JP2013078398A - Laser operation apparatus for ophthalmology - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmologic operation apparatus capable of efficiently performing an operation by improving the Z-directional moving speed of a laser spot with simple constitution.SOLUTION: A laser operation apparatus for ophthalmology includes a laser beam source which emits a pulse laser beam, and an irradiation optical system which serves as an irradiation optical system irradiating a target position with the laser beam, and has a moving optical system moving the spot of the laser beam in three dimensions, and cuts or breaks eyeball tissue by the laser beam. The moving optical system includes an objective lens for converging the laser beam on the target position and forming a spot, a first lens unit comprising at least one lens for guiding the laser beam as divergent beam or convergent beam toward the objective lens, and optical path change means placed between the first lens unit and objective lens, and changing the optical path length between the first lens unit and the objective lens.

Description

  The present invention relates to an ophthalmic laser surgical apparatus for irradiating a surgical eye with laser light to cut and remove tissue.

  In recent years, there has been proposed a technique for cutting (crushing) a tissue such as a crystalline lens of a patient's eye (surgical eye) by irradiating an ultrashort pulse laser beam such as a femtosecond pulse laser beam (see, for example, Patent Document 1). The apparatus of Patent Document 1 mechanically cuts and crushes the lens tissue by generating a minute plasma at the target position (laser spot position) of the lens in order to treat cataract. Cataract is treated by removing these tissues and inserting an intraocular lens or the like into the eye. When the depth direction of the patient's eye is the Z direction and the direction orthogonal to the Z direction is the XY direction, two galvanometer mirrors are used when the laser spot is moved (scanned) in the XY direction. On the other hand, when moving (scanning) the laser spot in the Z direction, the objective lens or the lens of the beam expander arranged upstream from the objective lens is moved along the Z direction (optical axis).

Special table 2010-538699

  Such movement of the laser spot in the Z direction requires movement of an optical element such as a lens. For this reason, when moving a laser spot at high speed along a Z direction, the positional accuracy in the movement of a lens and the suppression of the vibration accompanying a movement of a lens are requested | required. In order to cope with these, the apparatus configuration becomes complicated.

  It is a technical object of the present invention to provide an ophthalmic surgical system that can efficiently perform surgery by improving the moving speed of a laser spot in the Z direction with a simple configuration.

In order to solve the above-mentioned problems, the present invention has the following configuration.
(1) a laser light source that emits pulsed laser light, and an irradiation optical system that irradiates the target position with the laser light, the irradiation optical system having a moving optical system that three-dimensionally moves the spot of the laser light; In the ophthalmic laser surgical apparatus for cutting or crushing eyeball tissue with laser light, the moving optical system includes an objective lens for focusing the laser light at a target position to form the spot, and the laser light. A first lens unit comprising at least one lens for guiding light toward the objective lens as diverging light or convergent light; and the first lens unit is disposed between the first lens unit and the objective lens. Optical path length changing means for changing the optical path length between the unit and the objective lens.
(2) The ophthalmic laser surgical apparatus according to (1) is placed between the optical path length changing unit and the objective lens, and the divergence of the laser light toward the objective lens through the optical path length changing unit A second lens unit including at least one lens for changing the state or the convergence state is provided.
(3) In the ophthalmic laser surgical apparatus according to (2), the moving optical system includes a scanning unit for two-dimensionally scanning the laser light, and the scanning unit includes the optical path length changing unit. The passing laser beam is two-dimensionally scanned.
(4) In the ophthalmic laser apparatus according to any one of (1) to (3), the optical path length changing unit includes a first reflecting member having a reflecting surface that deflects the optical path of the user light, and the first reflecting member. A second reflecting member having a reflecting surface orthogonal to the reflecting surface of the reflecting member and having a reflecting surface that forms an angle of 45 degrees with respect to the optical axis of the laser beam before being deflected by the first reflecting member; A reflecting unit having two reflecting surfaces for making the laser beam deflected by the first reflecting member incident on the second reflecting member, the reflecting unit having a reflecting surface parallel to the reflecting surface of the first reflecting member. A reflection unit comprising: 3 reflection members; a fourth reflection member having a reflection surface parallel to the reflection surface of the second reflection member; and laser light reflected by the first reflection member and the second reflection member In order to change the optical path length of the incident laser beam, And a drive unit that moves the reflection unit along the optical axis direction of the laser light reflected by the reflection member.
(5) In the ophthalmic laser surgical apparatus according to (4), the first reflecting member is disposed so as to deflect the laser light in a right angle direction.
(6) In the ophthalmic laser surgical apparatus according to (4) or (5), the reflection unit is a right-angle prism.
(7) The ophthalmic laser surgical apparatus according to any one of (4) to (6), wherein the first reflecting member and the second reflecting member are an integrated right-angle prism. .
(8) The ophthalmic laser surgical apparatus according to any one of (1) to (7), wherein the first lens unit has a negative refractive power that uses incident laser light as divergent light. Do

