing lens so as to focus on each of the first portion and the second portion, so that the signal corresponding to the first portion and the second portion The detection accuracy of the corresponding signal can be improved.

  In the ophthalmologic apparatus according to the embodiment, the interference optical system includes an optical path splitting member (for example, a beam splitter 92) and an optical path length changing unit (for example, a reference mirror unit 94 for retinal / anterior chamber depth, its moving mechanism and its driving unit). And different reference optical path lengths may be applied when the first detection data is obtained and when the second detection data is obtained. The optical path dividing member divides the optical path of the reference light to form at least a first reference optical path (for example, a corneal reference optical path) and a second reference optical path (for example, a retinal / anterior chamber depth reference optical path). The optical path length changing unit changes the length of the second reference optical path.

  According to such a configuration, for example, the first detection data and the second detection data are obtained by changing the length of the second reference light path while the length of the first reference light path is fixed. In addition, it is possible to measure a plurality of intraocular distances of the subject's eye without increasing the number of moving mechanisms.

  Further, the ophthalmologic apparatus according to the embodiment may include a refractive power measurement unit (for example, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an eye refractive power calculation unit 121). The refractive power measurement unit irradiates light from a second light source (for example, the reflex measurement light source 61) to the subject's eye, and moves a third focusing lens (for example, the focusing lens 72) movable along the optical path of the return light. The refractive power of the subject's eye is measured by detecting the return light through the eye. The focusing control unit controls the movement of the first focusing lens based on the position of the third focusing lens obtained in focusing on the subject's eye for measuring the refractive power.

  According to such a configuration, since the position of the first focusing lens can be obtained from the position of the third focusing lens obtained by the measurement by the refractive power measurement unit, it is necessary to measure the intraocular distance of the subject's eye. The measurement control including the focus control of (1) can be simplified.

<Modification>
The above-described embodiment or its modification is merely an example for embodying the present invention. Those who intend to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the present invention.

  In the above-described embodiment, a case has been described in which the lens lens 89 is provided to move the focus adjustment range near the crystalline lens. However, a plurality of focus adjustment range changing units corresponding to a plurality of measurement targets in the eye are described. (For example, a lens or the like) may be provided.

  In the above-described embodiment, the case where the crystalline lens 89 is inserted and removed between the focusing lens 85 and the relay lens 86 has been described. However, the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. The crystalline lens can be inserted and removed at any position in the optical path of the measurement light.

Reference Signs List 1 Z alignment system 2 XY alignment system 3 Kerato measurement system 4 Target projection system 5 Observation system 6 Ref measurement projection system 7 Ref measurement light receiving system 8 Intraocular distance measurement system 9 Processing units 72, 85 Focusing lens 80 Interferometer unit 89 Lens lens 111A Focus control unit 122 Intraocular distance calculation unit 1000 Ophthalmic apparatus

Claims (5)

Dividing light from the first light source into reference light and measurement light, irradiating the measurement light to the subject's eye, generating interference light between the returned light and the reference light, and detecting the generated interference light Interference optics,
A first focusing lens movable along an optical path of the measurement light;
A second focusing lens that can be inserted into and removed from the optical path of the measurement light;
A focusing control unit that performs at least movement control of the first focusing lens;
In a state where the second focusing lens is retracted from the optical path, a first intraocular distance is obtained based on first detection data of the interference light obtained by the interference optical system, and the second focusing lens is An intraocular distance calculation unit that obtains a second intraocular distance based on second detection data of the interference light acquired by the interference optical system while being inserted into the optical path,
Including
Before the first detection data is acquired, the focus control unit, said to be a position corresponding to the measurement result of the refractive power of the eye, or the you corresponds to the first region to be examined the intensity of the interference signal corresponding to the interference light is controlled becomes highest due urchin said first focusing lens,
Before the second detection data is acquired, the focus control unit, the intensity of the interference signal corresponding to the interference light you corresponds to the second site in different the subject's eye and the first portion is the highest I control the urchin said first focusing lens, the ophthalmic device. The intraocular distance calculator,
Seeking the first intraocular distance based on the position of the signal corresponding to the first site contained in the position of the corresponding signal the first detection data to the reference position included in the first detection data,
To seek the second intraocular distance based on the position of the signal corresponding to the second site contained in the second detection data and the position of the signal corresponding to the reference site contained in the second detection data The ophthalmic apparatus according to claim 1, wherein: The ophthalmologic apparatus according to claim 2, wherein the reference part is an anterior cornea or a retina. The interference optical system includes:
An optical path dividing member that divides an optical path of the reference light to form at least a first reference optical path and a second reference optical path;
A reference light path length changing unit that changes the length of the second reference light path;
Including
By changing the length of the second reference light path by the reference light path length changing unit, the length of the reference light path different from each other when the first detection data is obtained and when the second detection data is obtained. The ophthalmologic apparatus according to any one of claims 1 to 3, wherein The refraction power of the eye is measured by irradiating the eye to be inspected with light from a second light source and detecting the return light through a third focusing lens movable along the optical path of the return light. Including a refractive power measurement unit,
The focus control unit controls the movement of the first focus lens based on the position of the third focus lens obtained in focusing on the eye to be measured for measuring the refractive power. The ophthalmologic apparatus according to any one of claims 1 to 4, wherein

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