JP2016202452A - Microscope for ophthalmic surgery - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a microscope for ophthalmic surgery having a high freedom degree in arrangement of a drive system for moving an optical member, capable of observing a patient's eye and acquiring an OCT image.SOLUTION: The microscope for ophthalmic surgery includes an illumination optical system, an observation optical system, an interference optical system, an optical scanner, a collimator lens, an optical fiber, and a moving mechanism. The illumination optical system illuminates the patient's eye with illumination light. The observation optical system is used for observing a patient's eye illuminated by the illumination optical system. The interference optical system splits light from a light source into measurement light and reference light, and detects interference light of return light of the measurement light from the subject's eye and the reference light. The optical scanner is disposed at an optical path of the measurement light. The collimator lens is disposed between the light source and the optical scanner. The optical fiber is so disposed as to place an outgoing end of the measurement light at a position facing the collimator lens. The moving mechanism moves the collimator lens and the outgoing end relative to each other along the optical path of the measurement light.SELECTED DRAWING: Figure 2

Description

  The present invention relates to an ophthalmic surgical microscope.

  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 microscope is used. The microscope for ophthalmologic surgery is a device for visually observing or photographing an image of a patient's eye illuminated by an illumination optical system via an observation optical system.

  Such an ophthalmic surgical microscope includes an OCT optical system for acquiring an OCT image of a patient's eye using optical coherence tomography (hereinafter referred to as OCT) (for example, Patent Document 1).

U.S. Pat. No. 8,049,873

  In a microscope for ophthalmologic surgery, it is desired to reduce the size of a lens barrel portion that is configured so that an operator can move in an arbitrary direction. However, since the microscope for ophthalmic surgery disclosed in Patent Document 1 includes various optical systems such as an illumination optical system, an observation optical system, and an OCT optical system, a plurality of optical members are formed of an objective lens inside the lens barrel. Arranged around. Accordingly, there is a problem that it is difficult to dispose a drive system that moves an optical member disposed around the objective lens.

  The present invention has been made to solve the above-described problems, and has a high degree of freedom in the arrangement of a drive system for moving an optical member, and can be used for observation of a patient's eye and acquisition of an OCT image. The purpose is to provide.

  The ophthalmic surgical microscope according to the embodiment includes an illumination optical system, an observation optical system, an interference optical system, an optical scanner, a collimator lens, an optical fiber, and a moving mechanism. The illumination optical system illuminates the patient's eye with illumination light. The observation optical system is used for observing the patient's eye illuminated by the illumination optical system. The interference optical system divides light from the light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light. The optical scanner is disposed in the optical path of the measurement light. The collimating lens is disposed between the light source and the optical scanner in the optical path of the measurement light. The optical fiber guides the measurement light generated by the interference optical system, and the measurement light emission end is disposed at a position facing the collimating lens. The moving mechanism relatively moves the collimating lens and the emission end along the optical path of the measurement light.

  According to the present invention, it is possible to provide an ophthalmic surgical microscope that can easily arrange a drive system that moves an optical member and that can observe a patient's eye and acquire an OCT image.

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

  An example of an embodiment of the microscope for ophthalmic surgery according to the present invention will be described in detail with reference to the drawings. The microscope for ophthalmic surgery according to the following embodiment is used in ophthalmic surgery. The microscope for ophthalmologic surgery according to the embodiment is an apparatus capable of observing the patient's eye by illuminating the patient's eye (operated eye) with the illumination optical system and guiding the return light (reflected light) to the observation optical system. is there.

  Moreover, the microscope for ophthalmic surgery according to the embodiment includes an OCT optical system, and can acquire an OCT image of a patient's eye. The region to be imaged may be an arbitrary region of the patient's eye. For example, the anterior segment may be the cornea, the vitreous body, the crystalline lens, the ciliary body, or the like, and the retinal segment may be the retina or choroid. Or a vitreous body. Further, the imaging target region may be a peripheral region of the eye such as a eyelid or an eye socket. It is possible to form a cross-sectional image or a three-dimensional image of the patient's eye based on the return light of the OCT measurement light by a known method.