  According to the present invention, with a simple configuration, the moving speed of the laser spot in the Z direction can be improved and surgery can be performed efficiently.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a schematic configuration diagram of an ophthalmic laser surgical operation apparatus according to an embodiment of the present invention. The ophthalmic laser surgical apparatus of this embodiment is an apparatus that cuts and crushes the crystalline lens of the surgical eye with a laser.

  An ophthalmic laser surgical apparatus 100 includes a laser unit (laser light source) 10 that emits a pulsed laser beam having a characteristic of generating a breakdown at a condensing point, and a laser that guides the laser beam and irradiates a target (eyeball tissue). An irradiation optical system (laser irradiation unit) 20, an observation optical system (observation unit) 30 for observing the surgical eye, an eyeball fixing unit 40 for fixing and holding the surgical eye, an operation unit 50 for operating the apparatus 100, A monitor 60 that is a display unit for setting and confirming the apparatus 100 and a control unit 70 that controls and controls the apparatus 100 are provided.

  The laser unit 10 is a laser light source that emits an ultrashort pulse laser that generates plasma (causes breakdown) at a laser condensing point (laser spot). As the laser unit 10, a device that emits a pulse laser having a pulse width on the order of femtoseconds to picoseconds is used. At the focal point of the pulse laser, plasma is generated, and the target tissue, here, the lens that is the eyeball tissue, is incised and crushed.

  The irradiation optical system 20 includes a beam expander unit (hereinafter simply referred to as an expander) 21 for moving the spot of the pulse laser along the depth direction (Z direction, optical axis direction), and the spot of the pulse laser light. An optical scanner (scanning unit) 22 that scans (deflects) two-dimensionally (XY directions orthogonal to the optical axis) on the target surface, a beam splitter 23 that matches the optical axis of the laser with the observation optical axis, and the laser as a target An objective lens 24 as an imaging optical system that forms an image on a surface (a laser spot is formed on a target surface) and an applicator 25 that comes into contact with the surgical eye are provided. The expander 21 and the optical scanner 22 constitute a moving optical system that three-dimensionally moves the laser light spot within the crystalline lens of the surgical eye.

  The expander 21 is disposed upstream of the objective lens 24 (on the laser unit 10 side) and upstream of the optical scanner 22. By moving the optical element included in the expander 21 along the optical axis, the laser spot position is moved along the Z direction (details will be described later). As the optical scanner 22, for example, two galvanometer mirrors whose rotation axes are orthogonal to each other are used. As a result, the laser spot is scanned on a predetermined two-dimensional plane, here, an XY plane orthogonal to the optical axis. As the optical scanner, a resonant mirror, a rotating prism, a scanner using a combination of a polygon mirror and a galvanometer mirror, or the like can also be used. The beam splitter 23 is a dichroic mirror that reflects the laser light emitted from the laser unit (laser light source) 10 and transmits the illumination light and the reflected light of the illumination light. The objective lens 24 has a role of forming an image on the target surface with a pulse laser having a minute spot diameter on the order of micron to submicron. The applicator 25 is a translucent (transparent) contact lens, and is used for applanation of the cornea of a surgical eye. At this time, the cornea of the surgical eye is positioned at a certain position from the front surface (contact surface) of the applicator 25. Accordingly, the applicator 25 has a role of fixing and holding the eyeball tissue and positioning the laser irradiation.

