microscope

Abstract

To provide a microscope that is reduced in a size and cost and can reduce labor of an operator (inspector).SOLUTION: A microscope comprises an objective lens (second objective lens 508), a first irradiation optical system (patterning optical system 600) that irradiates a patient eye E with first light (aiming light LG) through the objective lens, a scanning optical system (light scanner 503) that scans the first light emitted from the first irradiation optical system to the patient eye E to generate a measurement pattern (ring pattern LP), and observation optical systems (observation optical systems 40L and 40R) that guide first return light (return light LA) from the patient eye irradiated with the measurement pattern to at least one of an imaging element and an ocular lens through the objective lens.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to a microscope used for observing a patient's eye (eye to be examined). [Background technology]

[0002] In cataract surgery, the cloudy lens is removed from the patient's eye and an intraocular lens (IOL) is inserted into the patient's eye to replace it. A toric IOL, which can correct astigmatism, is known as an intraocular lens. Note that the term "patient" includes the examinee, and the term "patient eye" includes the examinee's eye.

[0003] To maximize the corrective effect of a toric IOL when the patient has astigmatism, it is necessary to align the direction of the patient's corneal maximal meridian with the direction of the toric IOL's inferior meridian as closely as possible. When the patient is standing, sitting, or lying supine, the patient's eye rotates, causing the direction of the patient's superior meridian (also called the astigmatic axis direction (also called the astigmatic axis angle)). Therefore, measuring the direction of the patient's superior meridian is extremely important during cataract surgery using a toric IOL. Therefore, cataract surgery using a toric IOL is performed using a surgical microscope capable of measuring the direction of the patient's superior meridian.

[0004] Patent Documents 1 and 2 describe a surgical microscope equipped with a keratinizing light source disposed between an objective lens and a patient's eye and having a plurality of point light sources arranged in a ring shape, and an imaging optical system having an image sensor. This surgical microscope irradiates a ring pattern (measurement pattern) onto the cornea of ​​the patient's eye from the keratinizing light source, and captures an image of the cornea with a camera. The surgical microscope then calculates the direction of the maximal meridian of the patient's eye based on the observation image of the cornea captured by the camera, and notifies the surgeon of the direction of the maximal meridian of the patient's eye by, for example, blinking a point light source corresponding to the maximal meridian direction. [Prior art documents] [Patent documents]

[0005] [Patent Document 1] Japanese Patent Application Laid-Open No. 2012-152454 [Patent Document 2] Japanese Patent Application Laid-Open No. 2013-27536 Summary of the Invention [Problem to be solved by the invention]

[0006] However, with the surgical microscopes described in the above patent documents, when measuring the inferior meridian direction of the patient's eye, a keratinizing light source must be placed between the objective lens and the patient's eye, and the keratinizing light source must be retracted from between the objective lens and the patient's eye when measuring other than the inferior meridian direction. Therefore, the surgical microscopes described in the above patent documents require an insertion / removal mechanism for inserting and removing the keratinizing light source between the objective lens and the patient's eye, which increases the size and cost of the surgical microscope. Furthermore, the surgical microscopes described in the above patent documents also have the problem that it is time-consuming for the surgeon to insert and remove the keratinizing light source.

[0007] The present invention has been made in view of the above circumstances, and has as its object to provide a microscope that is small in size, low in cost, and can reduce the burden on the operator (examiner). [Means for solving the problem]

[0008] A microscope for achieving the object of the present invention comprises an objective lens, a first illumination optical system that illuminates a patient's eye with first light through the objective lens, a scanning optical system that scans the first light illuminated onto the patient's eye by the first illumination optical system to generate a measurement pattern, and an observation optical system that guides the first return light from the patient's eye illuminated with the measurement pattern through the objective lens to at least one of an image sensor and an eyepiece lens.

[0009] According to this microscope, it is not necessary to provide a keratinizing light source and a reflector light source unit in the microscope.

[0010] In a microscope according to another aspect of the present invention, when the observation optical system guides the first returned light to the image sensor, the microscope further includes an ocular characteristic calculation unit that calculates the ocular characteristics of the patient's eye based on an image of the first returned light captured by the image sensor, thereby making it possible to measure the ocular characteristics of the patient's eye without providing a keratinizing light source and a reflector light source unit in the microscope.

[0011] In a microscope according to another aspect of the present invention, a first irradiation optical system irradiates a cornea of ​​a patient's eye with a first light through an objective lens, a scanning optical system forms a continuous or intermittent ring pattern on the cornea as a measurement pattern, and an eye characteristic calculation unit calculates the corneal shape of the patient's eye as the eye characteristic. This makes it possible to measure the corneal shape of the patient's eye without providing a keratinizing light source in the microscope.

[0012] In a microscope according to another aspect of the present invention, the scanning optical system changes the ring diameter of the ring pattern multiple times, and each time the scanning optical system changes the ring diameter, the image sensor repeatedly captures the first returned light, and the ocular characteristic calculation unit calculates the corneal shape based on the captured images for each of the different ring diameters. This makes it possible to measure the corneal shape of the patient's eye with high accuracy.

[0013] In a microscope according to another aspect of the present invention, an ocular characteristic calculation unit calculates the direction of the maximal meridian of the patient's eye as the corneal shape, and a scanning optical system scans the first light to be irradiated onto the cornea based on the calculation result of the maximal meridian direction by the ocular characteristic calculation unit, thereby forming a guide pattern on the cornea indicating the maximal meridian direction, thereby making it possible to present the maximal meridian direction of the cornea to the surgeon.

[0014] In a microscope according to another aspect of the present invention, the first irradiation optical system includes a front lens removably disposed between the objective lens and the patient's eye, and irradiates the fundus of the patient's eye with first light through the objective lens and the front lens, the scanning optical system generates a continuous or intermittent ring pattern as the measurement pattern, and the ocular characteristic calculation unit calculates the ocular refractive power of the patient's eye as the ocular characteristic. This makes it possible to measure the ocular refractive power of the patient's eye without providing a reflector light source unit in the microscope.

[0015] In a microscope according to another aspect of the present invention, a second irradiation optical system is provided that irradiates a patient's eye with a second light different from the first light through an objective lens, the second irradiation optical system having a common optical system from the scanning optical system to the objective lens, the first irradiation optical system shares the common optical system with the second irradiation optical system, the first irradiation optical system selectively irradiates the patient's eye with the first light and the second irradiation optical system selectively irradiates the patient's eye with the second light, and when the second irradiation optical system irradiates the patient's eye with the second light, the scanning optical system scans a predetermined portion of the patient's eye with the second light.

[0016] In a microscope according to another aspect of the present invention, the second irradiation optical system has an interference optical system that splits light emitted from the light source into reference light and measurement light, which is the second light, and irradiates the patient's eye with the measurement light through a common optical system. The interference optical system detects interference light between the reference light and the second return light that enters through the common optical system from the patient's eye irradiated with the measurement light, and the interference image generation unit generates a tomographic image of the patient's eye based on a detection signal of the interference light detected by the interference optical system.

[0017] In a microscope according to another aspect of the present invention, the objective lens includes a first objective lens used in the observation optical system and a second objective lens used in the first irradiation optical system.

[0018] In a microscope according to another aspect of the present invention, the objective lens includes a first objective lens used in the observation optical system and a second objective lens used in the first illumination optical system and the second illumination optical system, thereby achieving a compact and low-cost microscope.