  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 microscope according to the embodiment can acquire an OCT image of a patient's eye using a known swept source OCT technique. It is also possible to apply the configuration according to the present invention to a type other than a swept source, for example, an ophthalmic surgical microscope using a spectral domain OCT technique.

  In the following embodiment, an apparatus in which the OCT optical system is applied to an ophthalmic surgical microscope will be described. However, it is also possible to apply the OCT optical system according to the embodiment to an ophthalmic observation apparatus other than the microscope for ophthalmic surgery, for example, a scanning laser opthalmoscope (SLO), a slit lamp, a fundus camera, and the like.

  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 (patient eye E) from the below-mentioned objective lens 15 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.

[Appearance structure]
FIG. 1 shows an external configuration of an ophthalmic surgical microscope according to this embodiment. The ophthalmic surgical microscope 1 includes a support column 2, a first arm 3, a second arm 4, a drive device 5, an operator microscope 6, an assistant's microscope 7, and a foot switch 8. ing. The support column 2 supports the entire microscope 1 for ophthalmic surgery. One end of the first arm 3 is connected to the upper end of the column 2. One end of the second arm 4 is connected to the other end of the first arm 3. A driving device 5 is connected to the other end of the second arm 4. The surgeon's microscope 6 is suspended by a driving device 5. The assistant's microscope 7 is attached to the surgeon's microscope 6. The foot switch 8 is used to perform various operations with the feet of an operator or the like. The driving device 5 acts to move the surgeon's microscope 6 and the assistant's microscope 7 three-dimensionally in the vertical and horizontal directions in response to an operation by the surgeon or the like.

  The surgeon's microscope 6 has a lens barrel portion 10 that houses various optical systems, drive systems, and the like. An upper part of the lens barrel unit 10 is provided with an inverter unit 12 that houses a known optical unit (image erecting prism) that converts an observation image obtained as an inverted image into an erect image. A pair of left and right eyepieces 11 </ b> L and 11 </ b> R is provided on the top of the inverter unit 12. The surgeon looks into the eyepieces 11L and 11R and observes the patient's eye E with both eyes.

  A front lens 13 is connected to the surgeon's microscope 6 via a holding arm 14. The upper end of the holding arm 14 is pivotally pivoted in the vertical direction so that the front lens 13 can be retracted from a position between the patient's eye E and the front focal point of the objective lens (not shown). ing. The retracted front lens 13 and holding arm 14 are stored in a storage unit (not shown).

[Configuration of optical system]
2 to 4 show configuration examples of the optical system of the microscope for ophthalmic surgery 1. FIG. 2 is a side view from the assistant's microscope 7 side. FIG. 3 is a side view from the operator side. FIG. 4 shows a configuration example of an OCT unit 70 described later.

  The optical system of the ophthalmic surgical microscope 1 is housed in the lens barrel 10 of the surgeon's microscope 6, and includes an objective lens 15, an illumination optical system 20, a main observation optical system 30, a sub-observation optical system 40, And an OCT optical system 60. The main observation optical system 30 is an optical system (observation optical system) of the surgeon's microscope 6, and the sub-observation optical system 40 is an optical system (observation optical system) of the assistant's microscope 7.

(Illumination optics)
The illumination optical system 20 illuminates the patient's eye E via the objective lens 15. 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 collimating lens 27, and a dichroic mirror 25.

  The illumination field stop 23 is provided at a position optically conjugate with the front focal position of the objective lens 15.

  The illumination light source 21 is provided outside the lens barrel unit 10. 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 patient's eye E and the optical axis O of the objective lens 15 can be changed.

  The collimating lens 27 converts the illumination light that has passed through the illumination field stop 23 into a parallel light flux. The dichroic mirror 25 reflects the illumination light converted into a parallel light beam by the collimator lens 27 toward the objective lens 15. The dichroic mirror 25 transmits measurement light from an OCT optical system 60 described later and return light of measurement light from the patient's eye E. The illumination light that has become a parallel light beam is reflected by the dichroic mirror 25 and projected onto the patient's eye E via the objective lens 15. Illumination light (a part) projected onto the patient's eye E is reflected by the cornea. The return light (sometimes referred to as observation light) of illumination light from the patient's eye E enters the main observation optical system 30 and the sub observation optical system 40 via the objective lens 15.

