JP2018126548A - Ophthalmic surgery device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmic surgery device which can obtain a high-quality observation image and an optical coherence tomography image of a subject eye without impacting an existing configuration.SOLUTION: An ophthalmic surgery device includes: an observation optical system; an illumination optical system; an interference optical system; and an image generating part. The observation optical system is an optical system for observing a subject eye through an object lens. The illumination optical system is an optical system for illuminating the subject eye through the object lens. The interference optical system includes a signal light path and a reference light path guided to the subject eye through a deflection member provided between the object lens and the subject eye, and detects an interference light based on a return light from the subject eye via the signal light path and the reference light via the reference light path. The image generating part generates an image of the subject eye based on the detection result of the interference optical system. When the deflection member is placed on an illumination light path, the strength of the illumination light is controlled such that an attenuation amount of observation light is canceled.SELECTED DRAWING: Figure 2

Description

  The present invention relates to an ophthalmic surgical apparatus used for ophthalmic surgery.

  Various operations are performed in the ophthalmology field. Typical examples include cataract surgery and retinal vitreous surgery. In such an operation in the ophthalmic field, an ophthalmic surgical apparatus is used. The ophthalmologic surgical apparatus is an apparatus for observing the operated eye illuminated by the illumination optical system with the naked eye or taking an image through the observation optical system.

  Such an ophthalmic surgical apparatus includes an OCT apparatus for acquiring an OCT image of an eye to be operated using optical coherence tomography (hereinafter referred to as OCT) (for example, Patent Documents 1 to 3).

  The ophthalmic surgical apparatus disclosed in Patent Documents 1 to 3 has a configuration in which a beam combiner for acquiring an OCT image is arranged in an observation optical path between an objective lens and a variable power lens system. The beam combiner deflects signal light for acquiring an OCT image of the eye to be operated toward the objective lens using OCT.

Japanese Patent No. 3789960 Japanese Patent No. 4091143 JP 2006-95318 A

  However, in the ophthalmic surgical apparatus disclosed in Patent Literature 1 to Patent Literature 3, a beam combiner is disposed in the observation optical path between the variable power lens system and the objective lens, and thus light guided through the observation optical system (observation light) ) Is attenuated, and the observation image of the eye to be operated becomes dark and affects the observation image. Further, in order to minimize the influence on the observation image, it is considered that a new device is required for the coating of the optical element.

  Furthermore, the ophthalmic surgical apparatus may be provided with a port for connecting an assistant's microscope or the like for the operator's assistant to observe the eye to be operated. In this case, if an OCT optical system is connected to an existing port, another optical system cannot be connected to the port. Therefore, it is necessary to add a new port for connecting the OCT optical system in addition to the existing port.

  The present invention has been made to solve the above-described problems, and ophthalmic surgery capable of acquiring a high-quality observation image and OCT image of the operated eye without affecting the existing configuration. An object is to provide an apparatus.

The invention according to claim 1 is an observation optical system for observing the operated eye through the objective lens, an illumination optical system for illuminating the operated eye through the objective lens, and the objective lens And a reference light path guided to the eye via a deflection member disposed between the eye and the eye to be operated, and a return light from the eye to be operated via the signal light path and the reference light path An interference optical system that detects interference light based on reference light that has passed through a reference optical path; and an image forming unit that forms an image of the eye to be operated based on a detection result by the interference optical system, and the deflection member Can be inserted into and removed from the illumination optical path formed by the illumination optical system, and when the deflection member is disposed in the illumination optical path, the attenuation of light guided through the observation optical system is canceled. Of light guided through the illumination optical system Degree is controlled, a ophthalmic surgical device.
The invention according to claim 2 is the ophthalmic surgical apparatus according to claim 1, wherein the deflection member is formed from at least one of an optical path formed by the observation optical system and an optical path formed by the illumination optical system. It is placed at a position that is off.
The invention according to claim 3 is the ophthalmic surgical apparatus according to claim 1 or 2, wherein the deflecting member includes an optical path formed by the observation optical system and an optical path formed by the illumination optical system. It is a beam splitter arrange | positioned at at least one.
The invention according to claim 4 is the ophthalmic surgical apparatus according to claim 3, wherein the beam splitter is a dichroic mirror arranged in an optical path formed by the observation optical system.
The invention according to claim 5 is the ophthalmic surgical apparatus according to claim 3, wherein the beam splitter is a dichroic mirror or a half mirror arranged in an optical path formed by the illumination optical system.
The invention according to claim 6 is the ophthalmic surgical apparatus according to any one of claims 1 to 5, wherein the first optical unit in which at least a part of the interference optical system is stored is At least, it is formed as an attachment that can be attached to and detached from the main body holding the objective lens.
The invention according to claim 7 is the ophthalmic surgical apparatus according to claim 6, wherein the interference optical system splits light from a light source into signal light and reference light, and the signal A scanning unit for scanning the eye to be operated with light guided through an optical path, and interference between the return light from the operated eye of the signal light passing through the signal light path and the reference light passing through the reference light path The deflection member is disposed between the eye to be operated and the scanning unit, and the first optical unit stores at least the scanning unit and the deflection member.
The invention according to claim 8 is the ophthalmic surgical apparatus according to claim 7, in which the optical path of visible light from a visible light source and the signal optical path are located at a position between the dividing section and the scanning section. Includes a synthesis unit to synthesize.
The invention according to claim 9 is the ophthalmic surgical apparatus according to claim 7 or claim 8, wherein the first optical unit is disposed between the scanning section and the deflecting member from the signal light path. The imaging unit arranged in the branched optical path is further stored.
The invention described in claim 10 is the ophthalmic surgical apparatus according to claim 9, and includes a scanning control unit that controls the scanning unit based on an image acquired by the imaging unit.
An eleventh aspect of the present invention is the ophthalmic surgical apparatus according to the tenth aspect, wherein the first optical unit further stores the scanning control unit.
The invention according to claim 12 is the ophthalmic surgical apparatus according to any one of claims 7 to 11, wherein at least a part of the dividing part and the interference part is a second optical unit. The first optical unit and the second optical unit are connected by light guiding means.
The invention according to claim 13 is the ophthalmic surgical apparatus according to any one of claims 6 to 12, wherein the first connection portion provided in the main body portion and the first optical device. The first optical unit is attached to the main body by being connected to a second connection provided on the unit, and the first connection is provided on an attachment different from the first optical unit. It is configured to be connectable with three connecting portions.
The invention according to claim 14 is the ophthalmic surgical apparatus according to any one of claims 6 to 13, further comprising a control unit that controls the observation optical system and the illumination optical system. And the control section controls the interference optical system when the first optical unit is mounted on the main body section.
The invention according to claim 15 is the ophthalmic surgical apparatus according to any one of claims 1 to 5, wherein at least the deflection member is stored in a third optical unit, and the interference At least a part of the optical system is stored in the fourth optical unit, and the fourth optical unit is attached to and detached from the third optical unit that is attached to at least the main body that holds the objective lens.
The invention according to claim 16 is the ophthalmic surgical apparatus according to any one of claims 1 to 15, further comprising a mechanism for moving the deflection member.

  According to the ophthalmic surgical apparatus according to the present invention, it is possible to acquire high-quality observation images and OCT images without affecting the existing configuration.

Schematic which shows an example of the external appearance structure of the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the OCT apparatus in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the OCT unit in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the control system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment. Schematic showing an example of a structure of the optical system in the ophthalmic surgery apparatus of embodiment.

  An example of an embodiment of an ophthalmic surgical apparatus and an ophthalmic surgical attachment according to the present invention will be described in detail with reference to the drawings. The ophthalmic surgical apparatus according to the following embodiments is used in ophthalmic surgery. The ophthalmic surgical apparatus according to the embodiment is an apparatus that obtains an observation image of the operated eye by illuminating the operated eye (patient eye) with an illumination optical system and causing the reflected light to enter the observation optical system. The ophthalmic surgical attachment is configured to be detachable from an ophthalmic observation apparatus that can be used in ophthalmic surgery.

  The ophthalmic surgical apparatus according to the following embodiment is configured to attach an attachment (first optical unit) including at least a part of an optical system of OCT to an ophthalmic surgical microscope (main body part), so that an OCT image of an eye to be operated can be obtained. Acquisition becomes possible. The region to be imaged may be an arbitrary region of the operated eye. For example, the anterior eye may be a cornea, a vitreous body, a crystalline lens, a ciliary body, or the like, and the posterior eye may be a retina or It may be choroid or vitreous. Further, the imaging target region may be a peripheral region of the eye such as a eyelid or an eye socket. By a known method, it is possible to form a cross-sectional image or a three-dimensional image of the operated eye based on the return light of the signal light passing through the attachment. In this specification, images acquired by OCT may be collectively referred to as OCT images. In addition, a measurement operation for forming an OCT image may be referred to as OCT measurement. In addition, it is possible to use suitably the description content of the literature described in this specification as the content of the following embodiment.

  In the following embodiment, a configuration to which Fourier domain type OCT is applied will be described. In particular, the ophthalmic surgical apparatus according to the embodiment can acquire an OCT image of the operated eye using a known swept source OCT technique.

  It is also possible to apply the configuration according to the present invention to an ophthalmic surgical apparatus using a type other than the swept source, for example, a spectral domain OCT technique. In the following embodiments, an OCT apparatus including an OCT optical system and an ophthalmic surgical microscope will be described. However, an ophthalmic observation apparatus other than an ophthalmic surgical microscope, for example, a scanning laser opthalmoscope (Scanning Laser Ophthalmoscope). : SLO), a slit lamp, a fundus camera, and the like can be combined with an OCT apparatus having the configuration according to the present invention.