  When breakdown occurs at the spot position of the laser, mechanical destruction (crack or the like) about the spot size occurs in the eyeball tissue. The laser spot is moved in the XY direction by the optical scanner 22 and moved in the Z direction by the expander 21 to be moved three-dimensionally (the position can be changed). In the eyeball tissue, the laser spot is moved three-dimensionally, and the spots are connected, whereby the eyeball tissue is cut into a three-dimensional shape (a preset laser irradiation pattern). Details of the laser irradiation pattern will be described later.

  The observation optical system 30 includes a camera 31 having a two-dimensional image sensor, a beam splitter 32, an illumination light source 33, illumination light, and an optical element 34 that is a light guide optical system for guiding reflected light from the surgical eye. I have. The beam splitter 32 has a characteristic of reflecting a part of the illumination light and transmitting a part of the reflected light (illumination light) from the surgical eye. In this embodiment, the beam splitter 32 is a half mirror. The illumination light source 33 emits illumination light suitable for illumination of the surgical eye such as visible light. The two-dimensional image sensor of the camera 31 is an imager having sensitivity to the wavelength of illumination light, for example. The illumination light source 33 may be a light source that emits infrared light. When the illumination light source emits infrared light, the camera 31 is preferably capable of receiving infrared light. Note that the observation optical system 30 shares the objective lens 24.

  The eyeball fixing unit 40 includes a suction ring 41 and an applicator 25. The suction ring 41 is an annular member and has a shape that comes into contact with the sclera of the anterior segment. The suction ring 41 receives suction by a pump or the like (not shown), and fixes and holds the surgical eye by sucking the eyeball to the suction ring 41. The applicator 25 is shared by the eyeball fixing unit 40. Further, the applicator may be of a type that fills the inside of the ring 41 with a liquid. In this case, the liquid is filled between the lens (contact lens) and the cornea, and the cornea is not applanated by the lens.

  The operation unit 50 includes an input unit 51 for setting the apparatus 100 and a foot switch 52 serving as an irradiation instruction switch for inputting a trigger signal for laser irradiation. The input means 51 includes a mouse that is a pointing device for designating surgical conditions and the like on the setting screen displayed on the monitor 60, a numerical value such as surgical conditions, and a keyboard for inputting information.

  On the monitor 60, a front image (observation image) of the surgical eye taken by the camera 31 is copied. The monitor 60 displays the surgical conditions, the laser irradiation pattern, and the like.

  The control unit 70 is a CPU (Central Processing Unit), to which the laser unit 10, the expander 21, the optical scanner 22, the camera 31, the illumination light source 33, and the ring 41 are connected. The control unit 70 is connected to a memory 71 for storing a control program, a laser irradiation pattern, a set surgical condition, a captured image, and the like. The memory 71 also stores measurement data acquired by another measuring device.

  Next, the movement of the laser spot in the Z direction will be described. FIG. 2 is a diagram illustrating an optical system that moves the laser spot along the Z direction. In FIG. 2, various optical members (the optical scanner 22, the mirror 23, the applicator 25, etc.) provided in the optical path are omitted for the sake of simplicity.

  The expander (beam expander unit) 21 includes a lens drive that is a first lens unit, a mirror 81, a mirror 82, a reflection unit 85, a lens 80B that is a second lens unit, and a drive unit 88 that moves the reflection unit 85. I have.