(Main observation optical system)
The main observation optical system 30 is used for observing the patient's eye E illuminated by the illumination optical system 20 with the surgeon's microscope 6 via the objective lens 15. As shown in FIG. 3, the left and right main observation optical systems 30 are provided as a pair. 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 15.

  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 variable magnification 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 patient's 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 patient's eye E along the observation optical axis OR and guides it to the imaging 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 ophthalmic surgical microscope 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 patient's eye E 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 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.

  The main observation optical system 30 may be configured to include a stereo variator configured to be detachable from the optical path of the observation light. The stereo variator is an optical axis position changing element for changing the relative positions of the observation optical axes OL and OR respectively guided by the left and right variable magnification lens systems 31. The stereo variator is removably moved with respect to the observation optical path by a solenoid controlled by a control unit 210 described later. For example, the stereo variator is retracted to a retracted position provided on the operator side with respect to the observation optical path.

(Sub-observation optical system)
The sub-observation optical system 40 is used for observing the patient's eye E illuminated by the illumination optical system 20 with the assistant's microscope 7 via the objective lens 15. The sub-observation optical system 40 guides the illumination light reflected by the patient's eye E illuminated by the illumination optical system 20 to the assistant eyepiece 43.

  The sub-observation optical system 40 is also provided with a pair of left and right optical systems, and stereoscopic observation with binocular is possible. The sub observation optical system 40 can change the position with respect to the main observation optical system 30 so that the assistant can change the position. In particular, the sub-observation optical system 40 is configured to be rotatable about the optical axis O of the objective lens 15.

  The sub observation optical system 40 includes a prism 41, a reflection mirror 42, and an assistant eyepiece 43. The sub observation optical system 40 may further include an imaging lens 44 disposed between the prism 41 and the reflection mirror 42. The return light of the illumination light from the patient's eye E passes through the objective lens 15 and is reflected by the reflecting surface 41a of the prism 41. The return light of the illumination light reflected by the reflecting surface 41 a passes through, for example, the imaging lens 44, is reflected by the reflecting mirror 42, and is guided to the assistant eyepiece 43. Similarly, the return light of the illumination light from the patient's eye E passes through the objective lens 15 and enters the zoom lens system 31 of the left observation optical system 30L and the right observation optical system 30R.

(OCT optical system)
As shown in FIG. 2, the OCT optical system 60 includes an OCT unit 70, an optical fiber 70a, a collimating lens 101, an optical scanner 102, a first lens group 103, a second lens group 104, and a relay optical system. 105. In FIG. 2, the measurement light generated by the OCT optical system 60 is shown to enter the patient's eye E with a predetermined incident angle. However, the configuration of the embodiment is limited to the incident angle of the measurement light. Is not to be done.

  As shown in FIG. 4, the OCT unit 70 includes an interference optical system. The interference optical system divides the light from the OCT light source unit 71 into the reference light LR and the measurement light LS, and detects the interference light LC between the return light of the measurement light LS guided to the patient's eye E and the reference light LR. . One end of an optical fiber 70 a is connected to the OCT unit 70. The measurement light LS generated by the interference optical system in the OCT unit 70 is emitted from the other end of the optical fiber 70a. The return light of the measurement light LS guided to the patient's eye E by the OCT optical system 60 described later travels in the opposite direction on the same path and enters the other end of the optical fiber 70a.

  The other end of the optical fiber 70 a (measurement light emission end) is disposed at a position facing the collimating lens 101. The measurement light LS emitted from the other end of the optical fiber 70 a enters the collimating lens 101. The return light of the measurement light LS that has passed through the collimator lens 101 is incident on the other end of the optical fiber 70a.

  The collimating lens 101 turns the measurement light LS emitted from the other end of the optical fiber 70a into a parallel light beam. The collimator lens 101 and the other end of the optical fiber 70a are configured to be relatively movable along the optical axis of the measurement light LS. In this embodiment, the collimator lens 101 is configured to be movable along the optical axis of the measurement light LS, but the other end of the optical fiber 70a is configured to be movable along the optical axis of the measurement light LS. May be.