[0019] In a microscope according to another aspect of the present invention, a portion of the first objective lens is cut out, and a second objective lens is disposed in the cut-out portion of the first objective lens. [Effects of the Invention]

[0020] The present invention can achieve miniaturization and cost reduction, and can reduce the effort required by the surgeon. [Brief explanation of the drawings]

[0021] [Figure 1] FIG. 1 is a top view of a surgical microscope according to a first embodiment. [Figure 2] 2 is a side view of the microscope body of the surgical microscope in FIG. 1, viewed from the direction A. FIG. [Figure 3] FIG. 1 is a schematic diagram of the optical system of an OCT unit. [Figure 4] FIG. 2 is a side view of the OCT optical system as seen from the X direction side. [Figure 5] FIG. 2 is a perspective view of an OCT optical system and a pattern formation optical system. [Figure 6] FIG. 2 is an explanatory diagram showing an example of a ring pattern formed on the cornea by the pattern forming optical system. [Figure 7] FIG. 2 is an explanatory diagram showing an example of a ring pattern formed on the cornea by the pattern forming optical system. [Figure 8] 10 is an explanatory diagram showing an example of a ring pattern formed on the fundus by the pattern forming optical system. FIG. [Figure 9] FIG. 2 is a functional block diagram of a control device for a surgical microscope. [Figure 10] 10 is an explanatory diagram for explaining the formation of a guide pattern on the cornea by a guide display control unit. FIG. [Figure 11] 10 is a flowchart showing the operation of the surgical microscope of the first embodiment, particularly the flow of measuring the corneal shape of the patient's eye E and presenting the direction of the corneal meridian in the corneal observation and measurement mode. [Figure 12] 10 is a flowchart showing the operation of the surgical microscope of the second embodiment, particularly the flow of measuring the corneal shape of the patient's eye E and presenting the direction of the corneal meridian in the corneal observation and measurement mode. [Figure 13] 10 is an explanatory diagram for explaining multiple changes in the ring diameter of the ring pattern on the cornea during corneal observation and measurement in the second embodiment. FIG. [Figure 14] FIG. 10 is a top view of a surgical microscope according to a third embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0022] [Overall configuration of the surgical microscope according to the first embodiment] Fig. 1 is a top view of a surgical microscope 10 (also referred to as a surgical microscope system) according to a first embodiment. Fig. 2 is a side view of a microscope body 10a of the surgical microscope 10 in Fig. 1, viewed from the A direction. Note that the X direction in the figure is the left-right direction (the interpupillary direction of the patient's eye E) based on the patient (also referred to as the examinee or the patient to be operated on), the Z direction is the working distance direction (for example, the up-down direction in this embodiment) parallel to the optical axis OA of a first objective lens 20 (described below), and the Y direction is the direction perpendicular to the XZ direction.

[0023] 1 and 2, a surgical microscope 10 corresponds to the microscope of the present invention and is used for cataract surgery using a toric IOL on a patient's eye E. This surgical microscope 10 has, as its operating modes, a corneal observation and measurement mode, a fundus observation mode, an eye refractive power measurement mode, and an OCT measurement mode using optical coherence tomography (OCT), and is capable of acquiring, as eye characteristics of the patient's eye E, the corneal shape (direction of the steepest meridian and corneal curvature) of the patient's eye E, the eye refractive power of the patient's eye E, and a tomographic image of the patient's eye E.

[0024] The corneal observation and measurement mode is an observation mode used to observe a magnified image of the cornea Ec of the patient's eye E. In addition, in the corneal observation and measurement mode, in order to support the surgeon in performing surgery on the patient's eye E, the corneal shape (direction of the maximal meridian, corneal curvature) of the patient's eye E is measured, and the direction of the maximal meridian of the cornea Ec is presented (informed) to the surgeon.

[0025] The fundus observation mode is an observation mode used to observe a magnified image (retroillumination image) of the fundus Ef of the patient's eye E. The eye refractive power measurement mode is a mode for measuring the eye refractive power (including astigmatism power) of the patient's eye E, and is performed, for example, before and after surgery on the patient's eye E. The OCT measurement mode is used to capture tomographic images of the patient's eye E (cornea Ec, fundus Ef).

[0026] The surgical microscope 10 includes a microscope body 10a, an operation unit 12, a monitor 14, and a control device 16. The microscope body 10a also includes an OCT optical system 500 used in the OCT measurement mode, and a pattern forming optical system 600 that forms a ring pattern LP on the patient's eye E (cornea Ec, fundus Ef).

[0027] In the cornea observation and measurement mode, the microscope body 10a captures a moving image of the cornea Ec on which a ring pattern LP is formed by a pattern formation optical system 600 (described later), and outputs an observation image D (captured image). In the fundus observation mode, the microscope body 10a captures a moving image of the fundus Ef while stereo coaxially illuminating the fundus Ef, and outputs an observation image D. In the eye refractive power measurement mode, the microscope body 10a captures a moving image of the fundus Ef on which a ring pattern LP is formed by a pattern formation optical system 600 (described later), and outputs an observation image D.

[0028] The operation unit 12 is connected to the control device 16 by wire or wirelessly. The operation unit 12 accepts inputs for various operations of the surgical microscope 10, including operations for adjusting the position and attitude of the microscope main body 10a (manual alignment operations), operations for switching the operating mode of the surgical microscope 10, and operations for changing the zoom magnification of the microscope main body 10a. The operation unit 12 includes various operation devices such as hardware keys (switches, buttons), an operation lever, a mouse, a keyboard, and an operation panel (including the display surface of the monitor 14) provided on the microscope main body 10a.

[0029] A display device such as an LCD (Liquid Crystal Display) is used as the monitor 14. The monitor 14 is connected to the control device 16 by wire or wirelessly, and displays an observation image D captured as a moving image by the microscope main body 10a under the control of the control device 16. In the figure, the observation image D acquired in the corneal observation measurement mode is displayed.

[0030] The control device 16 is an arithmetic device such as a computer provided within the housing of the surgical microscope 10. The control device 16 comprehensively controls the operation of each part of the microscope main body 10a and the display of the observation image D and the like on the monitor 14 in response to input operations on the operation unit 12. In addition, the control device 16 measures the corneal shape (superficial meridian direction, corneal curvature) of the patient's eye E and displays the superficial meridian direction in the corneal observation and measurement mode, and measures the ocular refractive power of the patient's eye E in the ocular refractive power measurement mode. The control device 16 may be provided outside the housing of the surgical microscope 10.

[0031] [Microscope body] The microscope main body 10a includes a first objective lens 20, a front lens 21, a reflecting mirror RM, a dichroic mirror DM1, illumination optical systems 31L and 31R, observation optical systems 40L and 40R, and cameras 60L and 60R.

[0032] The first objective lens 20 has an optical axis OA parallel to the Z direction and is disposed at a position facing the patient's eye E. The reflecting mirror RM is disposed at a position above the first objective lens 20 in the Z direction, more specifically at the intersection of the optical axis OA and the optical axis OB of the observation optical systems 40L and 40R (described below) which extends in a direction perpendicular to the optical axis OA (here, the Y direction). A dichroic mirror DM1, the observation optical systems 40L and 40R, and the cameras 60L and 60R are disposed along the optical axis OB (Y direction) from the reflecting mirror RM. The illumination optical systems 31L and 31R are disposed above the dichroic mirror DM1 in the Z direction.

[0033] The first objective lens 20 has a shape in which a portion thereof is cut out along a plane parallel to the ZX plane, and constitutes the objective lens of the present invention together with the second objective lens 508 described below. In the corneal observation and measurement mode, the first objective lens 20 transmits return light LA ​​(reflected light) from the cornea Ec on which a ring pattern LP has been formed by the pattern formation optical system 600 described below, and emits it to the reflecting mirror RM. The return light LA, together with the return light LB described below, corresponds to the first return light of the present invention.

[0034] In addition, in the fundus observation mode, the first objective lens 20 irradiates the fundus Ef with illumination light L1 emitted from illumination optical systems 31L and 31R (described later) via the front lens 21, and transmits return light LB from the fundus Ef to emit it toward the reflecting mirror RM. Furthermore, in the eye refractive power measurement mode, the first objective lens 20 transmits return light LB from the fundus Ef on which a ring pattern LP has been formed by the pattern forming optical system 600 to emit it toward the reflecting mirror RM.

[0035] The front lens 21 is provided between the first objective lens 20 and a second objective lens 508 (described later) and the patient's eye E, so as to be freely insertable into and removable from each optical path of the illumination light L1, the return lights LA and LB, and the measurement light LS. The front lens 21 focuses light incident from the first objective lens 20 or the second objective lens 508 onto the fundus Ef. The front lens 21 is switched to an inserted state where it is inserted into each optical path in the fundus observation mode and the eye refractive power measurement mode, and is switched to a retracted state where it is retracted from each optical path in the cornea observation and measurement mode. The front lens 21 can be switched between the inserted state and the retracted state by a lens inserting / retracting mechanism 22 (see FIG. 9) or manually.

[0036] The reflecting mirror RM is shared by the illumination optical systems 31L and 31R and the observation optical systems 40L and 40R. This reflecting mirror RM reflects the illumination light L1 incident from the dichroic mirror DM1 toward the first objective lens 20, and conversely reflects the return light LA ​​or return light LB incident from the first objective lens 20 toward the dichroic mirror DM1.

[0037] The dichroic mirror DM1 is shared by the illumination optical systems 31L, 31R and the observation optical systems 40L, 40R, and couples the optical path of the illumination light L1 emitted from the illumination optical systems 31L, 31R with the optical path of the observation optical systems 40L, 40R. The dichroic mirror DM1 reflects the illumination light L1 emitted from the illumination optical systems 31L, 31R toward the reflecting mirror RM, and conversely transmits the return light LA ​​or LB incident from the reflecting mirror RM as is, and emits it toward the observation optical systems 40L, 40R.