  The laser beam B from the laser unit 10 enters the expander 21 as parallel light. The lens 80A is a lens (first lens unit) having a negative refractive power and includes at least one lens, and has a role of making incident parallel light a diverging light. The lens 80A has a fixed focal length and is fixedly disposed on the optical axis L. For this reason, divergent light having a constant divergence angle is emitted from the lens 80A. In this embodiment, the lens 80B is a lens (second lens unit) having a positive refractive power, and includes at least one lens. Such a lens 80B has a role of changing the diverging state of the incident diverging light (changing the diverging state in the direction of decreasing the beam diameter), guiding the light to the objective lens 24 (not shown). . The lens 80B has a fixed focal length and is fixedly disposed on the optical axis L. The objective lens 24 has a fixed focal length and is fixedly disposed on the optical axis L. For this reason, the objective lens 24 changes the imaging position of the laser spot in the Z direction according to the divergence angle (or convergence angle) of the incident laser light.

  Between the lens 80A and the lens 80B, a mirror 81, a mirror 82, and a reflection unit 85 are disposed. In the present embodiment, the mirrors 81 and 82 and the reflection unit 85 are made to function as optical path changing means for changing the optical path length between the lens 80A and the objective lens 28. The mirror 81 is a total reflection mirror (first reflection member) fixedly disposed on the optical axis L, and is disposed so as to deflect the laser light axis before entering the mirror 81 at a right angle. The reflection surface of the mirror 81 forms an angle of 45 degrees with respect to the incident laser beam and the axis of the emitted (reflected) laser beam (the axis of the laser beam before and after deflection).

  In the reflection direction by the lens 80A, the reflection unit 85 is arranged to be movable (the optical path length can be changed) with respect to the optical axis direction. The mirror 82 is a total reflection mirror (second reflection member) that is fixedly disposed on the optical axis L in order to reflect the laser light reflected by the reflection unit 85 toward the lens 80B. The mirror 82 is disposed so that the reflection surface of the mirror 82 is orthogonal to the reflection surface of the mirror 81. The mirror 82 is disposed such that the reflection surface of the mirror 82 forms an angle of 45 degrees with respect to the optical axis L (the axis of the laser light before being deflected by the mirror 81). In the present embodiment, the mirror 81 and the mirror 82 are arranged so that the reflecting surfaces are orthogonal to each other and form an angle of 45 degrees with respect to the optical axis L.

  The reflection unit 85 is a right angle prism made of glass. The reflecting unit 85 includes a reflecting portion (third reflecting member) 86 having a reflecting surface parallel to the reflecting surface of the mirror 81 and a reflecting portion (fourth reflecting member) 87 having a reflecting surface parallel to the reflecting surface of the mirror 82. I have. The reflecting surfaces of the reflecting portion 86 and the reflecting portion 87 are orthogonal to each other. For this reason, the reflection unit 85 has a right-angled isosceles triangle shape. The reflection surface of the reflection part 86 forms an angle of 45 degrees with respect to the axis of the laser beam deflected by the mirror 81. The position of the reflecting unit 85 is determined on the reflecting surface of the reflecting portion 87 so that the laser beam incident on the mirror 82 has an angle of 45 degrees. The reflectors 86 and 87 are integrally formed in the right-angle prism. The reflection unit 85 has a function of reflecting to the mirror 82 in a state where the directions of the laser beams from the mirror 81 are matched. In the right-angle prism, the reflecting portions 86 and 87 are coated so as to be total reflection mirrors.

  The laser light that has passed through the lens 80A is reflected by the mirror 81 and deflected in the right-angle direction, and reflected by the reflecting portion 86 and deflected in the right-angle direction. The laser beam reflected by the reflecting portion 86 is further reflected by the reflecting portion 87 and deflected in a right angle direction, and travels toward the mirror 82. The light is reflected by the mirror 82 and deflected in the right-angle direction, and passes through the lens 80B. Thereby, the laser light is deflected (returned) in the same direction as the optical axis L when passing through the lens 80A and reaches the lens 80B. The laser beam is turned into a laser spot by the objective lens 24.