<First Embodiment>
[Appearance structure]
FIG. 1 shows an external configuration of an ophthalmic surgical apparatus according to this embodiment. The ophthalmic surgical apparatus 40 includes the ophthalmic surgical microscope 1 and the OCT apparatus 15. The microscope for ophthalmic surgery 1 includes a support column 2, a first arm 3, a second arm 4, a driving device 5, a microscope 6, a support unit 7, a foot switch 8, and a display unit 90. The microscope 6 has an illumination optical system for illuminating the surgical eye E, and an observation optical system for forming an observation image from the reflected light of the surgical eye E with respect to the illumination light by the illumination optical system.

  The OCT apparatus 15 includes an interference optical system and an image forming unit. The interference optical system divides the light from the light source into signal light and reference light, and the reference light that is the return light of the signal light from the operated eye E and the reference light is transmitted through the signal light path that is the optical path of the signal light. Interference light based on the reference light passing through the optical path is detected. The image forming unit forms an OCT image based on the detected interference light. The OCT apparatus 15 includes a first optical unit 16 and a second optical unit 17, and an optical element for forming an OCT image is stored in one of the two units. The first optical unit 16 is detachably provided on the microscope 6. The second optical unit 17 is provided on the upper part of the second arm 4 that supports the microscope 6. The first optical unit 16 and the second optical unit 17 are connected by an optical fiber (light guide means).

  A mechanism for moving the second arm 4 in a three-dimensional manner relative to the first arm 3 is provided between the first arm 3 and the second arm 4. It is also possible to provide a mechanism that allows the microscope 6 to rotate in the horizontal direction at the attachment position of the microscope 6 with respect to the arm that extends downward from the driving device 5. These mechanisms and the drive device 5 correspond to a mechanism for changing the position and orientation of the microscope 6 (main body part). In general, an operator performs an operation in a position on the parietal side or ear side of a patient. The microscope 6 is placed above the eye E with the eyepiece facing the operator. In “the direction of the microscope 6”, the direction of the eyepiece lens with respect to the patient, the direction of the eyepiece lens with respect to the optical axis of the optical system (for example, the objective lens), the position of the operator with respect to the patient, etc. It includes the concept of

  The drive device 5 includes an actuator such as a motor. The drive device 5 moves the microscope 6 in the vertical direction and the horizontal direction according to the operation using the operation lever 8a of the foot switch 8. Thereby, the microscope 6 can be moved three-dimensionally.

  Various optical systems and drive systems are accommodated in the lens barrel 10 of the microscope 6. An inverter unit 12 is provided on the upper portion of the lens barrel unit 10. When the observation image of the eye E is obtained as an inverted image, the inverter unit 12 converts the observation image into an erect image. A pair of left and right eyepieces 11 </ b> L and 11 </ b> R are provided on the upper portion of the inverter unit 12. An observer (operator or the like) can view the operated eye E binocularly by looking into the left and right eyepieces 11L and 11R.

  The microscope 6 (lens barrel part 10) is provided with a first optical unit 16 which is detachable. The first optical unit 16 is an attachment that stores at least a part of the interference optical system. In this embodiment, the first optical unit 16 includes at least a deflecting member for deflecting signal light for acquiring an OCT image in the direction of the eye E to be operated. The microscope 6 is an example of a “main body”.

  A front lens 13 is connected to the microscope 6 via a holding arm. The front lens 13 is configured to be insertable / removable at a position on the optical axis of the objective lens provided at the lower end of the lens barrel 10. In particular, when observing the eye E, the front lens 13 can be disposed at a position between the front focal position of the objective lens and the eye E. The front lens 13 focuses the illumination light and illuminates the intraocular region of the eye E (the posterior eye portion such as the retina and vitreous body). As the front lens 13, a plurality of lenses having different refractive powers (for example, 40D, 80D, 120D, etc.) are prepared, and these are alternatively used.

  An intraoperative observation monitor 14 is provided on the upper part of the lens barrel 10. For example, a moving image of an observation image and a live image of an OCT image are displayed on the intraoperative observation monitor 14. The moving image of the observation image and the live image of the OCT image are acquired by the OCT apparatus 15. Note that the moving image of the observation image may be acquired by the microscope 1 for ophthalmic surgery. It is also possible to display on the intraoperative observation monitor 14 any information that can be referred to in the operation, such as information obtained by preoperative diagnosis or past operation. Such information is acquired from a hospital system such as an electronic medical record system or an image archive system via a network such as a LAN. The intraoperative observation monitor 14 may be configured to be removable, and may be a general-purpose tablet terminal or the like.

  The support 2 supports the support portion 7. The support unit 7 supports the display unit 90 so that the screen orientation can be changed in an arbitrary direction. For example, an OCT image (still image) obtained by capturing a live image by the OCT apparatus 15 is displayed on the display unit 90. In addition, an arbitrary image acquired by the ophthalmic surgical microscope 1 or the OCT apparatus 15 can be displayed on the display unit 90. Furthermore, any information that can be referred to in the operation, such as information acquired by preoperative diagnosis or past operation, can be displayed on the display unit 90. The display unit 90 and the intraoperative observation monitor 14 may be provided with an operation unit capable of performing the same operation as the foot switch 8.

  According to such a configuration, the surgeon can perform an operation while observing a cross-sectional image of a region to be operated during the operation.

〔Constitution〕
[Ophthalmic surgery microscope]
2 and 3 show the optical system of the microscope 1 for ophthalmic surgery. FIG. 2 is a view of the optical system viewed from the left side as viewed from the operator. FIG. 3 is a view of the optical system viewed from the operator side. In addition to the configuration shown in FIGS. 2 and 3, an optical system (assistant microscope) can be provided for the operator's assistant to observe the eye E. 2 and 3 also show the deflecting member 100 stored in the first optical unit 16. The deflection member 100 is a member for deflecting signal light from the outside of the optical system of the ophthalmic surgical microscope 1 in the direction of the eye E to be operated.

  In this embodiment, the directions such as up and down, left and right, and front and rear are directions seen from the operator side unless otherwise specified. In addition, about the up-down direction, let the direction which goes to the observation object (operated eye E) from the objective lens 19 be a downward direction, and let this opposite direction be an upper direction. Generally, since a patient undergoes surgery in a supine state, the vertical direction and the vertical direction are the same.

  The optical system of the microscope for ophthalmologic surgery 1 includes an illumination optical system 20 and an observation optical system 30.

  As shown in FIG. 3, the observation optical system 30 is provided in a pair of left and right. The left observation optical system 30L is called a left observation optical system, and the right observation optical system 30R is called a right observation optical system. Symbol OL indicates the optical axis (observation optical axis) of the left observation optical system 30L, and symbol OR indicates the optical axis (observation optical axis) of the right observation optical system 30R. The left and right observation optical systems 30L and 30R are arranged so as to sandwich the optical axis O (see FIG. 2) of the objective lens 19.

  The left and right observation optical systems 30L and 30R are a variable power lens system 31, a beam splitter 32 (only the right observation optical system 30R), an imaging lens 33, an image erecting prism 34, an eye width adjustment prism 35, and a field stop 36, respectively. And an eyepiece 37.

  The zoom lens system 31 includes a plurality of zoom lenses 31a, 31b, and 31c. Each zoom lens 31a to 31c can be moved in a direction along the observation optical axis OL (or the observation optical axis OR) by a zoom mechanism (not shown). Thereby, the magnification at the time of observing or photographing the eye E is changed.

  The beam splitter 32 of the right observation optical system 30R separates a part of the observation light guided from the operated eye E along the observation optical axis OR and guides it to the photographing optical system. The photographing optical system includes an imaging lens 54, a reflection mirror 55, and a television camera 56.

  The television camera 56 includes an image sensor 56a. The image pickup device 56a is configured by, for example, a charge coupled devices (CCD) image sensor, a complementary metal oxide semiconductor (CMOS) image sensor, or the like. As the image sensor 56a, an element having a two-dimensional light receiving surface (area sensor) is used.

  When the microscope for ophthalmic surgery 1 is used, the light receiving surface of the imaging device 56a is, for example, a position optically conjugate with the surface of the cornea of the eye E to be operated or a depth from the apex of the cornea by ½ of the corneal curvature radius. It is arranged at a position optically conjugate with a position away in the vertical direction.

  The image erecting prism 34 converts the inverted image into an erect image. The eye width adjustment prism 35 is an optical element for adjusting the distance between the left and right observation lights according to the eye width of the operator (the distance between the left eye and the right eye). The field stop 36 blocks the peripheral region in the cross section of the observation light and limits the operator's visual field.

  As shown in FIG. 2, the illumination optical system 20 includes an illumination light source 21, an optical fiber 21a, an exit aperture stop 26, a condenser lens 22, an illumination field stop 23, a slit plate 24, a collimator lens 27, and an illumination prism 25. Is done.

  The illumination field stop 23 is provided at a position optically conjugate with the front focal position of the objective lens 19. The slit hole 24a of the slit plate 24 is formed at a position optically conjugate with the front focal position.

  The illumination light source 21 is provided outside the lens barrel 10 of the microscope 6. One end of an optical fiber 21 a is connected to the illumination light source 21. The other end of the optical fiber 21 a is disposed at a position facing the condenser lens 22 in the lens barrel 10. The illumination light output from the illumination light source 21 is guided by the optical fiber 21 a and enters the condenser lens 22.

  An exit aperture stop 26 is provided at a position facing the exit port (fiber end on the condenser lens 22 side) of the optical fiber 21a. The exit aperture stop 26 acts to shield a partial region of the exit port of the optical fiber 21a. When the shielding area by the exit aperture stop 26 is changed, the emission area of the illumination light is changed. Thereby, the irradiation angle by the illumination light, that is, the angle formed by the incident direction of the illumination light with respect to the eye E to be operated and the optical axis O of the objective lens 19 can be changed.