  The optical scanner 102 deflects the measurement light LS, which has been converted into a parallel light beam by the collimator lens 101, one-dimensionally or two-dimensionally. The optical scanner 102 is configured so that the deflection surface can be rotated about one axis, or the deflection surface can be rotated about each of two axes orthogonal to (intersect) each other. A deflecting member is used. Examples of the deflecting member include a galvanometer mirror, a polygon mirror, a rotating mirror, and a MEMS (Micro Electro Mechanical Systems) mirror scanner. In this embodiment, the optical scanner 102 includes a galvanometer mirror. That is, the optical scanner 102 is configured such that the deflection surface is rotatable about the first axis and the deflection surface is rotatable about the second axis orthogonal to the first axis. A second scanner 102b. A relay optical system 105 is provided between the first scanner 102a and the second scanner 102b.

  The first lens group 103 includes one or more lenses. The second lens group 104 includes one or more lenses. The deflection surface of the first scanner 102a and the deflection surface of the second scanner 102b are optically substantially conjugate. The magnification of the OCT optical system 60 can be determined by the focal length of the first lens group 103 and the focal length of the second lens group 104.

  As described above, the dichroic mirror 25 reflects visible light (illumination light) and transmits infrared light (measurement light and its return light). The dichroic mirror 25 may be a beam splitter or a half mirror.

  Instead of the movement of the collimating lens 101 in the optical axis direction, at least one of the first lens group 103 and the second lens group 104 may be configured to be movable along the optical axis of the measurement light LS. Further, in addition to the movement of the collimating lens 101 in the optical axis direction, at least one of the first lens group 103 and the second lens group 104 may be configured to be movable along the optical axis of the measurement light LS.

<OCT unit>
The OCT unit 70 has an interference optical system as shown in FIG. The detection result (detection signal) of the interference light LC detected by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit 200.

  The OCT light source unit 71 includes a wavelength scanning type (wavelength sweep type) light source capable of scanning (sweeping) the wavelength of emitted light, as in a general swept source type OCT apparatus. The OCT light source unit 71 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 OCT light source unit 71 is indicated by a symbol L0.

  The light L0 output from the OCT light source unit 71 is guided to the polarization controller 73 by the optical fiber 72 and its polarization state is adjusted. The polarization controller 73 adjusts the polarization state of the light L0 guided through the optical fiber 72, for example, by applying external stress to the looped optical fiber 72.

  The light L0 whose polarization state is adjusted by the polarization controller 73 is guided to the fiber coupler 75 by the optical fiber 74 and split into the measurement light LS and the reference light LR.

  The reference light LR is guided to the collimator 81 by the optical fiber 80 and becomes a parallel light beam. The reference light LR that has become a parallel light beam is guided to the corner cube 84 via the optical path length correction member 82 and the dispersion compensation member 83. The optical path length correction member 82 functions as a delay unit for matching the optical path lengths (optical distances) of the reference light LR and the measurement light LS. The dispersion compensation member 83 functions as a dispersion compensation means for matching the dispersion characteristics of the reference light LR and the measurement light LS.

  The corner cube 84 folds the traveling direction of the reference light LR that has become a parallel light beam by the collimator 81 in the reverse direction. The optical path of the reference light LR incident on the corner cube 84 and the optical path of the reference light LR emitted from the corner cube 84 are parallel. The corner cube 84 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 84 passes through the dispersion compensation member 83 and the optical path length correction member 82, is converted from a parallel light beam into a focused light beam by the collimator 86, enters the optical fiber 87, and is guided to the polarization controller 88. Accordingly, the polarization state of the reference light LR is adjusted.

  For example, the polarization controller 88 has the same configuration as the polarization controller 73. The reference light LR whose polarization state has been adjusted by the polarization controller 88 is guided to the attenuator 90 by the optical fiber 89, and the amount of light is adjusted under the control of the arithmetic control unit 200. The reference light LR whose light amount has been adjusted by the attenuator 90 is guided to the fiber coupler 92 by the optical fiber 91.