  The reflection unit 85 is held by a drive unit 88 so as to be movable in one direction. The drive unit 88 includes a stepping motor and a slider (rail). The drive unit 88 moves the reflection unit 85 along the optical axis direction of the laser light after being deflected by the mirror 81.

  When the drive unit 88 moves the reflection unit 85, the optical path length between the lens 80A and the lens 80B (objective lens 24) is changed. Since the laser light emitted from the lens 80A is divergent light having a constant divergence angle, the beam diameter of the laser light on the lens 80B is changed with the change of the optical path length of the laser light. Since the focal length of the lens 80B is constant, the divergence angle (or convergence angle) of the beam from the lens 80B varies depending on the beam diameter of the incident laser light. Further, since the focal length of the objective lens 24 is constant, the position of the laser spot (condensing position) formed by the objective lens 24 varies in the Z direction depending on the divergence angle of the laser light incident on the objective lens 24. Become.

  The movement of the focal position in the Z direction will be described in detail with reference to FIG. In FIG. 2, the change state of the optical path length due to the movement of the reflection unit 85 is indicated by a solid line portion and a dotted line portion. .

  When the reflection unit 85 is at the position indicated by the solid line, the diverging light emitted from the lens 80A is reflected (deflected at right angles) by the mirror 81, the reflection portion 86, the reflection portion 87, and the mirror 82 of the reflection unit 85, respectively. To the lens 80B. The divergent light is focused by the refractive power of the lens 80B and guided to the downstream optical element (emitted). Here, the laser light emitted from the lens 80B is assumed to be parallel light. Therefore, at the position of the reflection unit 85, the optical path length from the lens 80A to the lens 80B is such that the focal point of the lens 80A and the focal point of the lens 80B coincide. The laser beam is focused on the target surface by the objective lens 24. At this time, the laser spot is formed at the position of the focal length of the objective lens 24.

  On the other hand, when the reflecting unit 85 is disposed at the position of the reflecting unit 85a indicated by the dotted line, the diverging light emitted from the lens 80A is reflected by the mirror 81 and reflected by the reflecting portion of the reflecting unit 85a. Since the reflection unit 85a (dotted line portion) is closer to the mirrors 81 and 82 than the reflection unit 85 (solid line portion position), the optical path length is shortened, and as a result, the beam diameter of the laser light toward the lens 80B is reduced (divergence). The corner becomes smaller). The laser light emitted from the lens 80B is slightly diverged and enters the objective lens 24. The objective lens 24 collects the diverged beam further away. In other words, the laser spot is formed on the deeper side than when the reflection unit 85 is at the position indicated by the solid line.

  As described above, the optical path length of the laser light can be changed by moving the reflection unit 85 along one direction, and the position of the laser spot can be moved along the Z direction. In addition, the arrangement | positioning precision of a member improves by making the reflection unit 85 into an integral member (right angle prism). The reflection unit 85 that is a right-angle prism is configured to reflect the laser light in the same direction as the direction of the laser light incident on the reflection unit 85, so that the reflection unit 85 is directed to the laser light axis deflected by the mirror 81. The laser beam can be deflected with high accuracy with respect to the mirror 82 even if it is disposed at a tilt (tilt along the surface in the moving direction of the reflection unit 85). Further, in the movement operation of the reflection unit 85 by the drive unit 88, the above relationship is maintained even if the reflection unit 85 vibrates. For this reason, even if the reflection unit 85 is moved at a high speed, the laser spot is hardly displaced on the XY plane. Therefore, the movement of the laser spot in the Z direction can be speeded up with a simple configuration. Furthermore, the movement of the reflection unit 85 can change both the forward and backward optical path lengths of the laser light with respect to the reflection unit 85. For this reason, the position of the laser spot in the Z direction can be greatly changed (twice here) by the minute movement of the reflection unit 85. Thereby, the speed of a series of laser irradiation can be improved with an irradiation pattern with a high frequency of movement (scanning) of the laser spot in the Z direction, and the operation time can be shortened. For example, after finishing the movement of the position of the laser spot in the Z direction, it is possible to change the position in the XY direction and increase the irradiation pattern for moving the laser spot along the Z direction at another position on the XY. Further, by making the first lens group a lens having a negative refractive power, the laser light can be diverged, and the laser light does not form an image in the optical path to the second lens group. For this reason, the reflection unit 85 is hardly damaged by the pulse laser. Further, the beam diameter can be reduced by using the second lens group as a lens having a positive refractive power. Thereby, it is not necessary to increase the size of members downstream of the lens 80B (for example, the optical scanner 22, the objective lens 24, etc.), and the increase in size of the apparatus can be suppressed.

