JP2017086154A - Ophthalmological contact lens - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a contact lens that enables at least one of treatment, observation, and imaging of an eye of a patient to be performed satisfactorily.SOLUTION: An ophthalmological contact lens can be rotated in a circumferential direction with respect to a visual line of an eye of a patient, has a deflection surface for deflecting at least one of treatment light, observation light and imaging light, and comes in contact with the eye of the patient. The ophthalmological contact lens includes rotation detection means for detecting a rotation position in a circumferential direction of the deflection surface, and output means for outputting a detection result.SELECTED DRAWING: Figure 1

Description

  The present disclosure relates to an ophthalmic contact lens used to perform treatment, observation, and / or imaging of a patient's eye.

  A corner mirror that is pressed against the cornea of a patient's eye to observe the corner of the patient's eye is known (for example, see Patent Document 1). The corner mirror of Patent Document 1 has a reflecting surface that reflects light from the corner of the eye to be examined that is incident on the contact surface so as to be substantially parallel to the optical axis of the eye to be examined. The user observes the light reflected by the reflecting surface.

  In addition, a treatment method is known in which a trabecular meshwork of a patient's eye is irradiated with laser light (see, for example, Patent Document 2). In the treatment method of Patent Document 2, a corner lens is brought into contact with a patient's eye. Then, the laser light is deflected by a mirror included in the corner lens, and the trabecular meshwork of the patient's eye is irradiated with the laser light.

JP 58-36525 A US Pat. No. 5,549,596

  For example, there is a case where treatment laser light is intermittently irradiated so as to trace a trabecular meshwork of a patient's eye while rotating a contact lens (corner mirror or the like) held by an operator. During such treatment, if the contact lens is gripped in an inappropriate state (for example, the contact lens is rotated too much), for example, a treatment laser beam that has been irradiated may be irradiated again. There is a possibility of irradiating a treatment laser beam to a site separated from a site to be irradiated or the like. There may also be a problem when observing or photographing a patient's eye while rotating the contact lens. That is, the conventional contact lens requires skill in handling.

  An object of the present disclosure is to provide a contact lens that can suitably execute at least one of treatment, observation, and imaging of a patient's eye.

In order to solve the above problems, the present invention is characterized by having the following configuration.
An ophthalmic contact lens that is rotatable in the circumferential direction with respect to the visual axis of a patient's eye, has a deflecting surface that deflects at least one of treatment light, observation light, and imaging light, and that contacts the patient's eye And a rotation detecting means for detecting the rotational position of the deflection surface in the circumferential direction, and an output means for outputting the detection result.

  According to the present disclosure, it is possible to provide a contact lens that can suitably execute at least one of treatment, observation, and imaging of a patient's eye.

It is an external appearance perspective view of the contact lens of this embodiment. It is AA sectional drawing of FIG. It is the figure which looked at the contact lens of FIG. 1 from the base end side. It is a figure explaining the structure of the contact lens of FIG. It is a figure explaining the displacement of a contact lens. It is an external view of the ophthalmic laser treatment system of this embodiment. It is explanatory drawing explaining the structure of the ophthalmic laser treatment system of FIG. It is a figure of the navigation screen displayed on a monitor. It is a figure of the navigation screen displayed on a monitor.

  Hereinafter, exemplary embodiments of the present disclosure will be described with reference to the drawings. FIG. 1 is an external perspective view of a contact lens 1 of the present embodiment. FIG. 2 is a cross-sectional view taken along the line AA of FIG. In FIG. 2, as an example of the usage state of the contact lens 1 of the present embodiment, the anterior eye part of the patient's eye Ep and the operator's finger holding the contact lens 1 are indicated by dotted lines. FIG. 3 is a view of the contact lens 1 of the present embodiment as viewed from the proximal end side. In the following description, the right side of FIG. 1 may be referred to as the base end side, and the left side of FIG. FIG. 4 is an explanatory view illustrating the configuration of the contact lens 1 of the present embodiment.