  The measurement light LS generated by the fiber coupler 75 is guided to the collimating lens 101 by the optical fiber 70a (see FIG. 2). The measurement light LS incident on the collimator lens 101 reaches the dichroic mirror 25 via the optical scanner 102, the first lens group 103, and the second lens group 104. Then, the measurement light LS passes through the dichroic mirror 25 and is irradiated to the patient's eye E via the objective lens 15. The measurement light LS is scattered (including reflection) at various depth positions of the patient's eye E. The backscattered light of the measurement light LS from the patient's eye E travels in the opposite direction on the same path as the forward path, is guided to the fiber coupler 75, and reaches the fiber coupler 92 via the optical fiber 78.

  The fiber coupler 92 generates interference light by combining (interfering) the measurement light LS incident via the optical fiber 78 and the reference light LR incident via the optical fiber 91. The fiber coupler 92 branches the interference light between the measurement light LS and the reference light LR at a predetermined branching ratio (for example, 50:50), thereby generating a pair of interference lights LC. A pair of interference light LC emitted from the fiber coupler 92 is guided to the detector 95 by optical fibers 93 and 94, respectively.

  The detector 95 is, for example, a balanced photo diode (hereinafter referred to as “BPD”) that includes a pair of photodetectors that respectively detect a pair of interference lights LC and outputs a difference between detection results obtained by the pair of photodetectors. The detector 95 sends the detection result (detection signal) to the arithmetic control unit 200. The arithmetic control unit 200 forms a cross-sectional image by performing Fourier transform or the like on the spectrum distribution based on the detection result obtained by the detector 95 for each series of wavelength scans (for each A line), for example. The arithmetic control unit 200 causes the display unit 300 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.

[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 95 and forms an OCT image of the patient eye E. The arithmetic processing for this is the same as that of a conventional swept source type OCT apparatus.

  The arithmetic control unit 200 controls the OCT optical system 60. For example, the arithmetic control unit 200 displays an OCT image of the patient's eye E on the display unit 300. As a control for the OCT optical system 60, the arithmetic control unit 200 controls the operation of the OCT light source unit 71, the movement control of the corner cube 84, the operation control of the detector 95, the operation control of the attenuator 90, and the operations of the polarization controllers 73 and 88. Control and so on. In addition, the arithmetic control unit 200 can perform focusing control by movement of the collimating lens 101, the first lens group 103, and the second lens group 104 in the optical axis direction, scan control by the optical scanner 102, and the like. .

  The arithmetic control unit 200 includes, for example, a microprocessor, a RAM (Random Access Memory), a ROM (Read Only Memory), a hard disk drive, a communication interface, and the like, 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 (Liquid Crystal Display).

[Control system]
FIG. 5 shows an example of the configuration of the control system of the microscope for ophthalmic surgery 1. In FIG. 5, the same parts as those in FIGS.

(Control part)
The control system of the microscope for ophthalmologic surgery 1 is configured with a control unit 210 as a center. The control unit 210 has functions of both a control unit for controlling the microscope for ophthalmic surgery 1 and a control unit (arithmetic control unit 200) for controlling the OCT optical system 60. One or more elements for realizing these means may be distributed in the ophthalmic surgical microscope 1 and the outside thereof. 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 56 a, the zoom lens driving unit 31 d, and the illumination light source 21 of the microscope for ophthalmic surgery 1. The main control unit 211 controls the OCT light source unit 71, the polarization controllers 73 and 88, the attenuator 90, the lens driving unit 101a, the optical scanner 102, the detector 95, the image forming unit 220, and the data processing unit 230. For example, the main control unit 211 can perform the above-described various controls based on the operation contents of the operator with respect to the foot switch 8.

  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 lens driving unit 101a controls the moving mechanism 101b. The moving mechanism 101b moves the collimating lens 101 along the optical axis of the measurement light LS. For example, the moving mechanism 101b transmits a holding member that holds the collimating lens 101, a slide mechanism that moves the holding member in the optical axis direction of the measurement light LS, and a driving force generated by the lens driving unit 101a to the slide mechanism. And a member to be used. The main control unit 211 controls the collimating lens 101 by controlling the lens driving unit 101a so that, for example, the return light of the measurement light LS from the patient's eye E, the interference light LC, and the intensity of the detection signal are equal to or higher than a predetermined intensity. It is possible to move. Moreover, the moving mechanism 101b can move the collimating lens 101 manually. When moving manually, the moving mechanism 101b can move the collimating lens 101 by controlling the lens driving unit 101a based on the operation content of the user (for example, an operator) with respect to the foot switch 8 or an operation unit (not shown). Is possible.