  The operation of the apparatus having the above configuration will be described. Prior to surgery, the surgeon sets the surgical conditions and patterns. The operator lays the patient on an operating table or the like and fixes the eyeball by the eyeball fixing unit 40. The surgical eye is held by the suction link 41 and is applanated by the applicator 25. When the foot switch 42 is stepped on by the operator, the control unit 70 starts laser irradiation based on the trigger signal. The control unit 70 irradiates the laser based on the set surgical condition and irradiation pattern. The control unit 70 controls the laser unit 10 based on the irradiation pattern, and also controls the expander 21 (drive unit 88) and the optical scanner 22. At this time, the control unit 70 performs laser irradiation while moving the laser spot from the back side to the front side in the irradiation pattern. The lens tissue of the operative eye E (the lens nucleus and part of the sac) is cut and crushed. When the laser irradiation is finished, the crushed lens is removed by another perfusion suction device, an intraocular lens is installed in the sac of the surgical eye E, and the operation is finished.

  In the above description, the configuration in which the mirror 81 deflects the optical axis of the laser light in the orthogonal direction is not limited to this. Any configuration may be used as long as the orientation of the reflection unit 85 and the mirror 82 corresponds to the mirror 81 and the beam diameter on the objective lens 24 can be changed.

  In the above description, the mirrors 81 and 82 are configured by mirrors, but the present invention is not limited to this. Any structure that can deflect (reflect) the laser light while maintaining the relationship between the mirrors 81 and 82 may be used. The mirrors 81 and 82 may be integrated to form a right-angle prism. In this case, it is preferable to apply a reflective coating on the surface of the prism.

  In the above description, the reflection unit 85 is a right-angle prism, but the present invention is not limited to this. Any structure that deflects the laser light while maintaining the relationship between the reflecting portions 86 and 87 may be used. The reflection unit may be constituted by individual mirrors. Further, the reflection unit 85 may be a corner cube integrally manufactured.

  In the above description, the embodiment of crushing the crystalline lens of the surgical eye has been described as an example, but the present invention is not limited to this. Any structure may be used as long as the eyeball of the surgical eye is irradiated with laser to incise and crush the tissue. The present invention can be used in an apparatus for excising the cornea, iris, and the like.

  In the above description, the lens 80A is a lens having a negative refractive power, and the lens 80B is a lens having a positive refractive power. However, the present invention is not limited to this configuration. The first lens unit may be configured to diverge or converge the laser light on the optical path whose optical path length is changed, and may have a positive refractive power. The second lens unit group may have a negative refractive power as long as the second lens unit group guides the laser light to the objective lens 24. The first lens unit may be composed of at least one lens. Similarly, the second lens unit may be composed of at least two lenses.

  In the above description, the lens 80B as the second lens unit is used. However, the present invention is not limited to this. The lens 80B is not always necessary. Any configuration in which the beam diameter of the beam incident on the objective lens 24 is changed may be used. For example, the objective lens 24 may be arranged near the downstream of the mirror 82. In this case, the expander 21 is arranged downstream of the optical scanner 22.