<Contact Lens>
The contact lens 1 of this embodiment is used for ophthalmic laser treatment. The contact lens 1 of the present embodiment includes a contact unit 10, an optical unit 20, a sensor unit 30, and a grip unit 40. In the following description, an axis passing through the center of the contact lens 1 (in other words, the optical unit 20) will be referred to as an axis L1. Note that the axis L <b> 1 of the present embodiment passes through the center of the contact portion 10 and the center of the second optical surface 22. In the present embodiment, it is assumed that when the operator contacts the contact lens 1 with the patient's eye Ep, the visual axis of the patient's eye Ep coincides with the axis L1. Of course, the axis L1 and the visual axis do not have to coincide exactly.

  The contact part 10 of this embodiment is contacted with the cornea of the patient's eye Ep at the time of use. The optical unit 20 of the present embodiment can emit (transmit) while refracting light (for example, visible light) incident on the optical unit 20. Further, the optical unit 20 of the present embodiment transmits observation light (for example, visible light) from the observation site of the patient's eye Ep. The sensor unit 30 of the present embodiment is a rotation detection unit that detects the rotational position of the optical unit 20 in the circumferential direction (in the present embodiment, the axis L1 is the center). Specifically, the sensor unit 30 of the present embodiment detects the rotational position of the contact lens 1 and outputs (sends) a detection result signal to the outside of the contact lens 1. The grasping portion 40 of this embodiment is grasped by an operator.

  The contact portion 10 of this embodiment is disposed at the tip portion of the contact lens 1. The optical unit 20 of the present embodiment includes a first optical surface 21, a second optical surface 22, a reflecting surface 23 (a polarizing surface, in other words, a deflecting unit), and a side surface 25 (see FIG. 2). The shape of the optical unit 20 of the present embodiment is a substantially partial cone shape that tapers toward the distal end side. Glass is used as the material of the optical unit 20 of the present embodiment. The first optical surface 21 of the present embodiment is provided on the tip side of the optical unit 20. The first optical surface 21 of the present embodiment has a curved shape that is depressed with a predetermined radius of curvature toward the base end side. The curvature radius of the first optical surface 21 is, for example, an average corneal curvature radius of a human by statistics or the like. Since the first optical surface 21 of the present embodiment is in contact with the patient's eye Ep, it is a part of the contact portion 10 described above.

  The second optical surface 22 is provided on the proximal end side of the optical unit 20. The first optical surface 21 of the present embodiment has a curved shape that rises toward the base end side with a predetermined radius of curvature. The side surface 25 of the present embodiment connects the edge of the first optical surface 21 and the edge of the second optical surface 22. Further, the contact lens 1 of the present embodiment is provided with a reflective surface 23 as a part of the side surface 25. The light (beam) incident on the reflecting surface 23 is deflected by the reflecting surface 23. The shape of the reflective surface 23 of this embodiment is a plane. When the optical unit 20 is viewed from the base end side of the axis L1, the reflecting surface 23 of the present embodiment is inclined toward the base end direction (see FIGS. 2 and 3). Moreover, the reflective surface 23 of this embodiment is arrange | positioned in the position spaced apart from the axis | shaft L1. A reflective coating (silver coat or the like) is formed on the reflective surface 23 of the present embodiment. The reflective surface 23 of the present embodiment can reflect visible light (for example, laser light having a wavelength of 532 nm, aiming light, observation light, and the like). In addition, the reflective surface 23 may be formed in the curved surface. Moreover, a drive part may be connected to the reflective surface 23, and a reflection direction may be changed. The configuration of the optical unit 20 is not limited to this embodiment. For example, you may comprise the 1st optical surface 21, the 2nd optical surface 22, and the reflective surface 23 with a respectively different member. For example, the optical unit 20 may be only the reflection surface 23 (deflection unit).