  The slit plate 24 is formed of a disk-shaped member having a light shielding property. The slit plate 24 is provided with a light-transmitting portion including a plurality of slit holes 24 a having a shape corresponding to the shape of the reflecting surface 25 a of the illumination prism 25. The slit plate 24 is moved in a direction perpendicular to the illumination optical axis O ′ (direction of a double-headed arrow B shown in FIG. 2) by a driving mechanism (not shown). Thereby, the slit plate 24 is inserted into and removed from the illumination optical axis O ′.

  The collimator lens 27 converts the illumination light that has passed through the slit hole 24a into a parallel light flux. The illumination light that has become a parallel light beam is reflected by the reflecting surface 25 a of the illumination prism 25 and projected onto the eye E through the objective lens 19. Illumination light (a part) projected onto the eye E is reflected by the cornea. Reflected light of illumination light (sometimes referred to as observation light) by the eye E to be operated enters the observation optical system 30 via the objective lens 19. With such a configuration, an enlarged image of the eye E can be observed.

  In this embodiment, when the first optical unit 16 is attached to the lens barrel 10 of the microscope 6, the deflection member 100 stored in the first optical unit 16 is located between the objective lens 19 and the eye E to be operated. Be placed. Specifically, the deflecting member 100 is disposed at a position separated by a distance d (provided that d ≧ 0) perpendicular to the optical axis O from a predetermined position on the operated eye E side on the optical axis O of the objective lens 19. The The deflecting member 100 is disposed so as to deviate from the optical path (observation optical path) formed by the observation optical system 30. In this embodiment, the deflecting member 100 is disposed at a position deviated from both the observation optical axis OL and the observation optical axis OR, and is disposed on the optical axis O of the objective lens 19. A part of the deflection member 100 may be arranged so as to enter an observation optical path or an optical path (illumination optical path) formed by the illumination optical system 20. When the deflection member 100 is disposed in the illumination optical path, the intensity of the illumination light can be controlled so that the attenuation of the observation light is canceled. Therefore, when the brightness of the acquired image is not important, or when the illumination light can be controlled, the deflecting member 100 may be arranged in the illumination optical path. On the other hand, when the deflecting member 100 is arranged in the observation optical path, the brightness of the naked eye observation image and the captured image is reduced due to attenuation of the observation light, which may adversely affect the observation of the eye E to be operated. Therefore, it is desirable that the deflecting member 100 is arranged so as not to enter the observation optical path as much as possible. Such a deflection member 100 includes a beam splitter, a half mirror, or a dichroic mirror.

  The observation optical system 30 is an example of an “observation optical system” according to this embodiment. The illumination optical system 20 is an example of an “illumination optical system” according to this embodiment.

[OCT equipment]
FIG. 4 shows a block diagram of a configuration example of the OCT apparatus 15. 4, parts that are the same as those in FIG. 1 are given the same reference numerals, and descriptions thereof will be omitted as appropriate. In FIG. 4, the objective lens 19 and its optical axis O are also shown.

  In this embodiment, in order to enable the operator to identify the scanning position of the signal light for OCT measurement without taking his eyes off the eyepiece, the aiming light, which is visible light, is applied to the operated eye E together with the signal light. It is possible to irradiate. It is also possible to confirm the scanning position of the signal light from the display image by acquiring a visible image (an image photographed using visible light) while projecting the aiming light onto the eye E to be operated. In addition, in the case where a configuration excluding observation of the scanning position of the signal light through the eyepiece (that is, with the naked eye) is applied, invisible light (such as infrared light) can be used as the aiming light. It is. In addition, when aiming light composed of invisible light is applied, a trajectory of aiming light is identified from an invisible image (an image taken using invisible light), and an image representing the position and orientation of the trajectory is separately provided. It is also possible to configure such that it is presented within an acquired image (such as a visible image) or a visual field for visual observation.

  The first optical unit 16 is formed as an attachment that can be attached to and detached from the microscope 6 that holds at least the objective lens 19. In this embodiment, the first optical unit 16 includes the deflection member 100, the focus lens 101, the beam splitter 102, the filter 103, the condenser lens 104, the CCD image sensor 105, and the arithmetic control unit 106. The scanning unit 107, the scanning control unit 108, and the combining unit 109 are configured. The first optical unit 16 does not need to be configured to include all of the above members, and may store at least the scanning unit 107 and the deflection member 100, for example. Further, for example, other units (for example, the second optical unit 17) other than the first optical unit 16 may be configured to include the calculation control unit 106. It is also possible to apply a configuration in which at least a part of the function of the arithmetic control unit 106 is assigned to the arithmetic control device (arithmetic control means) provided in the microscope 1 for ophthalmic surgery.

  The second optical unit 17 includes an OCT unit 150, an arithmetic control unit 200, and a visible light source unit 201. The visible light source unit 201 may be included in a unit other than the second optical unit 17 (for example, the first optical unit 16). A display unit 90 is connected to the second optical unit 17. Further, the intraoperative observation monitor 14 of FIG. 1 is connected to the second optical unit 17.

  The deflection member 100 is disposed on the optical axis O of the objective lens 19 so as to be out of the observation optical path, but may be disposed at a position deviated from at least one of the observation optical path and the illumination optical path. Such a deflection member 100 may be a beam splitter (half mirror) disposed in at least one of the observation optical path and the illumination optical path. The deflecting member 100 deflects the signal light guided along the signal light path in the direction of the eye E to be operated and deflects the return light of the signal light from the eye E to be operated in the direction of the focus lens 101.

  In this embodiment, a moving image is acquired based on a detection signal obtained by the CCD image sensor 105 of the first optical unit 16. This moving image photographing is performed using, for example, infrared light or red free light. Here, the red free light is light obtained by removing a red component from visible light.

  When photographing with infrared light, for example, means for projecting infrared light to the eye E to be operated is provided around the front lens 13, and a dichroic mirror is employed as the deflecting member 100. In this case, the deflecting member 100 reflects at least the light in the wavelength band used for OCT measurement and the wavelength band of the infrared light among the reflected light of the eye E to be operated, and is for observation in the wavelength band of visible light. Of light. The means for projecting infrared light includes, for example, one or more infrared LEDs, and the installation position is not limited to the periphery of the front lens 13, but the periphery of the objective lens 19 or the objective lens 19 and the eye to be operated. It may be a position between E and the like. In addition, a half mirror can be used as the deflecting member 100.

  When shooting with red-free light, a half mirror is employed as the deflecting member 100.

  In the optical path for OCT measurement, a combining unit 109, a scanning unit 107, a beam splitter 102, and a focus lens 101 are provided in this order from the OCT unit 150 side.

  An OCT unit 150 is connected to the combining unit 109 via an optical fiber. A visible light source unit 201 is connected to the combining unit 109 via an optical fiber. The visible light source unit 201 outputs aiming light including visible light (for example, light having a center wavelength of 633 nm). The aiming light output from the visible light source unit 201 is guided to the combining unit 109. Signal light for OCT measurement (for example, light having a center wavelength of 1050 nm) from the OCT unit 150 is guided to the combining unit 109. The combining unit 109 combines the optical path for OCT measurement and the optical path of aiming light. That is, the combining unit 109 combines the optical path of visible light from the visible light source unit 201 with the signal optical path at a position between the dividing unit and the scanning unit 107. Such a combining unit 109 is configured by a fiber coupler. The synthesizing unit 109 is an example of a “synthesizing unit” according to this embodiment. Hereinafter, the optical path combined by the combining unit 109 will also be described as a new optical path for OCT measurement.

  In addition, it is possible to prevent the detection efficiency of the OCT measurement signal light from being lowered by preventing the return light of the OCT measurement signal light from the operated eye E from entering the visible light source unit 201. .

  The light combined by the combining unit 109 is converted into a parallel light beam by a collimator (not shown) and enters the scanning unit 107. The scanning unit 107 changes the traveling direction of light (signal light) that passes through the optical path for OCT measurement. Thereby, the eye E can be scanned with the signal light. The scanning unit 107 includes, for example, a galvanometer mirror that scans signal light in the x direction, a galvanometer mirror that scans in the y direction orthogonal to the x direction, and a mechanism that drives these independently. Thereby, the signal light can be scanned in an arbitrary direction on the xy plane.

  Further, the scanning unit 107 changes the traveling direction of the aiming light guided along the signal light path. As a result, the eye E can be irradiated with the aiming light. By configuring the scanning unit 107 as described above, the aiming light can be scanned in an arbitrary direction on the xy plane. The aiming light irradiation timing (timing at which the user can visually recognize the OCT scanning range) is not only at the time of OCT measurement, but also when setting the scanning range, or when checking the already scanned range. Also good.

  Such a scanning unit 107 can be realized by a known optical scanner. The scanning unit 107 is an example of a “scanning unit”.

  The beam splitter 102 branches the optical path for tracking from the optical path for OCT measurement. Specifically, the beam splitter 102 branches the optical path for tracking from the optical path of the return light from the operated eye E of the signal light for OCT measurement. In the optical path for tracking, a filter 103, a condensing lens 104, and a CCD image sensor 105 are provided in this order from the beam splitter 102 side.

  When infrared imaging is performed using the CCD image sensor 105 while irradiating the eye E with infrared light and visible light, the filter 103 has a filter characteristic that transmits infrared light. Thereby, the light passing through the optical path for tracking branched by the beam splitter 102 passes through the filter 103 and becomes infrared light. On the other hand, when infrared imaging is performed using the CCD image sensor 105 while irradiating the eye E with infrared light, the light that passes through the tracking optical path branched by the beam splitter 102 is directly used as it is. (That is, the filter 103 is not required). In this case, the beam splitter 102 is configured to transmit the wavelength band corresponding to the signal light and reflect the wavelength band of the infrared light for tracking. As a specific example, a beam splitter 102 (dichroic mirror) having a characteristic of separating signal light having a wavelength longer than that of infrared light for tracking is applied.

  In addition, when performing red-free photographing using the CCD image sensor 105 while irradiating the operating eye E with visible light, a case where the aiming light is not projected onto the operating eye E and an aiming light is projected onto the operating eye E. The case is configured as follows.