[0038] The illumination optical systems 31L and 31R are optical systems for illuminating the fundus Ef. In fundus observation mode, the illumination optical systems 31L and 31R perform stereo coaxial illumination of the fundus Ef using illumination light L1. The optical axes OL and OR of the illumination optical systems 31L and 31R are coupled to the optical axis OA of the first objective lens 20 via a dichroic mirror DM1 and a reflecting mirror RM. That is, the optical axes OL and OR and the optical axis OA are substantially aligned. As a result, the illumination optical systems 31L and 31R illuminate the fundus Ef with so-called "0-degree illumination" using the illumination light L1. As a result, the illumination light L1 is diffusely reflected on the fundus Ef, allowing a stereoscopic image (red reflex) of the fundus Ef to be photographed (observed).

[0039] The illumination optical systems 31L and 31R include a light source 31a and a condenser lens 31b. The light source 31a is a semiconductor light source or the like, and outputs illumination light L1 having a wavelength in the visible range with a color temperature of, for example, 3000 K (Kelvin). This illumination light L1 passes through the condenser lens 31b, is reflected by a dichroic mirror DM1 and a reflecting mirror RM, and then passes through the first objective lens 20 and the front lens 21 to irradiate the fundus Ef. As a result, return light LB of the illumination light L1 diffused and reflected by the fundus Ef travels in the opposite direction along the same optical path (outward path) as the illumination light L1, enters the dichroic mirror DM1, and further passes through the dichroic mirror DM1 to enter the observation optical systems 40L and 40R.

[0040] <Observation optical system> The observation optical system 40L is an optical system that guides the return light LA ​​or return light LB incident from the dichroic mirror DM1 to the camera 60L. The observation optical system 40R is an optical system that guides the return light LA ​​or return light LB incident from the dichroic mirror DM1 to the camera 60R.

[0041] In this embodiment, the observation optical systems 40L and 40R and their optical axes OB extend in the Y direction, which is perpendicular to the optical axis OA (including, for example, approximately perpendicular within a range of ±20°). Note that the direction is not limited to the Y direction as long as it is perpendicular to the optical axis OA; the observation optical systems 40L and 40R and their optical axes OB may extend, for example, in the X direction. This allows the observation optical systems 40L and 40R, which have long optical path lengths, to be arranged in a direction approximately parallel to the XY plane. Therefore, the observation optical systems 40L and 40R are not arranged directly in front of the surgeon, allowing the surgeon to comfortably view the screen of the monitor 14 in front of them (or the situation in front of them). Furthermore, the housing arranged directly in front of the surgeon does not impose a sense of oppression on the surgeon, thereby reducing the burden on the surgeon.

[0042] The observation optical system 40L includes a zoom expander 50L. The zoom expander 50L includes multiple zoom lenses 51, 52, and 53 that can be moved along the optical axis OB by a magnification change mechanism (not shown). This allows the zoom magnification of the observation image D to be changed.

[0043] The observation optical system 40R has the same configuration as the observation optical system 40L, and is equipped with a zoom expander 50R including multiple zoom lenses 51, 52, and 53, and changes the zoom magnification of the observation image D by moving the multiple zoom lenses 51, 52, and 53 using a variable magnification mechanism (not shown). Here, the observation optical systems 40L and 40R can have different zoom magnifications for the observation image D.

[0044] The cameras 60L and 60R continuously capture the return light LA ​​or return light LB incident from the observation optical systems 40L and 40R at a predetermined frame rate (hereinafter abbreviated as video capture) and output an observation image D.

[0045] The camera 60L includes an imaging lens 61 and an imaging element 62 arranged along the optical axis OB. The imaging lens 61 forms an image of the return light LA ​​or return light LB incident from the observation optical system 40L on the imaging surface of the imaging element 62. The imaging element 62 captures a video of the return light LA ​​or return light LB formed by the imaging lens 61 and outputs the observation image D to the control device 16. As a result, in the cornea observation measurement mode, an observation image D of the cornea Ec and ring pattern LP based on the return light LA ​​is obtained, in the fundus observation mode, an observation image D (retroillumination image) of the fundus Ef based on the return light LB is obtained, and in the eye refractive power measurement mode, an observation image D of the ring pattern LP based on the return light LB is obtained.

[0046] The camera 60R has the same configuration as the camera 60L and includes an imaging lens 61 and an image sensor 62. As a result, the return light LA ​​or return light LB incident from the observation optical system 40R is imaged on the imaging surface of the image sensor 62 by the imaging lens 61, and the image sensor 62 captures a video of the return light LA ​​or return light LB, outputting an observation image D to the control device 16. As a result, in the cornea observation measurement mode, an observation image D of the cornea Ec and ring pattern LP based on the return light LA ​​is obtained, in the fundus observation mode, an observation image D (retroillumination image) of the fundus Ef based on the return light LB is obtained, and in the ocular refractive power measurement mode, an observation image D of the ring pattern LP based on the return light LB is obtained. Note that the optical arrangements of the imaging lens 61 and the image sensor 62 of the cameras 60L and 60R can be changed independently of each other, i.e., the focus can be changed on the left and right.

[0047] [OCT optical system] The OCT optical system 500 corresponds to the second irradiation optical system of the present invention, and in the OCT measurement mode, captures a tomographic image of the patient's eye E. The OCT optical system 500 includes an OCT unit 100, an optical fiber 501, a collimator lens unit 502, a dichroic mirror DM2, an optical scanner 503, an OCT imaging lens 504, a mirror 505, a relay lens 506, a mirror 507, a second objective lens 508, and a head lens 21.

[0048] Fig. 3 is a schematic diagram of the optical system of the OCT unit 100. As shown in Fig. 3, the OCT light source 101 of the OCT unit 100 is a wavelength sweep type (wavelength scanning type) light source that can sweep (scan) the wavelength of the emitted light, similar to the light source of a general swept-source type OCT device, and includes a laser light source that includes a resonator. The OCT light source 101 changes the output wavelength over time in the near-infrared wavelength range that is invisible to the human eye.

[0049] The OCT unit 100 is provided with an optical system for performing swept-source OCT. This optical system includes an interference optical system. This interference optical system has the following functions: splitting light L0 from an OCT light source 101 into measurement light LS and reference light LR; generating interference light LC by superimposing return light LS1 (corresponding to second return light) of the measurement light LS from the patient's eye E on the reference light LR that has passed through the reference optical path; and detecting this interference light LC. A detection signal of the interference light LC obtained by the interference optical system is a signal indicating the spectrum of the interference light LC and is sent to the control device 16.

[0050] The OCT light source 101, for example, rapidly changes the wavelength of the emitted light (light L0) based on a wavelength of approximately 860 nm (840 nm in this embodiment). The OCT light source 101 also generates a clock KC synchronized with the output timing of each wavelength of the light L0 swept within a predetermined wavelength range. For example, the OCT light source 101 optically delays one of two branched lights obtained by branching the light L0 of each output wavelength, and then generates the clock KC based on the result of detecting the combined light. The OCT light source 101 then outputs the generated clock KC to the DAQ 130, which will be described later.

[0051] Light L0 output from an OCT light source 101 is guided by an optical fiber 102 to a polarization controller 103, where its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided by an optical fiber 104 to a fiber coupler 105, where it is split into a measurement light LS (corresponding to the second light of the present invention) and a reference light LR.

[0052] The reference light LR generated by the fiber coupler 105 is guided by an optical fiber 110 to a collimator 111 where it is converted into a parallel beam, and then guided to a corner cube 114 via an optical path length correction member 112 and a dispersion compensation member 113. The optical path length correction member 112 acts to match the optical path length of the reference light LR with that of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS.

[0053] The corner cube 114 is held so as to be movable along the incident direction of the reference light LR by a corner cube moving mechanism 115. The corner cube moving mechanism 115 is an actuator that moves the corner cube 114 along the incident direction of the reference light LR, and by moving the corner cube 114, the optical path length of the reference light LR is changed.

[0054] The reference light LR that has passed through the corner cube 114 passes through a dispersion compensation member 113 and an optical path length correction member 112, is converted from a parallel beam into a convergent beam by a collimator 116, and enters an optical fiber 117. The reference light LR that has entered the optical fiber 117 is guided to a polarization controller 118 where its polarization state is adjusted, is guided by an optical fiber 119 to an attenuator 120 where the light amount is adjusted, and is guided by an optical fiber 121 to a fiber coupler 122.