  The grip portion 40 of the present embodiment is provided on the proximal end side of the housing 2 that accommodates the optical portion 20 and the like. In addition, the housing | casing 2 of this embodiment is made into the substantially cylindrical shape which the front end side tapers, and the optical part 20 is accommodated in the column-shaped penetration part. The grip portion 40 of this embodiment is provided on the side surface of the housing 2. The grip part 40 of the present embodiment is provided around the optical part 20. As illustrated in FIG. 2, the light (indicated by reference numeral L <b> 2) incident on the optical unit 20 of the contact lens 1 is incident on the second optical surface 22 and then reflected (deflected) by the reflecting surface 23. The light reflected by the reflecting surface 23 is emitted from the first optical surface 21 to the outside of the optical unit 20. The light that has passed through the first optical surface 21 travels in the eye of the patient's eye Ep and strikes the treatment site or the like. That is, the reflecting surface 23 makes it easy to shine light on a peripheral portion (for example, a part away from the visual axis) in the eyeball of the patient's eye Ep. Of course, the reflection surface 23 makes it easy to observe the peripheral portion of the patient's eye Ep in the eyeball.

  For example, when the reflection surface 23 is viewed from the proximal end side of the axis L1 in a state where the contact portion 10 is in contact with the cornea of the patient's eye Ep, a partial region of the trabecular meshwork arranged in an annular shape becomes the reflection surface 23. Reflect. When the contact lens 1 is rotated about the axis L1 while the contact portion 10 is in contact with the cornea, the region of the trabecular meshwork reflected on the reflecting surface 23 changes. Thus, by rotating the contact lens 1, the trabecular meshwork arranged in an annular shape can be observed evenly. Since the reflecting surface 23 of the present embodiment can also reflect the treatment laser light (and aiming light), the treatment laser beam (a partial region of the trabecular meshwork) being observed can be irradiated with the treatment laser light. As an example, the surgeon can observe the treatment site using the contact lens 1 and can irradiate the treatment site with the treatment laser beam using the contact lens 1.

  The sensor unit 30 of this embodiment will be described with reference to FIG. The sensor unit 30 of the present embodiment is housed inside the housing 2. The sensor unit 30 of the present embodiment is disposed at a position separated from the axis L1. Specifically, the sensor 31 of the present embodiment is disposed at a position farther from the axis L1 than the optical unit 20. The sensor unit 30 of the present embodiment includes a sensor 31, a buzzer 32, an LED 33 (LED 33 </ b> A, LED 33 </ b> B), an arithmetic unit unit 34, a wireless transmission / reception unit 35, and a battery 36. The arithmetic unit 34 of the present embodiment includes a CPU 41, a ROM 42, a RAM 43, a nonvolatile memory 44, and the like. The CPU 41 controls each part in the contact lens 1. The ROM 42 stores various programs, initial values, and the like. The RAM 43 can temporarily store various information. The nonvolatile memory 44 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, the non-volatile memory 44 stores reference information for using the sensor 31 in advance.

  A sensor 31, a buzzer 32, an LED 33, a wireless transmission / reception unit 35, and a battery 36 are connected to the calculation unit unit 34 of the present embodiment. As an example, a 9-axis motion tracking device is used for the sensor 31 of the present embodiment. Moreover, the sensor 31 of this embodiment is a MEMS device (MEMS: Micro Electro Mechanical Systems). Therefore, it is small. The sensor 31 of this embodiment includes an angular velocity sensor (gyro sensor), an acceleration sensor (G sensor), and a geomagnetic sensor (electronic compass). For example, as a vibrating gyro sensor (angular velocity sensor) using MEMS technology, a capacitance method, a piezoelectric method, or the like may be used. Further, as the acceleration sensor, for example, a capacitance detection method, a piezoresistance method, a thermal resistance method, or the like may be used. Moreover, as a magnetic sensor (geomagnetic sensor), for example, a Hall element, an MR element (magnetoresistance element), an MI element (magnetic impedance element), or the like may be used. Note that the sensor 31 does not necessarily include all of the angular velocity sensor, the acceleration sensor, and the geomagnetic sensor. For example, only the acceleration sensor may be included as the sensor 31.