  In the case where the aiming light is not projected onto the surgical eye E, the filter 103 has a filter characteristic that blocks a red component contained in visible light. As a result, the visible light that passes through the optical path for tracking branched by the beam splitter 102 passes through the filter 103 and becomes red-free light. It is also possible to apply a light source capable of outputting red-free light. In that case, red-free shooting is performed using the CCD image sensor 105 while irradiating the eye E with red-free light. In this case, the filter 103 is not necessary.

  On the other hand, in the case where the aiming light is projected onto the eye E to be operated, a half mirror is employed as both the deflecting member 100 and the beam splitter 102, and the filter 103 blocks the red component contained in the visible light. Has filter characteristics. As a result, the visible light that passes through the optical path for tracking branched by the beam splitter 102 passes through the filter 103 and becomes red-free light. Alternatively, the beam splitter 102 has an optical characteristic that transmits infrared light and a red component of visible light and reflects green and blue components (that is, components other than the red component) of visible light. Also good. It is also possible to apply a light source capable of outputting red-free light. In that case, red-free shooting is performed using the CCD image sensor 105 while irradiating the eye E with red-free light. In this case, the filter 103 is not necessary.

  Note that, for example, in order to perform moving image shooting with light in an optimum wavelength band according to the observation site, it may be configured to be able to switch between infrared shooting and red-free shooting. Control for that purpose may include, for example, switching of the light source, switching of the output wavelength from the light source, switching of the filter 103, and the like.

  Thus, the light transmitted through the filter 103 is focused on the light receiving surface of the CCD image sensor 105 by the condenser lens 104. The CCD image sensor 105 detects light transmitted through the filter 103 at a predetermined frame rate, for example. The CCD image sensor 105 is arranged in an optical path branched from the signal optical path between the scanning unit 107 and the deflecting member 100. On the intraoperative observation monitor 14, an image (observation image) based on the light transmitted through the filter 103 detected by the CCD image sensor 105 is displayed as a live image. The CCD image sensor 105 is an example of an “imaging unit” according to this embodiment.

  The arithmetic control unit 106 receives an image signal based on the light detected by the CCD image sensor 105 at a time interval corresponding to the frame rate. The arithmetic control unit 106 performs arithmetic processing for performing tracking control based on these image signals (observation images). For example, the arithmetic control unit 106 obtains a displacement of another observation image with respect to a predetermined reference observation image for a plurality of observation images acquired in time series. The reference observation image may be, for example, an observation image obtained at a predetermined timing (such as when observation is started or when the observation range is fixed). The process for obtaining the displacement includes, for example, a process for obtaining the displacement (affine transformation matrix or the like) between the feature region in the reference observation image and the feature region in another observation image. Further, the arithmetic control unit 106 generates a control signal based on the obtained displacement, and sends this control signal to the scanning control unit 108. This control signal includes, for example, control details for changing the current scanning range by the signal light to a new scanning range in which the displacement is canceled. In addition, the arithmetic control unit 106 obtains the sum of differences in pixel units of other observation images with respect to the reference observation image, and outputs a control signal for minimizing the sum of the differences to the scanning control unit 108. May be.

  The arithmetic control unit 106 includes, for example, an FPGA (Field-Programmable Gate Array) or a GPU (Graphical Processor Unit), a communication interface, and the like. The arithmetic control unit 106 may include a (CPU (Central Processor Unit), a RAM (Random Access Memory), a ROM (Read Only Memory), a hard disk drive, a communication interface, and the like. The storage device stores a computer program for controlling the arithmetic control unit 106. The arithmetic control unit 106 may include various circuit boards, for example, a circuit board for forming an OCT image.

  The scanning control unit 108 controls at least one direction of the galvano mirror that scans the signal light in the x direction and the galvano mirror that scans the signal light in the y direction, and a change timing of the direction based on a control signal from the arithmetic control unit 106. . The scanning control unit 108 is an example of a “scanning control unit” according to this embodiment. The above series of processing is repeatedly executed at time intervals corresponding to the frame rate of the CCD image sensor 105. This time interval may be equal to the frame rate or may be an integral multiple of the frame rate (that is, it may be a thinning process). Thereby, the scanning range of the signal light can be made to follow the movement of the eye E to be operated in real time.

  The signal light passing through the optical path for OCT measurement passes through the beam splitter 102 and the focus lens 101 together with the aiming light, and is guided to the operated eye E by the deflecting member 100. The backscattered light of the signal light from the fundus or the like travels in the reverse direction on the same path as the forward path and reaches the OCT unit 150 or the CCD image sensor 105. Further, the reflected light of the aiming light from the fundus is transmitted through the deflecting member 100 and is incident on the observation optical system 30.

[OCT unit]
FIG. 5 shows an example of the configuration of the OCT unit 150. The OCT unit 150 is provided with an optical system for acquiring an OCT image of the surgical eye E. This optical system has the same configuration as a conventional swept source type OCT apparatus. That is, this optical system includes a splitting unit that splits light from a wavelength scanning (wavelength sweep) light source into signal light and reference light, signal light that passes through the eye to be operated, and reference light that passes through the reference light path. Is an interference optical system that includes an interference unit and detects interference light generated by the interference unit. The interference optical system may further include a scanning unit 107 for scanning the eye E with the light guided through the signal optical path. The detection result (detection signal) of the interference light in the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit 200.

  The light source unit 151 is configured to include a wavelength scanning type (wavelength sweep type) light source capable of scanning (sweeping) the wavelength of the emitted light, similarly to a general swept source type OCT apparatus. The light source unit 151 temporally changes the output wavelength in the near-infrared wavelength band that cannot be visually recognized by the human eye. The light output from the light source unit 151 is indicated by a symbol L0.

  The light L0 output from the light source unit 151 is guided to the polarization controller 153 by the optical fiber 152 and the polarization state thereof is adjusted. The polarization controller 153 adjusts the polarization state of the light L0 guided through the optical fiber 152, for example, by applying stress from the outside to the looped optical fiber 152.

  The light L0 whose polarization state is adjusted by the polarization controller 153 is guided to the fiber coupler 155 by the optical fiber 154, and is divided into the signal light LS and the reference light LR.

  The reference light LR is guided to the collimator 161 by the optical fiber 160 and becomes a parallel light beam. The reference light LR that has become a parallel light beam is guided to the corner cube 164 via the optical path length correction member 162 and the dispersion compensation member 163. The optical path length correction member 162 acts as a delay unit for matching the optical path lengths (optical distances) of the reference light LR and the signal light LS. The dispersion compensation member 163 functions as dispersion compensation means for matching the dispersion characteristics of the reference light LR and the signal light LS.

  The corner cube 164 folds the traveling direction of the reference light LR that has become a parallel light beam by the collimator 161 in the reverse direction. The optical path of the reference light LR incident on the corner cube 164 and the optical path of the reference light LR emitted from the corner cube 164 are parallel. Further, the corner cube 164 is movable in a direction along the incident optical path and the outgoing optical path of the reference light LR. By this movement, the length of the optical path (reference optical path) of the reference light LR is changed.

  The reference light LR that has passed through the corner cube 164 passes through the dispersion compensation member 163 and the optical path length correction member 162, is converted from a parallel light beam into a focused light beam by the collimator 166, enters the optical fiber 167, and is guided to the polarization controller 168. Accordingly, the polarization state of the reference light LR is adjusted.

  For example, the polarization controller 168 has the same configuration as the polarization controller 153. The reference light LR whose polarization state is adjusted by the polarization controller 168 is guided to the attenuator 170 by the optical fiber 169, and the light quantity is adjusted under the control of the arithmetic control unit 200. The reference light LR whose light amount is adjusted by the attenuator 170 is guided to the fiber coupler 172 by the optical fiber 171.

  The signal light LS generated by the fiber coupler 165 is guided to the first optical unit 16 through the optical fiber 177. The signal light LS incident on the first optical unit 16 reaches the deflecting member 100 via the combining unit 109, the scanning unit 107, the beam splitter 102, and the focus lens 101. Then, the signal light LS is reflected by the deflecting member 100 and irradiated to the eye E to be operated. The signal light LS is scattered (including reflection) at various depth positions of the operated eye. The backscattered light of the signal light LS from the eye to be operated travels in the same direction as the forward path in the reverse direction, is guided to the fiber coupler 155, and reaches the fiber coupler 172 via the optical fiber 178.

  The fiber coupler 172 combines (interferes with) the signal light LS incident via the optical fiber 178 and the reference light LR incident via the optical fiber 171 to generate interference light. The fiber coupler 172 generates a pair of interference lights LC by branching the interference light between the signal light LS and the reference light LR at a predetermined branching ratio (for example, 50:50). The pair of interference lights LC emitted from the fiber coupler 172 are guided to the detector 175 through the optical fibers 173 and 174, respectively.

  The detector 175 is, for example, a balanced photodiode (hereinafter referred to as BPD) that has a pair of photodetectors that respectively detect a pair of interference lights LC and outputs a difference between detection results obtained by these. The detector 175 sends the detection result (detection signal) to the arithmetic control unit 200. The arithmetic control unit 200 forms a tomographic image by performing Fourier transform or the like on the spectrum distribution based on the detection result obtained by the detector 175 for each series of wavelength scans (for each A line), for example. The arithmetic control unit 200 causes the display unit 90 to display the formed image.

  In this embodiment, a Michelson type interferometer is employed, but any type of interferometer such as a Mach-Zehnder type can be appropriately employed. In this embodiment, the interference optical system includes fiber couplers 155 and 172, a detector 175, and an optical fiber and various optical elements that guide the reference light LR and the signal light LS therebetween. The interference optical system may further include a light source unit 151. This interference optical system is an example of the “interference optical system” in this embodiment.