[0055] On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by an optical fiber 501 and converted into a parallel beam by a collimator lens unit 502. The measurement light LS converted into a parallel beam passes through a dichroic mirror DM2, an optical scanner 503, an OCT imaging lens 504, a mirror 505, a relay lens 506, a mirror 507, and a second objective lens 508 and is incident on the patient's eye E.

[0056] 4 is a side view of the OCT optical system 500 as viewed from the X direction side. FIG. 5 is a perspective view of the OCT optical system 500 and the pattern formation optical system 600.

[0057] 4 and 5 and the above-described FIG. 1, the dichroic mirror DM2 branches (wavelength separates) the optical path of the pattern formation optical system 600 from the optical path of the OCT optical system 500. The dichroic mirror DM2 reflects the measurement light LS and return light LS1 of the measurement light LS from the patient's eye E, and transmits the aiming light LG (visible light or near-infrared light) emitted from the pattern formation optical system 600 described below.

[0058] The optical scanner 503 corresponds to the scanning optical system of the present invention, and two-dimensionally scans (deflects) the measurement light LS (the same applies to the aiming light LG described later) irradiated onto the patient's eye E, for example, in the X and Y directions, scanning the imaging site (cornea Ec, fundus Ef) of the patient's eye E. Scanning modes of such measurement light LS include, for example, horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric scan, and spiral scan.

[0059] A galvanometer mirror 503a capable of scanning the measurement light LS in the X direction and a galvanometer mirror 503b capable of scanning the measurement light LS in the Y direction are used as the optical scanner 503. Note that a MEMS (Micro Electro Mechanical Systems) scanner, a polygon mirror, a rotating mirror, a dowel prism, a double dowel prism, a rotation prism, or the like may be used instead of the optical scanner 503.

[0060] The OCT imaging lens 504 has an optical axis O1 parallel to the Y direction, and is provided so that its position can be adjusted along this optical axis O1. Under the control of the control device 16, the OCT imaging lens 504 is adjusted in position so that the end face of the optical fiber 501 or an aiming light source 601 (described later) is in an optically conjugate relationship with the measurement site (cornea Ec, fundus Ef) of the patient's eye E.

[0061] The mirror 505 is disposed on the optical axis O1 of the OCT imaging lens 504 and on the X-direction side of the relay lens 506, i.e., at the intersection of the optical axis O1 and the optical axis O2 of the relay lens 506. The mirror 505 reflects the measurement light LS, which has entered from the OCT imaging lens 504 along the optical axis O1 (Y direction), in the X direction and causes it to enter the relay lens 506.

[0062] The relay lens 506 has an optical axis O2 parallel to the X direction, and is disposed between the mirror 505 and the mirror 507. The relay lens 506 transmits the measurement light LS incident from the mirror 505 along the optical axis O2 (X direction) as is, and causes the measurement light LS to be incident on the mirror 507.

[0063] The mirror 507 is disposed on the optical axis O2 of the relay lens 506 and above the second objective lens 508 in the Z direction, i.e., at the intersection of the optical axis O2 and the optical axis O3 of the second objective lens 508. The mirror 507 reflects the measurement light LS, which has entered from the relay lens 506 along the optical axis O2 (X direction), downward in the Z direction and causes it to enter the second objective lens 508.

[0064] The second objective lens 508 is disposed in the cutout portion of the first objective lens 20 and has an optical axis O3. The second objective lens 508 irradiates the measurement light LS incident from the mirror 507 onto the cornea Ec from an oblique direction or onto the fundus Ef from an oblique direction via the front lens 21.

[0065] Returning to FIG. 3, the return light LS1 of the measuring light LS from the patient's eye E travels in the opposite direction along the same path as the outward path and is guided to the fiber coupler 105, and then reaches the fiber coupler 122 via the optical fiber 128.

[0066] The fiber coupler 122 generates interference light LC between the return light LS1 incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121. The fiber coupler 122 also generates a pair of interference light LC by branching the interference light LC at a predetermined branching ratio (for example, 1:1). The pair of interference light LC is guided to a detector 125 via optical fibers 123 and 124, respectively.

[0067] The detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs the difference between the pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to a data acquisition system (DAQ) 130.

[0068] The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC supplied from the OCT light source 101 described above, and outputs the sampling result of this detection signal to the image forming unit 208 of the control device 16 (see Figure 9).

[0069] [Pattern formation optical system] The pattern formation optical system 600 corresponds to the first irradiation optical system of the present invention. This pattern formation optical system 600 forms a ring pattern LP on the cornea Ec in the cornea observation measurement mode, and forms a ring pattern LP on the fundus Ef in the eye refractive power measurement mode, by two-dimensionally scanning the aiming light LG (corresponding to the first light of the present invention) on the cornea Ec or the fundus Ef of the patient's eye E.

[0070] The pattern formation optical system 600 has an aiming light source 601 and a collimator lens unit 602, and also shares the above-mentioned dichroic mirror DM2, optical scanner 503, OCT imaging lens 504, mirror 505, relay lens 506, mirror 507, second objective lens 508, and front lens 21 with the OCT optical system 500. Therefore, in this embodiment, the OCT optical system 500 and the pattern formation optical system 600 operate selectively. Note that the optical elements from the dichroic mirror DM2 to the second objective lens 508 (front lens 21) constitute the common optical system of the present invention.

[0071] The aiming light source 601 emits aiming light LG, which is spot light (or light other than spot light) in a wavelength range different from that of the measurement light LS, for example, in the visible wavelength range or near-infrared wavelength range. As the aiming light source 601, a known LED (Light Emitting Diode) light source or the output end of an optical fiber, etc., is used.

[0072] The collimator lens unit 602 converts the aiming light LG incident from the aiming light source 601 into a parallel beam of light, and then emits it to the dichroic mirror DM2. As a result, the aiming light LG converted into a parallel beam of light passes through the dichroic mirror DM2, and then, like the measurement light LS described above, passes through the optical scanner 503, the OCT imaging lens 504, the mirror 505, the relay lens 506, and the mirror 507, and then enters the second objective lens 508.

[0073] The second objective lens 508 irradiates the cornea Ec with the aiming light LG from an oblique direction in the cornea observation and measurement mode, and irradiates the fundus Ef with the aiming light LG from an oblique direction via the front lens 21 in the eye refractive power measurement mode. By irradiating the cornea Ec with the aiming light LG from an oblique direction, it is possible to stereophotograph (observe) the cornea Ec while avoiding the effects of ghosts and flares due to reflection from the cornea Ec.

[0074] 6 and 7 are explanatory diagrams showing an example of a ring pattern LP formed on the cornea Ec by the pattern forming optical system 600 (optical scanner 503). Fig. 8 is an explanatory diagram showing an example of a ring pattern LP formed on the fundus Ef by the pattern forming optical system 600 (optical scanner 503).

[0075] Under the control of the control device 16, the optical scanner 503 two-dimensionally scans the aiming light LG irradiated onto the cornea Ec or fundus Ef of the patient's eye E, thereby forming a measurement pattern on the cornea Ec or fundus Ef to be used for measuring the ocular characteristics of the patient's eye E. For example, when measuring the corneal shape (superficial meridian direction, corneal curvature) of the patient's eye E in the corneal observation and measurement mode, the optical scanner 503 forms a continuous ring pattern LP (keratocondylus ring) on ​​the cornea Ec as shown by reference numerals 6A and 6B in FIG. 6, or forms an intermittent ring pattern LP on the cornea Ec as shown by reference numerals 7A and 7B in FIG. 7. As a result, the return light LA ​​from the cornea Ec on which the ring pattern LP is formed passes through the first objective lens 20, the reflecting mirror RM, the dichroic mirror DM1, and the observation optical systems 40L and 40R, and is captured as a moving image by the image sensor 62 of the cameras 60L and 60R.

[0076] Furthermore, in the eye refraction measurement mode, the optical scanner 503 two-dimensionally scans the aiming light LG on the fundus Ef to form a continuous ring pattern LP (reflection ring) on ​​the cornea Ec as shown in Fig. 8. As a result, the returned light LB from the fundus Ef on which the ring pattern LP has been formed passes through the head lens 21, the first objective lens 20, the reflecting mirror RM, the dichroic mirror DM1, and the observation optical systems 40L and 40R, and is captured as a moving image by the image pickup elements 62 of the cameras 60L and 60R. Note that instead of forming a continuous ring pattern LP on the fundus Ef, an intermittent ring pattern LP (see Fig. 7) may be formed.