The buzzer 32 of this embodiment generates (notifies) sound. LED33 of this embodiment lights light (visible light). In the present embodiment, the LED 33 includes a pair of LEDs (LED 33A, LED 33B) (see FIG. 3). The LED 33 of the present embodiment illuminates the side surface 25. For example, when the LED 33 is turned on, the rotation direction of the contact lens 1 can be guided (described in detail later). The wireless transmission / reception unit 35 of this embodiment can transmit and receive data wirelessly. In addition, the form which can only transmit (output) data may be sufficient. The battery 36 (power supply means) of this embodiment stores electricity. In the present embodiment, the electronic components of the sensor unit 30 operate using the electricity stored in the battery 36. Note that the battery 36 may not be mounted. For example, radio waves, light, magnetic fields, etc. received by the contact lens 1 may be used to supply power to the electronic components of the sensor unit 30 wirelessly. Of course, power may be supplied to the contact lens 1 by wire.
<Operation of contact lens>

  When the power is turned on, the contact lens 1 of the present embodiment outputs information related to the displacement of the contact lens 1 (spatial position, inclination angle (rotation position), etc.) as a radio signal. The contact lens 1 may be provided with a start button, and the state where the start button is pressed may be used as a reference position for detecting the displacement of the contact lens 1. For example, after the start button is pressed, when the contact lens 1 is displaced (rotated) by a predetermined amount, the buzzer 32 may be sounded to notify the operator. Further, when the contact lens 1 is displaced by a predetermined amount, the LED 33 may be turned on to notify the operator. Of course, the buzzer 32 may be sounded or the LED 33 may be turned on based on the information received by the wireless transmission / reception unit 35. In other words, the buzzer 32 or the LED 33 may be used as output means directed to the outside of the contact lens 1.

  The contact lens 1 of the present embodiment can detect the first displacement of the contact lens 1 (reflecting surface 23) due to the rotation about the axis L1 (see the symbol R in FIG. 3 as an example). In addition, the contact lens 1 of the present embodiment can detect the second displacement of the contact lens 1 caused by rotation in the left-right direction about the up-down direction (Y-axis) (see the symbol Y in FIG. 5A as an example). . In addition, the contact lens 1 according to the present embodiment can detect the third displacement of the contact lens 1 caused by the vertical rotation about the left-right direction (X-axis) (see the symbol Y in FIG. 5B as an example). . The detected result can be output to the outside of the contact lens 1. For example, the contact lens 1 may detect only the first displacement. Further, the parallel movement of the contact lens 1 (for example, movement while maintaining the direction in which the axis L1 is directed on the XY plane) may be detected.

<Ophthalmic laser treatment device>
Next, an example of a method for using the contact lens 1 of the present embodiment will be described with reference to FIGS. Here, as an example, a method of using an ophthalmic laser treatment system (a type of ophthalmic system) in which the contact lens 1 and an ophthalmic laser treatment device (a type of ophthalmic device) 100 are combined will be described.

  The ophthalmic laser treatment apparatus 100 according to this embodiment includes a slit delivery unit 102 and a table unit 112. The slit delivery unit 102 of the present embodiment can irradiate the patient's eye Ep with a treatment laser beam. The table part 112 of this embodiment mounts the slit delivery part 102. The slit delivery unit 102 according to this embodiment includes a main body unit 103, an illumination unit 104, an eyepiece unit 106, a displacement unit 107, an operation panel unit 108, a joystick unit 109, and a headrest unit 111. The main body 103 accommodates an irradiation optical system 110, which will be described later. A monitor 122 is fixed to the table unit 112.

  The illumination unit 104 of the present embodiment is used to illuminate the observation site of the patient's eye Ep. The operator can observe the observation site by looking through the eyepiece 106. The displacing means 107 of the present embodiment includes an optical system (for example, the irradiation optical system 110) included in the ophthalmic laser treatment apparatus 100 in the vertical direction (Y-axis direction in FIG. 6), the horizontal direction (X-axis direction in FIG. 6), Alternatively, it can be displaced (moved) in the front-rear direction (Y-axis direction in FIG. 6). Further, the displacing means 107 of the present embodiment can rotate the main body 103 in the horizontal direction (left and right in FIG. 6) with the axis extending in the vertical direction (see the axis L3 in FIG. 6) as the rotation center. That is, the displacement means 107 of the present embodiment includes the pan mechanism of the main body portion 103.