[Calculation control unit]
The configuration of the arithmetic control unit 200 will be described. The arithmetic control unit 200 analyzes the detection signal input from the detector 175 and forms an OCT image of the eye to be operated. The arithmetic processing for this is the same as that of a conventional swept source type OCT apparatus.

  The arithmetic control unit 200 controls each part of the OCT unit 150. For example, the arithmetic control unit 200 displays an OCT image of the operated eye on the display unit 90. As the control of the OCT unit 150, the arithmetic control unit 200 controls the operation of the light source unit 151, the movement control of the corner cube 164, the operation control of the detector 175, the operation control of the attenuator 170, the operation control of the polarization controllers 153 and 168, etc. I do.

  The arithmetic control unit 200 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, etc., as in a conventional computer. A computer program for controlling the microscope 1 for ophthalmic surgery is stored in a storage device such as a hard disk drive. The arithmetic control unit 200 may include various circuit boards, for example, a circuit board for forming an OCT image. The arithmetic control unit 200 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.

[Control system]
FIG. 6 shows an example of the configuration of the control system of the ophthalmic surgical apparatus 40. In FIG. 6, the same parts as those in FIGS.

(Control part)
The control system of the ophthalmic surgical apparatus 40 is configured around the control unit 210. The control unit 210 has both functions of a control unit (calculation control unit) for controlling the microscope 1 for ophthalmic surgery and a control unit (calculation control unit 200) for controlling the OCT apparatus 15. One or more elements for realizing the means are distributed in the ophthalmic surgical microscope 1 and the OCT apparatus 15. The control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like. The control unit 210 is provided with a main control unit 211 and a storage unit 212.

(Main control unit)
The main control unit 211 performs the various controls described above. In particular, the main control unit 211 controls the imaging device 56a, the variable power lens driving unit 31d, the illumination light source 21, and the slit plate driving unit 24b of the microscope for ophthalmic surgery 1. The main control unit 211 controls the CCD image sensor 105, the calculation control unit 106, and the scanning control unit 108 of the first optical unit 16. Further, the main control unit 211 controls the visible light source unit 201, the light source unit 151, the attenuator 170, the polarization controllers 153 and 168, and the detector 175 of the second optical unit 17.

  For example, the control means for controlling the components of the microscope for ophthalmic surgery 1 (for example, the image sensor 56a, the variable power lens driving unit 31d, the illumination light source 21, the slit plate driving unit 24b, etc.) in the control unit 210 is ophthalmic. Provided in the surgical microscope 1. In addition, the main control unit 211 includes components of the OCT apparatus 15 (for example, the CCD image sensor 105, the scanning control unit 108, the visible light source unit 201, the light source unit 151, the attenuator 170, the polarization controllers 153 and 168, the detector 175, etc. ) Is provided in the OCT apparatus 15 (the first optical unit 16 or the second optical unit 17). That is, the control unit 210 includes the calculation control unit 106, the scanning control unit 108, and the calculation control unit 200 shown in FIG. 4, and calculation control means of the microscope for ophthalmic surgery 1 (not shown). In other words, the main control unit 211 may include two or more arithmetic control devices that are dispersedly arranged in the ophthalmic surgical microscope 1 and the OCT device 15.

  At this time, the operation mode of the main control unit 211 can be changed based on the detection result of the mounting state of the first optical unit 16 with respect to the microscope 6 by a known detection unit. For example, in response to detecting that the first optical unit 16 is attached to the microscope 6, the main control unit 211 shifts to a mode in which two or more arithmetic control devices are operated in a linked manner. For example, when an OCT image or an observation image is acquired by the OCT apparatus 15, a control signal is sent from the arithmetic control unit 200 to the control means of the microscope for ophthalmic surgery 1, and the control means that receives this signal displays the display unit 90 or during operation. Display control on the observation monitor 14 can be performed. Further, in response to detecting that the first optical unit 16 has been removed from the microscope 6, the main control unit 211 switches from the above-described linkage operation mode to an operation mode by the control means alone of the ophthalmic surgical microscope 1. Transition.

  The zoom lens driving unit 31d moves each of the zoom lenses 31a, 31b, and 31c constituting the zoom lens system 31 independently in the direction along the observation optical axes OL and OR. The slit plate driving unit 24b moves the slit plate 24 in a direction orthogonal to the illumination optical axis O ′.

  Further, the main control unit 211 performs processing for writing data into the storage unit 212 and processing for reading data from the storage unit 212. Further, the main control unit 211 displays an image based on the transmitted light of the filter 103 detected by the CCD image sensor 105 on the intraoperative observation monitor 14.

(Image forming part)
The image forming unit 220 forms image data of a cross-sectional image such as a fundus based on the detection signal from the detector 175. This process includes processes such as noise removal (noise reduction), filter processing, FFT (Fast Fourier Transform), and the like, as in conventional swept source type optical coherence tomography. In the case of another type of OCT apparatus, the image forming unit 220 executes a known process corresponding to the type. The image forming unit 220 includes a component for forming an OCT image in the arithmetic control unit 200 shown in FIG. The image forming unit 220 may include components related to image formation in the arithmetic and control unit of the microscope 1 for ophthalmic surgery.

(Image processing unit)
The image processing unit 230 performs various types of image processing and analysis processing on the image formed by the image forming unit 220. For example, the image processing unit 230 executes various correction processes such as image brightness correction and dispersion correction. The image processing unit 230 can also perform various image processing and analysis processing on the image (fundus image, anterior eye image, etc.) obtained by the microscope 1 for ophthalmic surgery. The image processing unit 230 is a component for processing an OCT image in the arithmetic control unit 200 shown in FIG. 4, a component for processing an image output from the CCD image sensor 105 in the arithmetic control unit 106, Among the arithmetic and control unit of the microscope for ophthalmologic surgery 1, it includes components related to image processing.

  The image processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between cross-sectional images to form image data of a three-dimensional image such as a fundus. Note that the image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system. As image data of a three-dimensional image, there is image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data. When displaying an image based on volume data, the image processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data, and views the image from a specific gaze direction. Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 90.

  It is also possible to form stack data of a plurality of cross-sectional images as image data of a three-dimensional image. The stack data is image data obtained by three-dimensionally arranging a plurality of cross-sectional images obtained along a plurality of scanning lines based on the positional relationship of the scanning lines. That is, stack data is image data obtained by expressing a plurality of cross-sectional images originally defined by individual two-dimensional coordinate systems by one three-dimensional coordinate system (that is, by embedding them in one three-dimensional space). is there.

  The image processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. In a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored in advance.

  Note that the ophthalmic surgical apparatus 40 may further include a recording unit (a storage unit that stores a moving image) that records an observation image (visible) obtained by the observation optical system 30 as a moving image. For example, image data based on the detection signal obtained by the image sensor 56a is recorded in the recording unit. The recording means may be a storage device such as a known hard disk drive. The moving image recorded in this way may be read from the recording means and reproduced at an arbitrary timing and displayed on the display unit 90 or the intraoperative observation monitor 14. The surgeon, for example, gives instructions to start recording, to stop recording, to instruct playback of moving images recorded on the recording means by operating the operation panel or the foot switch 8 provided on the intraoperative observation monitor 14 or the display unit 90. Can be done. As a result, it is possible to confirm the surgical procedure for the eye E to be operated.

  Further, the ophthalmic surgical apparatus 40 has an observation image (visible) obtained by the observation optical system 30, an image photographed using the CCD image sensor 105 (an observation image by infrared light or an observation image by red-free light), and It may be configured to further include means for recording at least two of the live images of the OCT image as synchronized moving images. For example, the recording means includes image data based on the detection signal obtained by the image sensor 56a, image data based on the detection signal obtained by the CCD image sensor 105, image data formed by the image forming unit 220, or Image data subjected to image processing or the like by the image processing unit 230 is recorded. When the recorded image data is reproduced, the ophthalmic surgical apparatus 40 uses an observation image (visible) obtained by the observation optical system 30 and an infrared observation image captured by infrared photographing using the CCD image sensor 105 and 3. The live image of the three-dimensional OCT image can be synchronized and displayed in parallel on the display unit 90 or the intraoperative observation monitor 14. Further, the ophthalmic surgical apparatus 40 can graphically display the positional relationship between the OCT image and the observation image captured using the CCD image sensor 105 on the observation image by analyzing the image in which the aiming light is drawn. Is possible. Alternatively, the ophthalmologic surgical apparatus 40 graphically displays the positional relationship between the three-dimensional OCT image and the observation image captured using the CCD image sensor 105 on the observation image by analyzing the image on which the aiming light is depicted. Is possible. The operator gives instructions such as a recording start instruction, a recording stop instruction, and a reproduction instruction for the moving image recorded in the recording means by operating the operation panel or the foot switch 8 provided in the intraoperative observation monitor 14 and the display unit 90. Is possible.

[Operation]
The operation of the ophthalmic surgical apparatus 40 having the above configuration will be described.

  First, adjustment of the observation state by the microscope for ophthalmic surgery 1 is performed. For this purpose, for example, the operator adjusts the microscope 1 for ophthalmic surgery. That is, after adjusting the position and orientation of the second arm 4, the operator operates the foot switch 8 to move the microscope 6 in the vertical direction and the horizontal direction, and stops the microscope 6 at a desired position. Let Thereafter, the surgeon adjusts the eye width, the observation angle, the amount of light, and the like to adjust the focus and position. Accordingly, the surgical eye E is illuminated by the illumination light of the illumination optical system 20, and the operator can observe the surgical eye E while looking through the eyepiece lens 37.

  Next, acquisition of an observation image (moving image) by the OCT apparatus 15 is started. Specifically, the OCT apparatus 15 starts acquiring a moving image by infrared imaging or red-free imaging of the eye E (surgical site and its surroundings) from the detection signal obtained by the CCD image sensor 105. The image of each frame constituting this moving image is temporarily stored in the frame memory (storage unit 212) and sequentially sent to the image processing unit 230. The image of each frame temporarily stored in the frame memory is displayed on the intraoperative observation monitor 14.