[0077] Furthermore, as will be described in detail later, when the direction of the maximal meridian of the cornea Ec of the patient's eye E is calculated in the corneal observation and measurement mode, the optical scanner 503, under the control of the control device 16, two-dimensionally scans the aiming light LG irradiated onto the cornea Ec, thereby forming a guide pattern GP (see Figure 10) on the cornea Ec that indicates the direction of the maximal meridian of the cornea Ec.

[0078] [Control device] Fig. 9 is a functional block diagram of the control device 16 of the surgical microscope 10. As shown in Fig. 9, the control device 16 has an arithmetic circuit composed of various processors, memories, etc. The various processors include a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), and a programmable logic device (e.g., simple programmable logic device (SPLD), complex programmable logic device (CPLD), and field programmable gate array (FPGA)). The various functions of the control device 16 may be realized by a single processor, or by multiple processors of the same or different types.

[0079] The control device 16 is connected to the aforementioned operation unit 12, monitor 14, each part of the microscope main body 10a, each part of the OCT optical system 500, the aiming light source 601, and the lens inserting / removing mechanism 22 that inserts and removes the head lens 21, as well as a memory unit 18. Although not shown in the figure, the memory unit 18 stores the control program for the surgical microscope 10 and measurement results of the eye characteristics (corneal shape, eye refractive power) of the patient's eye E, etc.

[0080] The control device 16 reads and executes the control program in the memory unit 18, thereby functioning as a microscope body control unit 200, an image acquisition unit 202, a display control unit 204, an OCT measurement control unit 206, an image formation unit 208, a data processing unit 210, a ring pattern formation control unit 212, an eye characteristic calculation unit 214, and a guide display control unit 216.

[0081] The microscope body control unit 200 controls the operation of the illumination optical systems 31L and 31R, the observation optical systems 40L and 40R, and the cameras 60L and 60R, and also controls the insertion and removal of the head lens 21 by the lens insertion and removal mechanism 22.

[0082] Specifically, when a switching operation to the corneal observation and measurement mode is performed using the operation unit 12, the microscope body control unit 200 starts switching the front lens 21 to a retracted state using the lens insertion / removal mechanism 22 and capturing video of the return light LA ​​using the image sensor 62 of the cameras 60L and 60R.

[0083] Furthermore, when a switching operation to the fundus observation mode is performed using the operation unit 12, the microscope body control unit 200 starts turning on the light source 31a of the illumination optical systems 31L, 31R, switching the head lens 21 to the inserted state using the lens inserting / removing mechanism 22, and capturing video of the return light LB using the image sensor 62 of the cameras 60L, 60R. Furthermore, when a switching operation to the eye refractive power measurement mode is performed using the operation unit 12, the microscope body control unit 200 starts switching the head lens 21 to the inserted state using the lens inserting / removing mechanism 22 and capturing video of the return light LB using the image sensor 62 of the cameras 60L, 60R.

[0084] Furthermore, when the operation unit 12 is used to switch to the OCT measurement mode and tomographic imaging of the cornea Ec is selected, the microscope body control unit 200 switches the head lens 21 to a retracted state using the lens insertion / removal mechanism 22, and when tomographic imaging of the fundus Ef is selected, the microscope body control unit 200 switches the head lens 21 to an inserted state using the lens insertion / removal mechanism 22.

[0085] The image acquisition unit 202 sequentially acquires observation images D from the image pickup elements 62 of the cameras 60L, 60R via an interface (not shown) in the cornea observation and measurement mode, the fundus observation mode, and the eye refractive power measurement mode. Then, the image acquisition unit 202 sequentially outputs the acquired observation images D to the display control unit 204 and the eye characteristic calculation unit 214 in the cornea observation and measurement mode. Furthermore, the image acquisition unit 202 sequentially outputs the acquired observation images D to the display control unit 204 in the fundus observation mode. Furthermore, the image acquisition unit 202 sequentially outputs the acquired observation images D to the eye characteristic calculation unit 214 in the eye refractive power measurement mode.

[0086] The display control unit 204 displays, as a moving image, the observation image D sequentially input from the image acquisition unit 202 on the monitor 14 in the corneal observation measurement mode and the fundus observation mode. This allows the surgeon to observe the cornea Ec and the ring pattern LP in the corneal observation measurement mode, and to observe a retro-illumination image of the fundus Ef in the fundus observation mode. In addition, the display control unit 204 displays, on the monitor 14, a tomographic image (not shown) corrected by a data processing unit 210 (described later) in the OCT measurement mode.

[0087] When the operation unit 12 is used to switch to the OCT measurement mode, the OCT measurement control unit 206 controls the corner cube moving mechanism 115 and the optical scanner 503 of the OCT optical system 500 to perform one or more scan control operations to scan (B scan) the cornea Ec or the fundus Ef with the measurement light LS. Note that the scan control during OCT measurement (including changing the optical path length of the reference light LR by moving the corner cube 114) is a known technique, and therefore a detailed description thereof will be omitted here (see, for example, JP 2020-44027 A).

[0088] At the same time, the OCT measurement control unit 206 controls the OCT optical system 500 to cause the detector 125 to detect the interference light LC and output a detection signal, and the DAQ 130 to sample the detection signal, and then inputs the sampling result of this detection signal to the image forming unit 208.

[0089] The image forming unit 208 corresponds to the tomographic image generating unit of the present invention. Based on the sampling results of the detection signals input via the detector 125 and the DAQ 130 in the OCT measurement mode, the image forming unit 208 performs filtering and fast Fourier transform processing similar to those of conventional spectral domain OCT, and forms image data (B-scan image) of a tomographic image of the cornea Ec or fundus Ef.

[0090] The data processing unit 210 performs various types of data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 208. For example, the data processing unit 210 performs correction processing such as brightness correction and dispersion correction on the tomographic image. Then, the data processing unit 210 outputs the tomographic image after the correction processing to the display control unit 204. As a result, the tomographic image is displayed on the monitor 14 by the display control unit 204.

[0091] When the operation unit 12 is used to switch to the cornea observation measurement mode or the eye refractive power measurement mode, the ring pattern formation control unit 212 controls the pattern formation optical system 600 to form a ring pattern LP on the cornea Ec or the fundus Ef. Specifically, in the cornea observation measurement mode, as shown in FIGS. 6 and 7 , the ring pattern formation control unit 212 causes the aiming light source 601 to emit the aiming light LG and controls the optical scanner 503 to scan the cornea Ec with the aiming light LG, thereby forming a continuous or intermittent ring pattern LP on the cornea Ec. As a result, the image pickup elements 62 of the cameras 60L, 60R capture moving images of the returned light LA ​​from the cornea Ec on which the ring pattern LP has been formed, and the image pickup elements 62 sequentially output observation images D of the cornea Ec and the ring pattern LP to the image acquisition unit 202.

[0092] 8, in the ocular curvature measurement mode, the ring pattern formation control unit 212 causes the aiming light source 601 to emit the aiming light LG and controls the optical scanner 503 to scan the aiming light LG irradiated onto the fundus Ef, thereby forming a continuous or intermittent ring pattern LP on the fundus Ef. As a result, the image pickup elements 62 of the cameras 60L, 60R capture moving images of the return light LB from the fundus Ef on which the ring pattern LP has been formed, and the image pickup elements 62 sequentially output observation images D of the fundus Ef and the ring pattern LP to the image acquisition unit 202.

[0093] The eye characteristic calculation unit 214 includes a corneal shape calculation unit 214a and an eye refractive power calculation unit 214b. The corneal shape calculation unit 214a calculates the direction of the steepest meridian and the corneal curvature as the corneal shape of the patient's eye E based on the observation image D input from the image acquisition unit 202 in the corneal observation and measurement mode.

[0094] Specifically, the corneal shape calculation unit 214a detects a ring pattern LP from the observation image D and calculates the direction of the maximal meridian of the cornea Ec by analyzing the directions of the major and minor axes of the ellipse of this ring pattern LP. Note that the specific method for calculating the direction of the maximal meridian is a known technique (see, for example, International Publication No. 2011 / 030509), and therefore a detailed description thereof will be omitted here.

[0095] The corneal shape calculation unit 214a also calculates the corneal curvature of the cornea Ec by detecting and analyzing the ring pattern LP from the observation image D. Note that the specific method for calculating the corneal curvature is also a publicly known technique (see, for example, Japanese Patent Application Laid-Open No. 2019-166277), so a detailed description thereof will be omitted here. The calculation result of the corneal curvature by the corneal shape calculation unit 214a is output to the display control unit 204, which then displays it on the monitor 14.