  Note that the sensor unit 161 (see FIG. 7) is connected to the displacement means 107. The sensor unit 161 is used to detect the displacement state of the main body unit 103. In addition, the aspect of the displacement means 107 is not restricted to this. It is only necessary that the main body 103 (the irradiation optical system 110 or the like) can be displaced with respect to the patient's eye Ep. For example, the displacement unit 107 may include a tilt mechanism (vertical rotation) of the main body 103.

  The operation panel unit 108 of the present embodiment is used by an operator to set various operating conditions of the ophthalmic laser treatment apparatus 100. The joystick unit 109 is used by the operator to align various optical systems with respect to the patient's eye Ep. In addition, the trigger switch for starting irradiation of a treatment laser beam is provided in the front-end | tip of the joystick part 109 of this embodiment. The headrest part 111 is used for fixing the patient's face.

  The ophthalmic laser treatment apparatus 100 of this embodiment includes an irradiation optical system 110, a guide optical system 120, an observation optical system 130, an illumination optical system, and a control unit 140 (see FIG. 7). The irradiation optical system 110 is used for irradiating a treatment laser beam to a treatment site. The irradiation optical system 110 of this embodiment includes a treatment laser light source 131, a dichroic mirror 132, a lens group 133, a dichroic mirror 134, and an objective lens 135. Note that the dichroic mirror 132 of the present embodiment has a characteristic of transmitting the treatment laser light and reflecting the aiming light. Further, the dichroic mirror 134 of the present embodiment has a characteristic of reflecting the treatment laser light and the aiming light and transmitting the observation light.

  The treatment laser light source 131 of the present embodiment emits treatment laser light. As an example, the treatment laser light source 131 of this embodiment includes a Q switch, and can emit pulsed laser light having a wavelength of 532 nm. The treatment laser light emitted from the treatment laser light source 131 forms a spot on the treatment site of the patient's eye Ep via the dichroic mirror 132, the lens group 133, the dichroic mirror 134, the objective lens 135, and the contact lens 1.

  The guide optical system 120 of the present embodiment is used for guiding treatment laser light. The guide optical system 120 of this embodiment shares the optical members from the dichroic mirror 132 to the objective lens 135 with the irradiation optical system 110. The guide optical system 120 of this embodiment includes a guide light source 136. The guide light source 136 of the present embodiment emits light having a wavelength of 635 nm (continuous light). The guide light emitted from the guide light source 136 is reflected by the dichroic mirror 134 and then travels in the same optical path as the treatment laser light to be condensed on the treatment site (in other words, a guide light spot is formed at the treatment site). ) In the present embodiment, the spot size of the treatment laser beam formed at the treatment site and the spot size of the guide beam are substantially the same. Therefore, the surgeon can easily grasp the irradiation region of the treatment laser light by observing the spot of the guide light.

  The observation optical system 130 of this embodiment provides an operator with an observation image of a treatment site. The observation optical system 130 of this embodiment shares the objective lens 135 and the dichroic mirror 134 with the irradiation optical system 110 (guide optical system 120). The observation optical system 130 of this embodiment includes a lens group 137 and an eyepiece lens 138. The light emitted from the treatment site is collected on the fundus of the operator's eye Eo via the objective lens 135, the dichroic mirror 134, the lens group 137, and the eyepiece lens 138. For example, the surgeon can simultaneously observe an observation image of a treatment site and the like and guide light superimposed on the observation image. By using the displacement means 107 together, it is possible to aim the treatment laser beam at the treatment site. When the trigger switch of the joystick unit 109 is pressed, a spot of the treatment laser light emitted from the treatment laser light source 131 is formed at the treatment site. Note that the treatment laser light emitted by the ophthalmic laser treatment apparatus 100 of the present embodiment has a low energy density at the spot position. Therefore, it is difficult to confirm (observe) the irradiation trace with the naked eye of the operator.