  The surgeon performs focusing by moving the focus lens 101 while viewing the naked eye observation image obtained by the microscope for ophthalmic surgery 1 or the moving image displayed on the intraoperative observation monitor 14. Note that the main control unit 211 may control the focus lens 101 to move based on the calculated movement amount by calculating the movement amount of the focus lens 101 by analyzing each frame using a known method. .

  Subsequently, the control unit 210 starts tracking. Specifically, the arithmetic control unit 106 performs arithmetic processing for performing tracking control based on the observation image acquired by the CCD image sensor 105. The scanning control unit 108 controls the scanning unit 107 based on a control signal from the calculation control unit 106. Thereby, it is possible to maintain a suitable positional relationship in focus at a desired position.

  Next, the scanning range of the signal light for OCT measurement and the scanning pattern (scanning shape and size of the scanning region) are set. The scanning range of the signal light can be set automatically or manually. When automatically setting the scanning range of the signal light, for example, the same range as the preoperative OCT measurement is reproduced, or the surgical site is detected by analyzing the frame of the current observation image, and the detected surgery It is possible to set a range including a part. The preoperative OCT measurement range can be specified by recording the preoperative OCT scanning range in a three-dimensional image or a front image and comparing it with the frame of the current observation image. When manually setting the scanning range of the signal light, for example, the operator sets the desired scanning range while viewing the observation image on which the live image of the OCT image or the projected image of the aiming light is depicted. . When the scanning range of signal light is automatically set, the scanning range may be identified by projection of aiming light. As a method for setting the scanning pattern, there are automatic setting of the same scanning pattern as before the operation and manual setting using the foot switch 8. When the scanning pattern is set manually, scanning pattern options are presented on the intraoperative observation monitor 14 and the like, and desired options are designated using the foot switch 8 and the like. The scanning pattern options may include at least one of a one-dimensional pattern and a two-dimensional pattern.

  After the setting related to the scanning of the signal light is completed, the OCT measurement is started (however, when a live image of the OCT image is used for the setting, the OCT measurement is already started). Aiming light can be projected in parallel with the execution of the OCT measurement. In that case, the aiming light is combined with the signal light by the combining unit 109 and irradiated to the same position as the signal light in the eye E to be operated. Since the reflected light of the eye E to be operated by the aiming light is incident on the observation optical system 30, the surgeon can observe the trajectory of the aiming light in the eye E to be operated. That is, the surgeon can visually recognize the scanning trajectory of the signal light (the position where the OCT measurement is performed).

  In order to perform OCT measurement, the control unit 210 controls the light source unit 151 and the corner cube 164 and also controls the scanning unit 107 based on the scanning region set as described above. The image forming unit 220 forms a tomographic image of the eye E based on the interference light spectrum obtained by OCT measurement. When the scanning pattern is a three-dimensional scan, the image processing unit 230 forms a three-dimensional image of the eye E based on a plurality of tomographic images formed by the image forming unit 220.

  Further, in response to an operation on the foot switch 8 by the operator, the control unit 210 may cause the display unit 90 to display a still image captured from the moving image displayed on the intraoperative observation monitor 14.

  The surgeon observes the eye with the microscope for ophthalmic surgery 1, observes the visible image acquired with the microscope for ophthalmic surgery 1, observes the OCT image acquired with the OCT apparatus 15, and obtains the infrared acquired with the OCT apparatus 15. Surgery is performed while selectively observing images (or red-free images).

[effect]
The effect of the ophthalmic surgical apparatus 40 according to this embodiment will be described.

  The ophthalmic surgical apparatus 40 according to this embodiment includes an observation optical system 30, an illumination optical system 20, an interference optical system, and an image forming unit 220. The observation optical system is an optical system for observing the operated eye E through the objective lens 19. The illumination optical system 20 is an optical system for illuminating the eye E through the objective lens 19. The interference optical system has a signal optical path and a reference optical path guided to the surgical eye E via the deflection member 100 disposed between the objective lens 19 and the surgical eye E, and the surgical operation via the signal optical path. Interference light based on the return light from the eye E and the reference light passing through the reference light path is detected. The image forming unit 220 forms an image of the eye E based on the detection result by the interference optical system.

  In such an ophthalmic surgical apparatus 40, the deflecting member 100 is disposed between the objective lens 19 and the eye E to be operated, and the deflecting member 100 deflects the signal light guided along the signal optical path and the return light. Yes. This prevents the observation light from being attenuated by disposing the deflecting member 100 for acquiring the OCT image, and allows high-quality observation images and OCT images to be operated during the operation without affecting the existing configuration. It becomes possible to get to.

  The deflection member 100 may be disposed at a position deviated from at least one of the optical path formed by the observation optical system 30 and the optical path formed by the illumination optical system 20. Further, the deflecting member 100 may be a beam splitter disposed on at least one of the optical path formed by the observation optical system 30 and the optical path formed by the illumination optical system 20. The beam splitter may be a dichroic mirror disposed in the optical path formed by the observation optical system 30. Further, the beam splitter may be a dichroic mirror or a half mirror disposed in the optical path formed by the illumination optical system 20.

  The first optical unit 16 in which at least a part of the interference optical system is stored may be formed as an attachment that can be attached to and detached from the microscope 6 that holds at least the objective lens 19. Thereby, it is possible to obtain a high-quality observation image and OCT image of the operated eye E during the operation without affecting the existing configuration of the microscope 1 for ophthalmic surgery.

  The interference optical system may include a dividing unit, a scanning unit 107, and an interference unit. The dividing unit divides light from the light source into signal light and reference light. The scanning unit 107 is used to scan the eye E with light guided through the signal light path. The interference unit interferes the return light of the signal light from the operated eye E via the signal light path and the reference light via the reference light path. In this case, the deflection member 100 is disposed between the eye to be operated E and the scanning unit 107. The first optical unit 16 stores at least the scanning unit 107 and the deflection member 100. Thereby, the weight reduction of the 1st optical unit 16 is attained.

  Further, the ophthalmic surgical apparatus 40 may include a synthesis unit 109. The combining unit combines the optical path of visible light from the visible light source unit 201 with the signal optical path at a position between the dividing unit and the scanning unit 107. According to such a configuration, the operator can confirm the OCT scanning position while observing the eye E with the observation optical system 30. Thereby, the operator can designate the scanning position for acquiring the OCT image without taking his eyes off the eyepiece part of the microscope 1 for ophthalmic surgery, and can improve the efficiency of the operation.

  The first optical unit 16 may further store a CCD image sensor 105. The CCD image sensor 105 is disposed in an optical path branched from the signal optical path between the scanning unit 107 and the deflecting member 100. The ophthalmic surgical apparatus 40 may include a scanning control unit 108 that controls the scanning unit 107 based on an image acquired by the CCD image sensor 105. The first optical unit 16 may further store the scanning control unit 108. Thereby, tracking can be performed based on the signal detected by the CCD image sensor 105.

  In addition, at least a part of the dividing unit and the interference unit may be stored in the second optical unit 17, and the first optical unit 16 and the second optical unit 17 may be connected by an optical fiber (light guide unit).

  The ophthalmic surgical apparatus 40 further includes a main control unit 211 that controls the observation optical system 30 and the illumination optical system 20, and the main control unit 211 has the first optical unit 16 mounted on the microscope 6. The interference optical system may be controlled.

  The first optical unit 16 (attachment for ophthalmic surgery) is detachable from the microscope for ophthalmic surgery 1. The microscope for ophthalmologic surgery 1 includes an observation optical system 30 for observing the operated eye E through the objective lens 19 and an illumination optical system 20 for illuminating the operated eye E through the objective lens 19. . The first optical unit 16 includes a deflection member 100 disposed between the objective lens 19 and the eye E to be operated in a state where the first optical unit 16 is attached to the ophthalmic surgical microscope 1, and has a signal light path and a reference light path. The signal light path from the interference optical system that detects the interference light based on the return light from the operated eye E that passes through the signal light path and the reference light that passes through the reference light path is guided to the operated eye E through the deflection member 100. It is configured as follows.

<Second Embodiment>
Although the deflection member 100 according to the first embodiment has been described as having a rectangular shape as shown in FIGS. 2 and 3, the embodiment according to the present invention is limited to this. It is not a thing. The deflecting member according to the second embodiment has a shape corresponding to the optical path formed by the observation optical system 30. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

  The configuration and control of the ophthalmic surgical apparatus according to the second embodiment are substantially the same as those of the first embodiment. The configuration of the ophthalmic surgical apparatus according to the second embodiment is different from the configuration of the ophthalmic surgical apparatus 40 according to the first embodiment in the shape of the deflection member.

  FIG. 7 shows an optical system of the microscope for ophthalmologic surgery 1 according to the second embodiment viewed from the surgeon. 7, parts that are the same as those in FIG. 3 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

  The deflecting member 100 has a symmetrical trapezoidal shape when viewed from the front (operator side). Specifically, the deflection member 100 is formed with trapezoidal legs so as to be out of the observation optical path. That is, between the objective lens 19 and the eye E to be operated, the left and right observation optical paths are inclined so as to approach each other toward the surgical eye E, and the left and right side surfaces of the deflection member 100 correspond to the left and right observation optical paths. Has a slope. In other words, the lower surface of the deflecting member 100 (the surface on the eye to be operated E side) is formed in a smaller area than the upper surface (the surface on the objective lens 19 side), and the difference (or ratio) between the areas is, for example, It is set by the inclination of the left and right observation optical paths and the height of the deflecting member 100 (distance between the upper surface and the lower surface). Thereby, attenuation of observation light can be prevented like the first embodiment. Note that the shape of the deflection member according to this embodiment is not limited to that shown in FIG. 7. For example, the upper surface and the lower surface may be non-parallel, or a certain surface may be a curved surface. In any case, a deflection member is formed so as not to obstruct the left and right observation optical paths (or to obstruct the left and right observation optical paths so as not to substantially affect the observation), and the deflection members What is necessary is just to be arrange | positioned under the objective lens 19. FIG.