[0096] The ocular refractive power calculation unit 214b calculates the ocular refractive power of the patient's eye E based on the observation image D input from the image acquisition unit 202 in the ocular refractive power measurement mode. Specifically, the ocular refractive power calculation unit 214b detects a ring pattern LP from the observation image D, obtains an approximation ellipse that approximates the ring pattern LP, and calculates the ocular refractive power of the patient's eye E based on the shape (major axis, minor axis, and axis angle) of the approximation ellipse (see, for example, Japanese Patent Application Laid-Open No. 2017-51430). The calculation result of the ocular refractive power by the ocular refractive power calculation unit 214b is output to the display control unit 204, which then displays it on the monitor 14. The surgical microscope 10 has a function for measuring the ocular refractive power of the patient's eye E, making it possible to easily and quickly measure the ocular refractive power of the patient's eye E before and after surgery. Furthermore, by measuring the astigmatism power of the patient's eye E as the ocular refractive power, it is possible to determine the incision position during surgery that is appropriate for the astigmatism power of the patient's eye E.

[0097] Fig. 10 is an explanatory diagram for explaining the formation of a guide pattern GP on the cornea Ec by the guide display control unit 216. Note that the symbol SD1 in Fig. 10 indicates the direction of the principal meridian of the cornea Ec, and the symbol SD2 indicates the direction of the minor meridian of the cornea Ec.

[0098] As shown in FIG. 10, the guide display control unit 216 controls the optical scanner 503 of the pattern forming optical system 600 in the cornea observation and measurement mode to form a guide pattern GP indicating the direction of the steepest meridian on the cornea Ec.

[0099] For example, the guide display control unit 216 determines the three-dimensional position of the cornea Ec (the relative position of the cornea Ec with respect to the surgical microscope 10) based on the position of the cornea Ec in the observation image D and the known optical magnification of the first objective lens 20, etc. Next, the guide display control unit 216 determines a formation area of ​​the guide pattern GP on the cornea Ec based on the three-dimensional position of the cornea Ec and the detection result of the steepest meridian direction by the corneal shape calculation unit 214a. Then, the guide display control unit 216 controls the optical scanner 503 to repeatedly scan the determined formation area with the aiming light LG, thereby forming the guide pattern GP on the cornea Ec.

[0100] In this way, the guide pattern GP is formed on the cornea Ec, and the return light LA ​​from this cornea Ec is captured as a moving image by the imaging elements 62 of the cameras 60L, 60R. Then, the observation image D of the cornea Ec on which the guide pattern GP is formed is sequentially input from the imaging elements 62 of the cameras 60L, 60R to the display control unit 204 via the image acquisition unit 202. As a result, the display control unit 204 causes the monitor 14 to display the observation image D of the cornea Ec on which the guide pattern GP is formed.

[0101] In addition, while the observation image D of the cornea Ec and the guide pattern GP is displayed on the monitor 14, the formation of the ring pattern LP on the fundus Ef and the calculation of the steepest meridian direction by the corneal shape calculation unit 214a may be performed periodically or continuously in parallel, thereby periodically or continuously updating the formation position of the guide pattern GP on the cornea Ec.

[0102] [Operation of the first embodiment] FIG. 11 is a flowchart showing the operation of the surgical microscope 10 of the first embodiment, particularly the flow of measuring the corneal shape (superficial meridian direction, corneal curvature) of the patient's eye E and presenting the superficial meridian direction of the cornea Ec in the corneal observation and measurement mode.

[0103] 11, after manual alignment of the microscope body 10a with respect to the patient's eye E is performed, the surgeon performs a switching operation to the corneal observation and measurement mode on the operation unit 12 (step S1). In response to this switching operation, the microscope body control unit 200 switches the head lens 21 to a retracted state using the lens inserting / removing mechanism 22, and starts driving the image pickup elements 62 of the cameras 60L and 60R (step S2).

[0104] Furthermore, the ring pattern formation control unit 212 causes the aiming light source 601 to emit the aiming light LG (step S3). As a result, the aiming light LG passes through the collimator lens unit 602, the dichroic mirror DM2, the optical scanner 503, the OCT imaging lens 504, the mirror 505, the relay lens 506, and the mirror 507, and is then irradiated onto the cornea Ec by the second objective lens 508. Furthermore, the return light LA ​​from the cornea Ec passes through the first objective lens 20, the reflecting mirror RM, the dichroic mirror DM1, and the observation optical systems 40L and 40R, and is incident on the cameras 60L and 60R.

[0105] Next, the ring pattern formation control unit 212 controls the optical scanner 503 to two-dimensionally scan the aiming light LG irradiated onto the cornea Ec (step S4), thereby forming a continuous or intermittent ring pattern LP on the cornea Ec as shown in Figures 6 and 7 (step S5). As a result, the image pickup elements 62 of the cameras 60L, 60R capture a moving image of the returned light LA ​​from the cornea Ec on which the ring pattern LP has been formed, and output an observation image D of the cornea Ec and the ring pattern LP to the image acquisition unit 202 (step S6).

[0106] Then, the image acquisition unit 202 sequentially acquires the observation images D from the image pickup elements 62 of the cameras 60L and 60R, and sequentially outputs the observation images D to the display control unit 204 and the corneal shape calculation unit 214a (step S7). As a result, under the control of the display control unit 204, the display of the observation images D on the monitor 14 begins.

[0107] On the other hand, the corneal shape calculation unit 214a calculates the corneal shape (superficial meridian direction and corneal curvature) of the patient's eye E by detecting and analyzing the ring pattern LP from the observation image D input from the image acquisition unit 202, and outputs the calculation result of the superficial meridian direction to the guide display control unit 216 (step S8). The calculation result of the corneal curvature by the corneal shape calculation unit 214a is displayed on the monitor 14 by the display control unit 204.

[0108] Next, the guide display control unit 216 determines a formation area of ​​the guide pattern GP on the cornea Ec based on the three-dimensional position of the cornea Ec determined based on the observed image D etc. and the detection result of the steepest meridian direction by the corneal shape calculation unit 214a, and controls the optical scanner 503 so that the aiming light LG repeatedly scans this formation area (step S9). As a result, the guide pattern GP is formed on the cornea Ec (step S10).

[0109] Then, the return light LA ​​from the cornea Ec on which the guide pattern GP is formed is captured as a video by the imaging elements 62 of the cameras 60L, 60R, and the observation images D of the cornea Ec are sequentially output from the imaging elements 62 of the cameras 60L, 60R to the display control unit 204 via the image acquisition unit 202 (step S11). As a result, the display control unit 204 displays the observation image D of the cornea Ec on which the guide pattern GP is formed on the monitor 14. As a result, it is possible to present to the surgeon the direction of the steepest meridian of the cornea Ec, i.e., the position (incision position for cataract surgery) where the corrective effect of the toric IOL can be maximized (where astigmatism can be most reduced).

[0110] If the eye refractive power measurement mode is selected instead of the corneal observation and measurement mode in step S1, the head lens 21 is switched to the inserted state in step S2, the fundus oculi Ef is irradiated with aiming light LG in step S3, and a ring pattern LP is formed on the fundus oculi Ef in steps S4 and S5. Then, in step S6, the image capturing elements 62 of the cameras 60L and 60R capture a moving image of the return light LB from the fundus oculi E on which the ring pattern LP has been formed. In step S7, the image acquisition unit 202 outputs an observation image D to the eye refractive power calculation unit 214b, and in step S8, the eye refractive power calculation unit 214b calculates the eye refractive power of the patient's eye E based on the observation image D. The calculation result of the eye refractive power of the patient's eye E is displayed on the monitor 14. In addition, when the ocular refractive power (astigmatism degree) of the patient's eye E is measured, it is possible to determine the incision position that matches the astigmatism degree of the patient's eye E during surgery, so the guide display control unit 216 can control the optical scanner 503 to scan the cornea Ec with the aiming light LG, thereby forming a guide pattern GP indicating this incision position on the cornea Ec.

[0111] As described above, in the surgical microscope 10 of the first embodiment, the aiming light LG can be scanned by the pattern forming optical system 600 to form a ring pattern LP on the cornea Ec or the fundus Ef, eliminating the need to provide a keratinizing light source and a reflector light source unit in the surgical microscope 10, thereby reducing the size and cost of the surgical microscope 10. Furthermore, the surgeon no longer needs to insert and remove the keratinizing light source, thereby reducing the surgeon's workload. As a result, size reduction, cost reduction, and reduction in the surgeon's workload can be achieved.