  The control unit 140 of the present embodiment includes a CPU 141, a ROM 142, a RAM 143, a nonvolatile memory 144, and the like. The CPU 141 controls each unit in the ophthalmic laser treatment apparatus 100. The ROM 142 stores various programs, initial values, and the like. The RAM 143 temporarily stores various information. The nonvolatile memory 144 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted.

  A treatment laser light source 131, a guide light source 136, a sensor unit 161, a wireless transmission / reception unit 162, an operation panel unit 108, and a monitor 122 are connected to the control unit 140 of this embodiment. The wireless transmission / reception unit 162 according to the present embodiment can receive a signal output from the contact lens 1 and can transmit a signal to the contact lens 1. The monitor 122 of the present embodiment can display a navigation screen (see FIGS. 8 and 9) described later. In the present embodiment, the control unit 140 controls the display content of the monitor 122. Note that a buzzer (sounding means) is connected to the control unit 140, and the displacement state of the contact lens 1 may be notified by sound. Although details will be described later, the ophthalmic laser treatment apparatus 100 may notify the displacement state of the contact lens 1.

<Cooperation between contact lens and ophthalmic laser treatment device>
An example of cooperation between the contact lens 1 and the ophthalmic laser treatment apparatus 100 will be described with reference to FIGS. Hereinafter, the case where the contact lens 1 and the ophthalmic laser treatment apparatus 100 are linked in the selective laser trabeculoplasty (SLT) will be described.

  The operator holds the contact lens 1 and brings the contact portion 10 of the contact lens 1 into contact with the cornea of the patient's eye Ep. Next, the operator operates the operation panel unit 108 to select the SLT mode as the operation mode of the ophthalmic laser treatment apparatus 100. A navigation screen (see FIG. 8) is displayed on the monitor 122. The surgeon operates the operation panel unit 108 and designates a treatment laser light irradiation scheduled region (partial region or entire region of the trabecular meshwork). In FIG. 8, a clockwise (clockwise) half-circumferential region (from S1 to S60) starting from the upper end is designated as the irradiation scheduled region.

  The surgeon fixes the patient's face to the headrest 111. Next, the operator operates the joystick part 109 or the contact lens 1 while looking into the eyepiece part 106, and matches the guide light to the treatment planned site. At this time, the surgeon focuses the guide light on the region (part) of the trabecular meshwork corresponding to the start point of the navigation screen displayed on the monitor 122 (reference numeral S1 in FIG. 8). In the present embodiment, the operator holds the contact lens 1 with the reflecting surface 23 disposed below (see also FIGS. 2 and 3).

  Next, the surgeon presses the trigger switch of the joystick unit 109 to irradiate the treatment site with treatment laser light (pulse light). A spot of treatment laser light is formed at the aiming position of the guide light. When treatment laser light is irradiated, the location of the reference sign S1 on the navigation screen changes (for example, in the present embodiment, the white circle changes to a black circle). The surgeon rotates the contact lens 1 so that it does not overlap the previous aiming position and moves the irradiation position of the aiming light to the next appropriate position adjacent to the rotation direction (examples of FIGS. 8 and 9). Then move it clockwise). Then, the trigger switch of the joystick unit 109 is pressed again. Then, the part of the code S2 changes from a white circle to a black circle. Note that the treatment laser beam irradiated in the SLT mode has a low energy density at the spot position. Therefore, no irradiation trace remains at the treatment site (trabecular band). Therefore, it is difficult for the surgeon to grasp the irradiated region of the treatment laser light even when observing the patient's eye Ep.

  FIG. 9 shows the state of the navigation screen after 20 treatment laser beams are irradiated while shifting the irradiation position of the treatment laser beam in the circumferential direction of the trabecular meshwork. In the present embodiment, the operator can rotate the contact lens 1 while confirming the planned irradiation position (direction) of the treatment laser beam by the navigation screen displayed on the monitor 122. As described above, irradiation with the treatment laser light is repeated until the portion indicated by reference numeral S60 becomes a black circle. When irradiation at the position (direction) indicated by reference sign S60 is completed, selective laser trabeculoplasty using the SLT mode is completed.