  The moving mechanism 101b may move at least one of the first lens group 103 and the second lens group 104 along the optical axis of the measurement light LS. In this case, the main control unit 211 can move at least one of the first lens group 103 and the second lens group 104 along the optical axis of the measurement light LS by controlling the lens driving unit 101a. is there.

  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.

(Image forming part)
The image forming unit 220 forms image data of a cross-sectional image such as the anterior segment or the fundus based on the detection signal from the detector 95. 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.

(Data processing part)
The data 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 data processing unit 230 executes various correction processes such as image brightness correction and dispersion correction. The data processing unit 230 can also perform various image processing and analysis processing on images (fundus image, anterior eye image, etc.) obtained by the microscope 1 for ophthalmic surgery.

  The data 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 an anterior segment or 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 data processing unit 230 performs rendering processing on the volume data to form image data of a pseudo three-dimensional image when viewed from a specific line-of-sight direction. Examples of rendering processing include volume rendering and MIP (Maximum Intensity Projection). The pseudo three-dimensional image is displayed on a display device such as the display unit 300.

  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 data 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.

  In the embodiment, the interference optical system includes fiber couplers 75 and 92, a detector 95, and optical fibers and various optical members that guide the reference light LR and the measurement light LS therebetween. The interference optical system may further include an OCT light source unit 71. This interference optical system is an example of the “interference optical system” in the embodiment. The main observation optical system 30 is an example of an “observation optical system” according to the embodiment. The dichroic mirror 25 is an example of an “optical path coupling member” according to the embodiment. The moving mechanism 101b is an example of a “first moving mechanism” and a “second moving mechanism” according to the embodiment. The sub-observation optical system 40 is an example of an “auxiliary optical system” according to the embodiment that performs at least one of irradiation of light to the patient's eye and reception of light from the patient's eye.

[Operation example]
An operation example of the microscope for ophthalmic surgery 1 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, the surgeon adjusts the position and orientation of the second arm 4 and then operates the foot switch 8 to move the surgeon's microscope 6 and the assistant's microscope 7 vertically and horizontally. The operator's microscope 6 and the assistant's microscope 7 are stopped at desired positions. Thereafter, the surgeon adjusts the eye width, the observation angle, the amount of light, and the like to adjust the focus and position. Thereby, the patient's eye E is illuminated by the illumination light of the illumination optical system 20, and the operator can observe the patient's eye E while looking through the eyepiece lens 37, and the assistant looks at the patient's eye E while looking through the assistant's eyepiece 43. Can be observed.

  When performing OCT measurement, a scan range and a scan pattern (the shape of the range and the size of the scan region) of measurement light for OCT measurement are set. The scan range of the measurement light can be set automatically or manually. When automatically setting the scan range of the measurement light, for example, the same range as the pre-operative OCT measurement is reproduced, or the surgical site is detected by analyzing the frame of the current observation image by the TV camera 56, It is possible to set a range including the detected surgical site. The preoperative OCT measurement range can be specified by recording the preoperative OCT scan range in a three-dimensional image or a front image and comparing it with the frame of the current observation image. Further, when manually setting the scan range of the measurement light, for example, an operator sets a desired scan range while viewing a live image of an OCT image. The scan pattern setting method includes automatic scan pattern setting similar to that before the operation and manual setting using the foot switch 8. When manually setting a scan pattern, scan pattern options are presented on the display unit 300 or the like, and desired options are designated using the foot switch 8 or the like. The scan pattern options may include at least one of a one-dimensional pattern and a two-dimensional pattern.