[0112] Furthermore, the pattern forming optical system 600 can be made smaller and less expensive by sharing the configuration with the OCT optical system 500 except for the aiming light source 601 and the collimator lens unit 602. Furthermore, the corneal shape and ocular refractive power of the patient's eye E can be measured regardless of the patient's posture (supine, sitting, standing), and a guide pattern GP that matches the direction of the steepest meridian and the astigmatism power can be formed on the cornea Ec.

[0113] [Second embodiment] Fig. 12 is a flowchart showing the operation of the surgical microscope 10 of the second embodiment, particularly the flow of measuring the corneal shape (superficial meridian direction, corneal curvature) of the patient's eye E and presenting the superficial meridian direction of the cornea Ec in the corneal observation and measurement mode. Fig. 13 is an explanatory diagram for explaining multiple changes in the ring diameter of the ring pattern LP on the cornea Ec during corneal observation and measurement in the second embodiment.

[0114] In the surgical microscope 10 of the first embodiment, a single ring pattern LP is formed on the cornea Ec, and the corneal shape (direction of the steepest meridian and corneal curvature) is calculated based on an observation image D of the cornea Ec on which this single ring pattern LP is formed. In contrast, in the surgical microscope 10 of the second embodiment, the ring diameter of the ring pattern LP is changed while repeatedly acquiring the observation image D, and the corneal shape of the patient's eye E is calculated based on the observation images D of multiple corneas Ec on which ring patterns LP with different ring diameters are formed. Note that the surgical microscope 10 of the second embodiment has basically the same configuration as the surgical microscope 10 of the first embodiment, and therefore, components that are identical in function or configuration to those of the first embodiment are assigned the same reference numerals and their description will be omitted.

[0115] As shown in Fig. 12, the processing flow from step S1 to step S5 is basically the same as that of the first embodiment shown in Fig. 11, and therefore a detailed description thereof will be omitted here. Then, as shown by reference numeral XIIIA in Fig. 13, the image pickup elements 62 of the cameras 60L, 60R capture a moving image of the return light LA ​​from the cornea Ec on which the ring pattern LP is formed, and output the observation image D to the image acquisition unit 202 (step S6 in Fig. 12). As a result, the image acquisition unit 202 acquires the observation image D, and the display control unit 204 displays the observation image D on the monitor 14 (step S7 in Fig. 12).

[0116] Next, as shown by reference symbol XIIIB in Fig. 13, the ring pattern formation control unit 212 of the second embodiment controls the optical scanner 503 to change the ring diameter of the ring pattern LP formed on the cornea Ec (YES in step S7A of Fig. 12, steps S4 and S5). As a result, the image pickup elements 62 of the cameras 60L and 60R capture moving images of the returned light LA ​​from the cornea Ec on which the ring pattern LP is formed after the change in ring diameter (step S6). As a result, observation images D of the cornea Ec for each of the two ring diameters of the ring pattern LP, i.e., images equivalent to the observation image D of the cornea Ec on which the double ring pattern LP is formed, are obtained (step S7).

[0117] Note that the process of changing the ring diameter of the ring pattern LP and capturing the observation image D of the cornea Ec on which the ring pattern LP is formed may be repeated three or more times. In this case, an observation image D equivalent to the observation image D of the cornea Ec on which multiple ring patterns LP are formed can be obtained.

[0118] The corneal shape calculation unit 214a of the second embodiment calculates the corneal shape (direction of the steepest meridian, corneal curvature) of the patient's eye E based on the observation images D of a plurality of corneas Ec in which the ring diameters of the ring pattern LP are made different from one another (NO in step S7A, step S8). As a result, the corneal shape calculation unit 214a of the second embodiment can improve the calculation accuracy of the corneal shape of the patient's eye E compared to the first embodiment in which the corneal shape is calculated based on a single observation image D without changing the ring diameter of the ring pattern LP.

[0119] The processing from step S9 onward in FIG. 12 is basically the same as that in the first embodiment shown in FIG. 11, and therefore a detailed description thereof will be omitted here.

[0120] As described above, in the second embodiment, the observation image D is repeatedly acquired while changing the ring diameter of the ring pattern LP, and the corneal shape of the patient's eye E is calculated based on the observation images D for each of the different ring diameters, thereby enabling the corneal shape of the patient's eye E to be measured with higher accuracy.

[0121] [Third embodiment] 14 is a top view of a surgical microscope 10 according to a third embodiment. In the above embodiments, the observation optical systems 40L, 40R guide the return light LA ​​or LB to the image sensor 62 of the camera 60L, 60R, but in the third embodiment, the observation optical systems 40L, 40R also guide the return light LB to the eyepieces 65 of the eyepiece systems 63L, 63R.

[0122] 14, the surgical microscope 10 of the third embodiment has basically the same configuration as the surgical microscopes 10 of the above-described embodiments, except that eyepiece lens systems 63L, 63R are provided in the microscope body 10a, and the observation optical system 40L includes a beam splitter BSL, and the observation optical system 40R includes a beam splitter BSR. For this reason, components that are functionally or structurally identical to those of the above-described embodiments are designated by the same reference numerals, and their description will be omitted.

[0123] The beam splitter BSL is disposed between the zoom expander 50L and the camera 60L. This beam splitter BSL transmits a portion of the return light LA ​​or return light LB incident from the zoom expander 50L to emit it to the camera 60L, and reflects the remainder toward the eyepiece lens system 63L.

[0124] The beam splitter BSR is disposed between the zoom expander 50R and the camera 60R. The beam splitter BSR transmits a portion of the return light LA ​​or return light LB incident from the zoom expander 50R to emit it toward the camera 60R, and reflects the remainder toward the eyepiece lens system 63R.

[0125] The eyepiece systems 63L and 63R each include an imaging lens 64 and an eyepiece 65. The imaging lens 64 of the eyepiece system 63L guides the return light LA ​​or return light LB incident from the beam splitter BSL to the eyepiece 65. The imaging lens 64 of the eyepiece system 63R also guides the return light LA ​​or return light LB incident from the beam splitter BSR to the eyepiece 65. This allows the surgeon to observe the cornea Ec illuminated with the ring pattern LP through the eyepiece 65 in the corneal observation and measurement mode. Also, the surgeon can observe the fundus Ef through the eyepiece 65 in the fundus observation mode.

[0126] Although the surgical microscope 10 of the third embodiment is equipped with both the cameras 60L, 60R (image pickup element 62) and the eyepiece lens systems 63L, 63R, it is also possible to omit the cameras 60L, 60R and only have the eyepiece lens systems 63L, 63R.

[0127] [others] In each of the above embodiments, a reflecting mirror RM is provided at the intersection of the optical axis OA and the optical axis OB, but a dichroic mirror DM1 may be provided at the intersection of the optical axis OA and the optical axis OB instead of the reflecting mirror RM. In this case, the positions of the illumination optical systems 31L and 31R are also changed to positions above the dichroic mirror DM1 in the Z direction.

[0128] In each of the above embodiments, a ring pattern LP is formed on the cornea Ec or the fundus Ef, but various measurement patterns used to measure the ocular characteristics of the patient's eye E may be projected onto the cornea Ec or the fundus Ef.

[0129] In each of the above embodiments, the surgical microscope 10 is provided with the monitor 14, but the present invention is also applicable to a surgical microscope 10 that does not have the monitor 14 and uses an external monitor.

[0130] In each of the above embodiments, the observation optical systems 40L, 40R and their optical axes OB extend perpendicular to the optical axis OA, but they may be parallel (including approximately parallel) to the optical axis OA, and the orientation of the observation optical systems 40L, 40R and their optical axes OB is not particularly limited.

[0131] In each of the above embodiments, the surgical microscope 10 is equipped with binocular illumination optical systems 31L and 31R, observation optical systems 40L and 40R, and cameras 60L and 60R, but may also be monocular.

[0132] In each of the above embodiments, the surgical microscope 10 is provided with the OCT optical system 500 and the pattern forming optical system 600. However, instead of the OCT optical system 500, an optical system capable of irradiating various types of light (second light) onto the patient's eye E may be provided. For example, as the second irradiation optical system of the present invention, the surgical microscope 10 may be provided with an SLO optical system used in a scanning laser ophthalmoscope (SLO), an optical system of a laser surgery apparatus that irradiates a treatment site of the patient's eye E with laser light to perform laser coagulation treatment, or the like. Furthermore, in this case, by providing an optical system having a scanning optical system capable of scanning the light to be irradiated onto the patient's eye E, the pattern forming optical system 600 and the scanning optical system can be shared, thereby achieving a reduction in size and cost of the surgical microscope 10.