  Here, a case will be described in which the operator rotates the contact lens 1 too much in the above-described SLT mode. The contact lens 1 of the present embodiment sequentially outputs (sends) a signal corresponding to the rotational position to the outside of the contact lens 1. The ophthalmic laser treatment apparatus 100 according to the present embodiment receives a signal output from the contact lens 1 and detects a rotational position of the contact lens 1 and the like. When the difference between the treatment site to be irradiated (for example, symbol S21 in FIG. 9) and the rotational position of the contact lens 1 is larger than a predetermined threshold, the ophthalmic laser treatment apparatus 100 sounds a buzzer to notify the operator. To do. The surgeon rotates the contact lens 1 in a suitable direction. In this way, it is possible to suppress irradiation of the treatment laser beam to an unintended site. In addition, the treatment site of the patient's eye Ep can be quickly treated.

  Note that the ophthalmic laser treatment apparatus 100 according to the present embodiment sends a guidance signal for guiding the rotational position of the contact lens 1 toward the contact lens 1. When the contact lens 1 receives the guidance signal, the contact lens 1 turns on the LED 33 (see FIG. 3 for the arrangement of the LED 33). The contact lens 1 of the present embodiment turns on either the LED 33A or the LED 33B according to the guidance signal. The LED 33A (or LED 33B) that is turned on illuminates the region of the side surface 25 that is on the opposite side via the axis L1. In the present embodiment, the arrow for guiding the rotation direction is formed in an uneven shape in a partial region of the side surface 25 illuminated by the LED 33. The surgeon observes the arrow illuminated by the LED 33 reflected in the observation image, and rotates the contact lens 1 in the corresponding direction.

  Note that the method of guiding the rotation of the contact lens 1 is not limited to this. For example, guidance information regarding rotation of the contact lens 1 based on a signal output from the contact lens 1 may be displayed on the monitor 122. Further, the rotation guidance may be performed by the contact lens 1 alone. For example, the contact lens 1 includes a rotation condition receiving unit. Then, the arithmetic unit 34 may perform lighting control of the LED 33 that guides the rotation direction based on the received rotation condition and the detection signal of the sensor 31. When performing such rotation guidance control, information regarding the detection signal of the sensor unit 161 output from the ophthalmic laser treatment apparatus 100 may be used. The contact lens 1 can also guide the direction of rotation using an LED or the like even when an illuminated arrow is not formed.

<Action and effect>
The contact lens 1 of the present embodiment is rotatable in the circumferential direction with respect to the visual axis of the patient's eye Ep, and has a reflection surface 23 (deflection surface) that deflects at least one of treatment light, observation light, and imaging light. It is an ophthalmic contact lens 1 having contact with a patient's eye. The contact lens 1 includes a rotation detection means (30) for detecting the rotational position of the reflection surface 23 (deflection surface) in the circumferential direction, and an output means (35) for outputting the detection result. Thereby, for example, irradiation of the treatment laser beam to an unintended site can be suppressed. Moreover, the contact lens 1 of this embodiment is provided with the wireless transmission part which transmits the information regarding a detection result wirelessly. Thereby, for example, the communication cable or the like is not entangled with the hand holding the contact lens 1, and the handling of the contact lens 1 becomes easy. Moreover, the contact lens 1 of this embodiment is provided with the holding part 40 which an operator holds. Thereby, for example, the contact lens 1 can be easily rotated while being held. Further, the contact lens 1 of the present embodiment includes at least one of an angular velocity sensor, an acceleration sensor, and a geomagnetic sensor as a rotation detection unit. Thereby, for example, the rotation of the contact lens 1 can be detected with a compact or simple configuration using a MEMS device or the like.

<Others>
In the contact lens 1 of the present embodiment, the optical unit 20 and the sensor unit 30 are integrated. However, the form of the contact lens is not limited to this. For example, the contact lens and the sensor unit may be separate. A commercially available contact lens and the sensor unit 30 may be combined. The sensor unit may be an accessory that can be attached to and detached from the contact lens.