  In the above description, the femtosecond pulse seed laser is used as the laser, but the present invention is not limited to this. A laser beam that emits an ultrashort pulse such as a picosecond pulse that does not involve heating, does not select the material of the object, can be processed minutely on the order of a micron, and can internally process a transparent object If it is.

  As described above, the present invention is not limited to the embodiment, and various modifications are possible. The present invention includes such modifications within the scope of making the technical idea the same.

It is a schematic block diagram of the ophthalmic surgery system which is embodiment of this invention. It is a figure explaining the optical system which moves a laser spot along a Z direction.

DESCRIPTION OF SYMBOLS 10 Laser unit 21 Beam expander unit 22 Optical scanner 80A, 80B Lens 81, 82 Mirror 85 Reflection unit 88 Drive unit 100 Ophthalmic laser surgery apparatus

Claims (8)

A laser light source that emits pulsed laser light, and an irradiation optical system that irradiates the target position with the laser light, the irradiation optical system having a moving optical system that three-dimensionally moves the spot of the laser light. In an ophthalmic laser surgical apparatus that cuts or crushes eyeball tissue with light,
The moving optical system includes:
An objective lens for condensing the laser beam at a target position to form the spot;
A first lens unit comprising at least one lens for guiding the laser light as diverging light or convergent light toward the objective lens;
An optical path length changing unit that is placed between the first lens unit and the objective lens and changes an optical path length between the first lens unit and the objective lens;
An ophthalmic laser surgical apparatus comprising: The ophthalmic laser surgical apparatus according to claim 1 is placed between the optical path length changing unit and the objective lens, and the divergence state or convergence of the laser light toward the objective lens through the optical path length changing unit An ophthalmic laser apparatus comprising a second lens unit including at least one lens for changing a state. 3. The ophthalmic laser surgical apparatus according to claim 2, wherein the moving optical system has a scanning unit for two-dimensionally scanning the laser light, and the scanning unit passes through the optical path length changing unit. An ophthalmic laser device that scans light two-dimensionally. In the ophthalmic laser apparatus according to any one of claims 1 to 3,
The optical path length changing means is
A first reflecting member having a reflecting surface for deflecting the optical path of the light;
A second reflection having a reflection surface orthogonal to the reflection surface of the first reflection member and a reflection surface forming an angle of 45 degrees with respect to the optical axis of the laser beam before being deflected by the first reflection member. Members,
A reflection unit comprising two reflection surfaces for making the laser beam deflected by the first reflection member incident on the second reflection member;
A third reflecting member having a reflecting surface parallel to the reflecting surface of the first reflecting member;
A fourth reflecting member having a reflecting surface parallel to the reflecting surface of the second reflecting member;
A reflection unit comprising:
In order to change the optical path length of the laser beam reflected by the first reflecting member and the laser beam incident on the second reflecting member, the laser beam reflected by the first reflecting member is changed along the optical axis direction of the laser beam. A drive unit for moving the reflection unit;
An ophthalmic laser device comprising: The ophthalmic laser surgical apparatus according to claim 4,
The first reflecting member is disposed so as to deflect the laser beam in a perpendicular direction.
An ophthalmic laser surgical apparatus characterized by that. In the ophthalmic laser surgical apparatus according to claim 4 or 5,
The reflection unit is a right angle prism;
An ophthalmic laser surgical apparatus characterized by that. The ophthalmic laser surgical apparatus according to any one of claims 4 to 6,
The first reflecting member and the second reflecting member are an integrated right-angle prism.
An ophthalmic laser surgical apparatus characterized by that. The ophthalmic laser surgical apparatus according to any one of claims 1 to 7,
The first lens unit has a negative refractive power that uses incident laser light as diverging light,
An ophthalmic laser surgical apparatus characterized by that.