  The ophthalmic surgical apparatus of this embodiment has the same effect as that of the first embodiment.

<Third embodiment>
In the first embodiment or the second embodiment, the case where the deflection member is disposed between the objective lens 19 and the eye E to be operated has been described. However, the embodiment according to the present invention is not limited to this. Absent. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

  The configuration and control of the ophthalmic surgical apparatus according to the third embodiment are substantially the same as those of the first embodiment. The configuration of the ophthalmic surgical apparatus according to the third embodiment is different from the configuration of the ophthalmic surgical apparatus 40 according to the first embodiment in the position where the deflection member is disposed.

  FIG. 8 shows an optical system of the microscope for ophthalmic surgery 1 according to the third embodiment viewed from the operator. 8, parts similar to those in FIG. 3 are given the same reference numerals, and description thereof will be omitted as appropriate.

  In the third embodiment, the deflecting member 100 is positioned at a predetermined position in the direction perpendicular to the optical axis O of the objective lens 19 between the objective lens 19 and the eye E to be operated so as to be out of the optical path formed by the observation optical system. Be placed. Thereby, attenuation of observation light can be prevented like the first embodiment. It should be noted that the closer the predetermined position is to the optical axis O, the closer the incident angle of the signal light to the eye E can be approached 90 degrees. Therefore, the detection accuracy of the return light with respect to the signal light is improved, and the image quality of the OCT image can be improved. On the other hand, when the predetermined position is brought close to the optical axis O, it becomes close to the optical path formed by the observation optical system 30, and the mounting may be difficult. The distance from the optical axis O at a predetermined position can be appropriately designed in consideration of the above.

  The ophthalmic surgical apparatus of this embodiment has the same effect as that of the first embodiment.

<Fourth embodiment>
In the first to third embodiments, the case where the deflection member is disposed between the objective lens 19 and the eye E to be operated has been described. However, the embodiment according to the present invention is not limited to this. Absent. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

  The configuration and control of the ophthalmic surgical apparatus according to the fourth embodiment are substantially the same as those of the first embodiment. The difference between the configuration of the ophthalmic surgical apparatus according to the fourth embodiment and the configuration of the ophthalmic surgical apparatus 40 according to the first embodiment is the position where the deflection member is disposed.

  FIG. 9 shows an optical system of the microscope for ophthalmologic surgery 1 according to the fourth embodiment viewed from the operator. 9, parts that are the same as those in FIG. 3 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

  In the fourth embodiment, the deflecting member 100 is disposed at a predetermined position in the direction perpendicular to the optical axis O of the objective lens 19 from the periphery of the objective lens 19 so as to be out of the optical path formed by the observation optical system. Thereby, in addition to the effect similar to 1st Embodiment, attenuation | damping of illumination light can be prevented. It should be noted that the closer the predetermined position is to the optical axis O, the closer the incident angle of the signal light to the eye E can be approached 90 degrees. Therefore, the detection accuracy of the return light with respect to the signal light is improved, and the image quality of the OCT image can be improved. On the other hand, when the predetermined position is brought close to the optical axis O, the deflecting member 100 may physically interfere with the objective lens 19. The distance from the optical axis O at a predetermined position can be appropriately designed in consideration of the above.

[effect]
The effect of the ophthalmic surgical apparatus according to this embodiment will be described.

  The ophthalmic surgical apparatus according to this embodiment includes an observation optical system 30, an illumination optical system 20, an interference optical system, and an image forming unit 220. The observation optical system is an optical system for observing the operated eye E through the objective lens 19. The illumination optical system 20 is an optical system for illuminating the eye E through the objective lens 19. The interference optical system has a signal optical path and a reference optical path that are guided from the peripheral edge of the objective lens 19 to the eye E to be operated through a deflecting member 100 disposed at a predetermined position in a direction orthogonal to the optical axis O of the objective lens 19. Then, the interference light based on the return light from the eye E to be operated through the signal light path and the reference light through the reference light path is detected. The image forming unit 220 forms an image of the eye E based on the detection result by the interference optical system.

  In such an ophthalmic surgical apparatus, the deflection member 100 is disposed at a predetermined position in the direction orthogonal to the optical axis O of the objective lens 19 from the periphery of the objective lens 19 to deflect the signal light guided through the signal optical path and its return light. Deflection is performed by the member 100. This prevents the attenuation of the observation light and the illumination light due to the arrangement of the deflecting member for acquiring the OCT image, and does not affect the existing configuration, and the high-quality observation image and OCT image of the operated eye Can be obtained during the operation.

  The first optical unit 16 (attachment for ophthalmic surgery) is detachable from the microscope for ophthalmic surgery 1. The microscope for ophthalmologic surgery 1 includes an observation optical system 30 for observing the operated eye E through the objective lens 19 and an illumination optical system 20 for illuminating the operated eye E through the objective lens 19. . The first optical unit 16 includes a deflecting member 100 disposed at a predetermined position in a direction orthogonal to the optical axis O of the objective lens 19 from the periphery of the objective lens 19 in a state where the first optical unit 16 is attached to the ophthalmic surgical microscope 1. The deflecting member 100 has a signal light path from an interference optical system that detects interference light based on the return light from the eye E to be operated through the signal light path and the reference light through the reference light path. It is comprised so that it may guide to the eye E to be operated through.

<Fifth embodiment>
In the first to fourth embodiments, the description has been given of the case where the deflecting member 100 is disposed at a position separated by a predetermined distance below or in the lateral direction of the objective lens 19, but the embodiment according to the present invention is not limited thereto. It is not limited. In the fifth embodiment, the deflection member 100 is disposed above the objective lens 19. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

  The configuration and control of the ophthalmic surgical apparatus according to the fifth embodiment are substantially the same as those of the first embodiment. The configuration of the ophthalmic surgical apparatus according to the fifth embodiment is different from the configuration of the ophthalmic surgical apparatus 40 according to the first embodiment in the position where the objective lens and the deflection member are arranged.

  FIG. 10 shows an optical system of the microscope for ophthalmic surgery 1 according to the fifth embodiment viewed from the operator. 10, parts that are the same as those in FIG. 3 are given the same reference numerals, and descriptions thereof will be omitted as appropriate.

  In the fifth embodiment, the deflecting member 100 is disposed between the objective lens 19 and the variable power lens system 31 so that the deflecting member 100 deviates from the optical path formed by the observation optical system. Further, in the objective lens 19, the portion through which the signal optical path passes and the portion through which the optical path formed by the observation optical system passes have different refractive characteristics. In this embodiment, the hole 19a is formed in the objective lens 19, and the deflecting member 100 is arranged so that the portion through which the signal optical path passes passes through the hole 19a. Thereby, in addition to the effect similar to 1st Embodiment, attenuation | damping of illumination light can be prevented.

[effect]
The effect of the ophthalmic surgical apparatus according to this embodiment will be described.

  The ophthalmic surgical apparatus according to this embodiment includes an observation optical system 30, an illumination optical system 20, an interference optical system, and an image forming unit 220. The observation optical system 30 is an optical system for observing the operated eye E via the objective lens 19, including a variable magnification lens system 31. The illumination optical system 20 is an optical system for illuminating the eye E through the objective lens 19. The interference optical system has a signal optical path and a reference optical path that are guided to the eye E to be operated through the deflecting member 100 disposed between the objective lens 19 and the variable power lens system 31, and the target optical path through the signal optical path. Interference light based on return light from the surgical eye and reference light passing through the reference light path is detected. The image forming unit 220 forms an image of the eye E based on the detection result by the interference optical system. In the objective lens 19, the portion through which the signal optical path passes and the portion through which the optical path formed by the observation optical system 30 passes have different refractive characteristics.

  In such an ophthalmic surgical apparatus 40, the deflection member 100 is disposed between the objective lens 19 and the variable power lens system 31, and the observation optical system 30 and the portion through which the signal optical path passes are formed in the objective lens 19. The portion through which the optical path passes has different refractive characteristics. This prevents the attenuation of the observation light and the illumination light due to the arrangement of the deflecting member for acquiring the OCT image, and does not affect the existing configuration, and the high-quality observation image and OCT image of the operated eye Can be obtained during the operation. Further, the portion of the objective lens 19 through which the signal light path passes has a refraction characteristic in consideration of the incident angle of the signal light with respect to the objective lens 19 or the eye to be operated E, thereby scattering the signal light and its return light. This makes it possible to obtain a higher quality OCT image.

  The first optical unit 16 (attachment for ophthalmic surgery) is detachable from the microscope for ophthalmic surgery 1. The microscope for ophthalmologic surgery 1 includes a variable magnification lens system 31, and an observation optical system 30 for observing the eye E to be operated through the objective lens 19 and illumination of the eye E to be operated through the objective lens 19. In the objective lens 19, the part through which the signal optical path passes and the part through which the optical path formed by the observation optical system 30 passes have different refractive characteristics. The first optical unit 16 includes a deflecting member 100 disposed between the objective lens 19 and the variable power lens system 31 in a state in which the first optical unit 16 is attached to the ophthalmic surgical microscope 1, and has a signal light path and a reference light path. Then, the signal light path from the interference optical system that detects the interference light based on the return light from the operated eye E that passes through the signal light path and the reference light that passes through the reference light path passes through the deflection member 100 to the operated eye E. It is configured to guide.

<Sixth embodiment>
In the first to fifth embodiments, the case where the deflecting member is disposed around the objective lens 19 has been described. However, the embodiment according to the present invention is not limited to this. Hereinafter, the codes used in the first embodiment are applied mutatis mutandis.