  OCT measurement is started after the setting relating to the scanning of the measurement light is completed (however, when a live image of an OCT image is used for the setting, OCT measurement is already started). In addition, in order to perform OCT measurement, the control unit 210 controls the OCT light source unit 71 and the corner cube 84 and controls the optical scanner 102 based on the scan region set as described above. The image forming unit 220 forms a cross-sectional image of the patient's eye E based on the interference light spectrum obtained by OCT measurement. When the scan pattern is a three-dimensional scan, the data processing unit 230 forms a three-dimensional image of the patient's eye E based on the plurality of cross-sectional images formed by the image forming unit 220.

  The surgeon performs an operation while selectively performing visual observation with the ophthalmic surgery microscope 1, observation of a visible image acquired with the ophthalmic surgery microscope 1, and observation of an OCT image acquired with the OCT optical system 60. Is possible.

[Modification]
At least one of the optical members constituting the OCT optical system 60 may be configured as a unit (attachment) that can be attached to and detached from the lens barrel unit 10 (microscope main body). Such a detachable unit includes a collimating lens 101, an optical scanner 102, a first lens group 103, and a second lens group 104.

  In the above-described embodiment, the case where the optical path of the OCT optical system 60 is coupled to the optical path of the illumination optical system 20 has been described. However, the configuration of the microscope for ophthalmic surgery according to the embodiment is not limited to this. For example, the optical path of the OCT optical system 60 may be coupled to the optical path of the main observation optical system 30, or the optical path of the OCT optical system 60 may be coupled to the optical path of the sub-observation optical system 40. It may be. Further, the optical path of the OCT optical system 60 may be configured independently without being coupled to the optical path of the illumination optical system 20 or the optical path of the observation optical system (the main observation optical system 30 and the sub-observation optical system 40). At this time, instead of the dichroic mirror 25, a total reflection mirror can be arranged.

[effect]
The effect of the microscope for ophthalmic surgery according to the embodiment will be described.

  An ophthalmic surgical microscope (for example, an ophthalmic surgical microscope 1) according to an embodiment includes an illumination optical system, an observation optical system, an interference optical system (for example, fiber couplers 75 and 92, a detector 95), and an optical scanner. A collimating lens, an optical fiber, and a moving mechanism. The illumination optical system (for example, the illumination optical system 20) illuminates the patient's eye (for example, the patient's eye E) with illumination light. The observation optical system (for example, the main observation optical system 30) is used for observing the patient's eye illuminated by the illumination optical system. The interference optical system divides the light from the light source (for example, OCT light source unit 71) into measurement light (for example, measurement light LS) and reference light (for example, reference light LR), and returns the measurement light from the patient's eye. Interference light (for example, interference light LC) between the light and the reference light is detected. The optical scanner (for example, the optical scanner 102) is disposed in the optical path of the measurement light. The collimating lens (for example, the collimating lens 101) is disposed between the light source and the optical scanner in the optical path of the measurement light. The optical fiber (for example, the optical fiber 70a) guides the measurement light generated by the interference optical system, and the emission end of the measurement light is disposed at a position facing the collimator lens. The moving mechanism (for example, the moving mechanism 101b) relatively moves the collimating lens and the emitting end along the optical path of the measurement light.

  According to such a configuration, the collimating lens and the light emitting end of the optical fiber are relatively moved on the upstream side in the measurement light path from the optical scanner, so that the moving mechanism and its driving means (driving system) The degree of freedom of arrangement can be increased. Accordingly, it is possible to provide an ophthalmic surgical microscope that has a high degree of freedom in arrangement of the drive system and can observe a patient's eye and acquire an OCT image. In addition, highly accurate OCT measurement can be performed without significantly changing the existing configuration of the illumination optical system and the observation optical system. Furthermore, since it is only necessary to move a small and light optical member such as a collimating lens to the driving means, high-speed focusing operation, miniaturization of the driving means, cost reduction, and the like are possible.

  Moreover, the microscope for ophthalmic surgery according to the embodiment may include an optical path coupling member (for example, a dichroic mirror 25). The optical path coupling member (for example, the dichroic mirror 25) is disposed on the downstream side of the optical fiber in the path of the measurement light toward the patient's eye, and couples the optical path of the measurement light to the optical path of the illumination light.