[0133] In each of the above embodiments, the surgical microscope 10 is provided with the OCT optical system 500 and the pattern forming optical system 600, but it may also be provided with only the pattern forming optical system 600.

[0134] In each of the above embodiments, the surgical microscope 10 includes the first objective lens 20 used in the microscope body 10a and the second objective lens 508 used in the OCT optical system 500 and the pattern formation optical system 600, but a single objective lens may be used in the microscope body 10a, the OCT optical system 500, and the pattern formation optical system 600. Note that if the OCT optical system 500 is omitted, a single objective lens may be used in the microscope body 10a and the pattern formation optical system 600.

[0135] In the above embodiments, the surgical microscope 10 used in cataract surgery has been described as an example, but the present invention can be applied to various microscopes that project various measurement patterns onto a patient's eye. [Explanation of symbols]

[0136] 10 Surgical microscope 10a Microscope body 12 Control section 14 monitors 16 Control device 18 Memory section 20 First objective lens 21 Front lens 22 Lens insertion / removal mechanism 31L,31R Illumination optical system 31a light source 31b Condenser Lens 40L, 40R observation optical system 50L, 50R Zoom Expander 51, 52, 53 Zoom lens 60L camera 60R Camera 61 Imaging lens 62 Image sensor 63L, 63R eyepiece system 64 Imaging Lens 65 eyepiece 100 OCT units 101 OCT light source 102 Optical Fiber 103 Polarization Controller 104 Optical Fiber 105 Fiber Coupler 110 Optical Fiber 111 Collimator 112 Optical path length correction member 113 Dispersion compensation material 114 Corner Cube 115 Corner cube movement mechanism 116 Collimator 117 Optical Fiber 118 Polarization Controller 119 Optical Fiber 120 Attenuator 121 Optical Fiber 122 Fiber Coupler 123 Optical Fiber 124 Optical Fiber 125 detector 128 Optical Fiber 200 Microscope main body control unit 202 Image acquisition unit 204 Display control unit 206 OCT measurement control unit 208 Image forming unit 210 Data Processing Unit 212 Ring pattern formation control section 214 Eye characteristics calculation section 214a Corneal shape calculation section 214b Eye refractive power calculation unit 216 Guide display control unit 500 OCT optics 501 Optical Fiber 502 Collimator lens unit 503 Optical Scanner 503a, 503b Galvanometer mirror 504 OCT imaging lens 505 Mirror 506 relay lens 507 Mirror 508 Second Objective Lens 600 Pattern Forming Optical System 601 Aiming light source 602 Collimator Lens Unit BSL Beam Splitter BSR Beam Splitter D Observation image DM1, DM2 dichroic mirrors E Patient's eye Ec cornea Ef fundus GP Guide Pattern KC Clock L0 light L1,L2 illumination light LA,LB Return light LC interference light LG Aiming Light LP Ring Pattern LR reference light LS measurement light LS1 Return light O1,O2,O3,OA,OB Optical axis OCT Swept Source OL,OR optical axis RM Reflective Mirror

Claims

1. An objective lens, a first irradiation optical system that irradiates a first light onto a patient's eye through the objective lens, the first irradiation optical system including a front lens that is removably disposed between the objective lens and the patient's eye; a scanning optical system that scans the first light irradiated onto the patient's eye by the first irradiation optical system to generate a measurement pattern; an observation optical system that guides a first return light from the patient's eye onto which the measurement pattern is irradiated, through the objective lens, to at least one of an image pickup element and an eyepiece; Equipped with the first irradiation optical system irradiates the cornea of ​​the patient's eye with the first light through the objective lens when measuring the corneal shape of the patient's eye, and irradiates the fundus of the patient's eye with the first light through the objective lens and the front lens when measuring the ocular refractive power of the patient's eye; The scanning optical system is a microscope that forms a continuous or intermittent ring pattern on the cornea as the measurement pattern when measuring the corneal shape of the patient's eye, and forms a continuous or intermittent ring pattern on the fundus as the measurement pattern when measuring the ocular refractive power of the patient's eye.

2. The microscope according to claim 1, further comprising an eye characteristic calculation unit that calculates the eye characteristics of the patient's eye based on an image of the first returned light captured by the imaging element when the observation optical system guides the first returned light to the imaging element.

3. the first irradiation optical system irradiates the first light onto the cornea of ​​the patient's eye through the objective lens; the scanning optical system forms a continuous or intermittent ring pattern on the cornea as the measurement pattern; 3. The microscope according to claim 2, wherein the eye characteristic calculation unit calculates the corneal shape of the patient's eye as the eye characteristic.

4. the eye characteristic calculation unit calculates the direction of the inferior meridian of the patient's eye as the corneal shape, 4. The microscope according to claim 3, wherein the scanning optical system scans the first light irradiated onto the cornea based on a calculation result of the direction of the most intense meridian by the eye characteristic calculation unit, thereby forming a guide pattern indicating the direction of the most intense meridian on the cornea.

5. An objective lens; a first irradiation optical system that irradiates a first light onto the patient's eye through the objective lens; a scanning optical system that scans the first light irradiated onto the patient's eye by the first irradiation optical system to generate a measurement pattern; an observation optical system that guides a first return light from the patient's eye onto which the measurement pattern is irradiated, through the objective lens, to at least one of an image pickup element and an eyepiece; an ocular characteristic calculation unit that calculates ocular characteristics of the patient's eye based on an image of the first returned light captured by the image sensor when the observation optical system guides the first returned light to the image sensor; Equipped with the first irradiation optical system irradiates the first light onto the cornea of ​​the patient's eye through the objective lens; the scanning optical system forms a continuous or intermittent ring pattern on the cornea as the measurement pattern; the eye characteristic calculation unit calculates a corneal shape of the patient's eye as the eye characteristic, the eye characteristic calculation unit calculates the direction of the inferior meridian of the patient's eye as the corneal shape, the scanning optical system scans the first light irradiated onto the cornea based on the calculation result of the direction of the strongest meridian by the eye characteristic calculation unit, and forms a guide pattern indicating the direction of the strongest meridian on the cornea.

6. the scanning optical system changes the ring diameter of the ring pattern multiple times; each time the scanning optical system changes the ring diameter, the imaging of the first returned light by the imaging element is repeatedly performed; 6. The microscope according to claim 4, wherein the eye characteristic calculation unit calculates the corneal shape based on the captured images for each of the different ring diameters.

7. the first irradiation optical system includes a front lens that is removably disposed between the objective lens and the patient's eye, and irradiates the first light onto the fundus of the patient's eye through the objective lens and the front lens; the scanning optical system generates a continuous or intermittent ring pattern as the measurement pattern; 3. The microscope according to claim 2, wherein the eye characteristic calculation unit calculates the eye refractive power of the patient's eye as the eye characteristic.

8. a second irradiation optical system that irradiates the patient's eye with second light different from the first light through the objective lens, the second irradiation optical system having a common optical system from the scanning optical system to the objective lens; the first irradiation optical system shares the common optical system with the second irradiation optical system; the first irradiation optical system selectively irradiates the patient's eye with the first light, and the second irradiation optical system selectively irradiates the patient's eye with the second light, 8. The microscope according to claim 1, wherein when the second light is irradiated onto the patient's eye by the second irradiation optical system, the scanning optical system scans a predetermined portion of the patient's eye with the second light.

9. the second irradiation optical system has an interference optical system that splits light emitted from a light source into reference light and measurement light that is the second light, and irradiates the measurement light onto the patient's eye through the common optical system; the interference optical system detects interference light between the reference light and second return light incident through the common optical system from the patient's eye irradiated with the measurement light; 9. The microscope according to claim 8, further comprising a tomographic image generating unit that generates a tomographic image of the patient's eye based on a detection signal of the interference light detected by the interference optical system.

10. 8. The microscope according to claim 1, wherein the objective lenses include a first objective lens used in the observation optical system and a second objective lens used in the first illumination optical system.

11. 10. The microscope according to claim 8, wherein the objective lenses include a first objective lens used in the observation optical system, and a second objective lens used in the first illumination optical system and the second illumination optical system.

12. 12. The microscope according to claim 10, wherein a portion of the first objective lens is cut out, and the second objective lens is disposed in the cut-out portion of the first objective lens.

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