  The configuration and control of the ophthalmic surgical apparatus according to the sixth embodiment are substantially the same as those in the first embodiment. The difference between the configuration of the ophthalmic surgical apparatus according to the sixth embodiment and the configuration of the ophthalmic surgical apparatus 40 according to the first embodiment is an objective lens.

  FIG. 11 shows an optical system of the microscope for ophthalmic surgery 1 according to the sixth embodiment viewed from the operator. In FIG. 11, the same parts as those in FIG.

  In the sixth embodiment, the deflection member 100 is provided on the objective lens 19. FIG. 11 illustrates a case where the deflection member 100 is provided inside the objective lens 19, but the deflection member 100 is configured such that the front surface (for example, the surface on the eye E side) or the back surface (for example, the deformed eye) of the objective lens 19. A surface on the double lens system 31 side) may be provided. In this embodiment, the signal light passing through the signal light path is deflected by the deflecting member 100 provided inside the objective lens 19. For example, signal light is incident from the normal direction of the vertical cross section formed on the objective lens 19, and the signal light is deflected by the deflection member 100 inside the objective lens 19. Thereby, in addition to the effect similar to 1st Embodiment, attenuation | damping of illumination light can be prevented.

[effect]
The effect of the ophthalmic surgical apparatus according to this embodiment will be described.

  The ophthalmic surgical apparatus according to this embodiment includes an observation optical system 30, an illumination optical system 20, an interference optical system, and an image forming unit 220. The observation optical system 30 is an optical system for observing the eye E to be operated through the objective lens 19 provided with the deflection member 100. The illumination optical system 20 is an optical system for illuminating the eye E through the objective lens 19. The interference optical system has a signal optical path and a reference optical path that are guided to the surgical eye E via the deflection member 100 provided in the objective lens 19, and the return light from the surgical eye E via the signal optical path and the reference Interference light based on the reference light passing through the optical path is detected. The image forming unit 220 forms an image of the eye E based on the detection result by the interference optical system.

  In such an ophthalmic surgical apparatus 40, the objective lens 19 is provided with a deflection member 100, and the signal light guided through the signal optical path and its return light are deflected by the deflection member 100 provided in the objective lens 19. This prevents the attenuation of the observation light and the illumination light due to the arrangement of the deflecting member for acquiring the OCT image, and does not affect the existing configuration, and the high-quality observation image and OCT image of the operated eye Can be obtained during the operation.

<Modification>
The embodiment described above is merely an example for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications, omissions, additions and the like within the scope of the present invention.

[First Modification]
In the embodiment shown above, the connection part (connector, port) on which the first optical unit 16 formed as an attachment is attached to the microscope 6 (main body part) can be connected to an attachment different from the first optical unit 16. May be configured. That is, the microscope 6 is provided with a first connection portion. The first optical unit 16 is provided with a second connection part. The first optical unit 16 is attached to the microscope 6 by connecting the first connection portion and the second connection portion. The first connection unit is configured to be connectable to a third connection unit provided on an attachment different from the first optical unit 16.

  Thereby, the 1st connection part provided in the microscope 6 turns into a general purpose connection part, and it becomes possible to make addition of a connection part unnecessary in order to mount | wear with an attachment.

[Second Modification]
In the embodiment shown above, the optical unit (third optical unit) in which at least the deflection member 100 is stored is different from the other optical unit (fourth optical unit) in which at least a part of the interference optical system is stored. You may form so that mounting | wearing is possible. Another optical unit (fourth optical unit) in which at least a part of the interference optical system is stored is an optical unit (third optical unit) that is attached to a microscope 6 (main body) that holds at least the objective lens 19. ).

[Third Modification]
In the embodiment described above, the ophthalmic surgical apparatus may further include a mechanism for moving the deflection member 100. Thereby, the deflection member 100 can be moved to a predetermined position only when an OCT image is acquired, and a high-quality observation image can be acquired for the eye E to be operated when the OCT image is not required. . In addition, when the mechanism is provided in an ophthalmic surgical attachment, and the attachment is configured to be attachable to various ophthalmic surgical microscopes, the optical path arrangement of the mounted ophthalmic surgical microscope It is possible to adjust the position of the deflection member 100 according to the above.

[Other variations]
In the embodiment shown above, the first optical unit 16 may be mounted between the mounting portion of the front lens 13 and the front lens 13.

  In the embodiment described above, the deflection member 100 includes an optical element having at least a function of changing the traveling direction of light, such as a non-planar mirror such as a plane mirror or a concave mirror, a deflection prism, or a diffraction grating. Also good.

  In the embodiment described above, the case where the OCT apparatus 15 is configured by the first optical unit 16 and the second optical unit 17 has been described. However, the OCT apparatus 15 may be configured by three or more optical units.

  The connection part (second connection part) of the attachment for ophthalmic surgery can be configured to be replaceable. That is, two or more second connection parts are prepared, and the second connection part having a form corresponding to the form of the connection part (first connection part) of the mounted ophthalmic surgical microscope can be selectively used. Is possible. Thereby, it is possible to attach the same ophthalmic surgical attachment to various types of ophthalmic surgical microscopes having different first connection portions.

  Moreover, it is possible to arbitrarily combine the configurations described in the first to sixth embodiments and the above-described modifications. For example, in a system in which two or more embodiments of the first to sixth embodiments can be applied, a desired embodiment of the two or more embodiments can be alternatively applied by switching operation modes. Is possible.

DESCRIPTION OF SYMBOLS 1 Microscope for ophthalmic surgery 2 Support | pillar 3 1st arm 4 2nd arm 5 Driving device 6 Microscope 7 Support part 8 Foot switch 8a Operation lever 10 Lens barrel part 11L, 11R Eyepiece part 12 Inverter part 13 Prefix lens 14 For intraoperative observation Monitor 19 Objective lens 19a Hole 40 Ophthalmic surgical device 90 Display unit 100 Deflection member 101 Focus lens 102 Beam splitter 103 Filter 104 Condensing lens 105 CCD image sensor 106 Operation control unit 107 Scanning unit 108 Scanning control unit 109 Combining unit 150 OCT unit 200 Arithmetic Control Unit 201 Visible Light Source Unit

Claims (16)

An observation optical system for observing the operated eye through the objective lens;
An illumination optical system for illuminating the eye to be operated through the objective lens;
A return path from the surgical eye via the signal optical path, the optical path having a signal optical path and a reference optical path that are guided to the surgical eye via a deflection member disposed between the objective lens and the surgical eye; An interference optical system for detecting interference light based on the light and the reference light passing through the reference optical path;
An image forming unit that forms an image of the eye to be operated based on a detection result by the interference optical system;
Including
The deflection member can be inserted into and removed from an illumination optical path formed by the illumination optical system, and when the deflection member is arranged in the illumination optical path, the attenuation of light guided through the observation optical system is canceled. The intensity of light guided through the illumination optical system is controlled so that
Ophthalmic surgery device. The ophthalmic surgical apparatus according to claim 1, wherein the deflecting member is disposed at a position deviated from at least one of an optical path formed by the observation optical system and an optical path formed by the illumination optical system. The ophthalmic surgery according to claim 1, wherein the deflecting member is a beam splitter disposed in at least one of an optical path formed by the observation optical system and an optical path formed by the illumination optical system. apparatus. The ophthalmic surgical apparatus according to claim 3, wherein the beam splitter is a dichroic mirror disposed in an optical path formed by the observation optical system. The ophthalmic surgical apparatus according to claim 3, wherein the beam splitter is a dichroic mirror or a half mirror disposed in an optical path formed by the illumination optical system. The first optical unit in which at least a part of the interference optical system is stored is formed as an attachment that can be attached to and detached from at least a main body that holds the objective lens. The ophthalmic surgical apparatus according to any one of 5. The interference optical system includes a dividing unit that divides light from a light source into signal light and reference light, a scanning unit that scans the eye to be operated with light guided through the signal light path, and the signal light path. An interference unit that interferes the return light of the signal light from the operated eye and the reference light that has passed through the reference light path,
The deflection member is disposed between the operated eye and the scanning unit,
The ophthalmic surgical apparatus according to claim 6, wherein the first optical unit stores at least the scanning unit and the deflection member. The ophthalmic surgical apparatus according to claim 7, further comprising a combining unit that combines an optical path of visible light from a visible light source with the signal optical path at a position between the dividing unit and the scanning unit. The first optical unit includes:
The ophthalmic surgical apparatus according to claim 7 or 8, further comprising an imaging unit disposed in an optical path branched from the signal optical path between the scanning unit and the deflecting member. The ophthalmic surgical apparatus according to claim 9, further comprising a scanning control unit that controls the scanning unit based on an image acquired by the imaging unit. The ophthalmic surgical apparatus according to claim 10, wherein the first optical unit further stores the scanning control unit. At least a part of the dividing unit and the interference unit is stored in a second optical unit,
The ophthalmic surgical apparatus according to any one of claims 7 to 11, wherein the first optical unit and the second optical unit are connected by a light guide unit. The first optical unit is attached to the main body by connecting the first connection provided in the main body and the second connection provided in the first optical unit,
The said 1st connection part is comprised so that connection with the 3rd connection part provided in the attachment different from the said 1st optical unit is possible. The Claim 13 characterized by the above-mentioned. Eye surgery equipment. A control unit for controlling the observation optical system and the illumination optical system;
The ophthalmology according to any one of claims 6 to 13, wherein the control unit controls the interference optical system when the first optical unit is mounted on the main body unit. Surgical device. At least the deflection member is stored in the third optical unit, and at least a part of the interference optical system is stored in the fourth optical unit;
The said 4th optical unit is attached or detached with respect to the said 3rd optical unit with which at least the main-body part holding the said objective lens is mounted | worn. The any one of Claims 1-5 characterized by the above-mentioned. The ophthalmic surgical apparatus according to Item. The ophthalmic surgical apparatus according to any one of claims 1 to 15, further comprising a mechanism for moving the deflection member.

Images