  According to such a configuration, the collimating lens and the emission end of the optical fiber are relatively moved on the upstream side in the measurement light path from the optical path coupling member, so that the moving mechanism and its driving means (driving system) ) Can be further enhanced.

  In the ophthalmic surgical microscope according to the embodiment, the optical scanner includes a first scanner (for example, the first scanner 102a) and a second scanner (for example, the second scanner 102b). The first scanner and the second scanner are arranged in order from the light source side and have different deflection directions. The second scanner deflects the measurement light toward the optical path coupling member.

  According to such a configuration, since the optical path of the measurement light deflected using the second scanner is coupled to the optical path of the illumination light, the number of optical members such as a deflection member for deflecting the measurement light is reduced. It becomes possible.

  In the ophthalmic surgical microscope according to the embodiment, a relay optical system (for example, the relay optical system 105) is provided between the first scanner and the second scanner.

  According to such a configuration, since the freedom degree of arrangement of the first scanner and the second scanner is increased by using the relay optical system, the interference optical system is disposed at a position away from the illumination optical system and the observation optical system. Can be placed.

  In the ophthalmic surgical microscope according to the embodiment, the first lens group (for example, the first lens group 103) and the second lens group (for example, the first lens group) are provided downstream of the optical scanner in the measurement light path toward the patient's eye. Two lens groups 104) are provided.

  According to such a configuration, it is possible to perform OCT measurement at a desired magnification without significantly changing the existing configuration of the illumination optical system and the observation optical system.

  The ophthalmic surgical microscope according to the embodiment includes an objective lens (for example, the objective lens 15). The illumination optical system illuminates the patient's eye with illumination light through the objective lens. In the observation optical system, the return light of the illumination light from the patient's eye is guided through the objective lens.

  According to such a configuration, it is possible to provide an ophthalmic surgical microscope capable of observing a patient's eye and acquiring an OCT image via the objective lens.

[Other variations]
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.

  The configurations described in the above-described embodiments can be arbitrarily combined.

DESCRIPTION OF SYMBOLS 1 Ophthalmic surgery microscope 2 Support | pillar 3 1st arm 4 2nd arm 5 Driving device 6 Surgeon's microscope 7 Assistant's microscope 8 Foot switch 10 Lens tube part 15 Objective lens 20 Illumination optical system 25 Dichroic mirror 30 Main observation optical system 40 Sub-observation optical system 60 OCT optical system 70 OCT unit 101 Collimate lens 102 Optical scanner 103 First lens group 104 Second lens group 105 Relay optical system

Claims (6)

An illumination optical system for illuminating the patient's eye with illumination light;
An observation optical system for observing the patient's eye illuminated by the illumination optical system;
An interference optical system that divides light from a light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light;
An optical scanner disposed in the optical path of the measurement light;
A collimating lens disposed between the light source and the optical scanner in the optical path of the measurement light;
An optical fiber that guides the measurement light generated by the interference optical system and has an emission end of the measurement light disposed at a position facing the collimator lens;
A moving mechanism that relatively moves the collimating lens and the emission end along the optical path of the measurement light;
Including ophthalmic surgical microscope. The optical path coupling member which is arrange | positioned in the downstream of the said optical fiber in the path | route of the said measurement light toward the said patient's eyes, and couple | bonds the optical path of the said measurement light with the optical path of the said illumination light is characterized by the above-mentioned. The microscope for ophthalmic surgery as described. The optical scanner includes a first scanner and a second scanner arranged in order from the light source side and having different deflection directions,
The microscope for ophthalmologic surgery according to claim 2, wherein the second scanner deflects the measurement light toward the optical path coupling member. The microscope for ophthalmic surgery according to claim 3, wherein a relay optical system is provided between the first scanner and the second scanner. The first lens group and the second lens group are provided downstream of the optical scanner in the path of the measurement light toward the patient's eye. The microscope for ophthalmic surgery according to 1. Including an objective lens,
The illumination optical system illuminates the patient eye with the illumination light through the objective lens,
The microscope for ophthalmic surgery according to any one of claims 1 to 5, wherein the observation optical system guides the return light of the illumination light from the patient's eye through the objective lens. .

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