  In the present embodiment, the rotational position or the like (displacement) of the contact lens is detected using a 9-axis motion tracking device. However, the contact lens rotation detection method is not limited to this. Note that, for example, the three-dimensional position of the contact lens may be detected using ultrasonic waves (see JP 2012-167971 A).

  In the ophthalmic laser treatment system of the present embodiment, the contact lens 1 and the ophthalmic laser treatment apparatus 100 are combined. The contact lens 1 is used to treat the trabecular meshwork of the patient's eye Ep with a treatment laser beam. Of course, the apparatus which emits a treatment laser beam, or the treatment site | part of the patient eye Ep is not restricted to this. For example, a combination of a contact lens and a laser photocoagulator may be used. For example, a treatment laser beam incident on the contact lens may be scanned. Treatment of the retina may be performed using the contact lens 1. The contact lens 1 may be used only for imaging an observation site. For example, the contact lens 1 of the present embodiment may be used for panoramic imaging in which a plurality of parts of the patient's eye Ep are imaged while the contact lens 1 is displaced. Moreover, you may measure the several site | part of the patient's eye Ep using the contact lens 1 of this embodiment. That is, the contact lens 1 of the present embodiment may be used for ophthalmic imaging, ophthalmic examination, ophthalmic diagnosis, and the like.

  In the contact lens 1 of the present embodiment, a reflective surface 23 is formed on a part of the side surface of the optical unit 20. However, the reflecting surface 23 may be the entire side surface of the optical unit 20. Further, the optical unit 20 may not include the reflecting surface 23. The treatment laser beam incident on the contact lens may be refracted and emitted. In other words, the traveling direction of the treatment laser light (beam) may be changed by the contact lens. Of course, it goes without saying that the technique of the present disclosure can be applied to other than laser light (for example, SLD light, LED light).

  The ophthalmic laser treatment apparatus 100 according to the present embodiment receives a signal output from the contact lens 1 and detects a rotational position of the contact lens 1 and the like. However, the ophthalmologic apparatus that performs at least one of observation, treatment, and imaging of the patient's eye Ep may detect the rotational position of the contact lens by another method. For example, the ophthalmologic apparatus may include a camera that captures contact lenses. In this case, the control unit of the ophthalmologic apparatus may detect the rotational position of the contact lens by processing an image of the contact lens photographed by the camera. For example, the control unit detects the rotational position of the contact lens by detecting the position of the characteristic part included in the contact lens (for example, the position of the mark provided on the contact lens or the position of the LED) by image processing. May be. The ophthalmic apparatus includes a light projecting unit that projects light for rotation detection toward the contact lens, and a light receiving unit that receives the reflected light that is projected by the light projecting unit and reflected by the contact lens. Also good. In this case, the control unit of the ophthalmologic apparatus may detect the rotational position of the contact lens based on the light reception result of the reflected light by the light receiving unit. The ophthalmologic apparatus may include a magnetic sensor that detects the rotational position of the contact lens.

  Based on the above, the ophthalmologic apparatus according to the present disclosure can also be expressed as follows. An optical member (for example, a contact lens) that includes a polarization plane that deflects at least one of treatment light, observation light, and imaging light and that can change the rotational position of the polarization plane in the circumferential direction with respect to the visual axis of the patient's eye is used. An ophthalmologic apparatus that performs at least one of treatment, observation, and imaging of a specific part of the patient's eye, and acquires a rotation position of the polarization plane or the optical member in the circumferential direction with respect to the visual axis of the patient's eye And a specifying means for specifying a region where at least one of treatment, observation, and imaging is performed based on the rotation position acquired by the rotation position acquisition means. Ophthalmic equipment.

  The rotation position acquisition unit may acquire the rotation position by inputting the rotation position detected by the rotation detection unit included in the optical member from the optical member. The rotational position acquisition unit may acquire the rotational position by processing an image captured by a camera that captures the optical member. The rotational position acquisition unit may acquire the rotational position based on a light reception result of the light for detecting rotation reflected by the optical member. The rotational position acquisition unit may acquire the rotational position of the optical member detected by a magnetic sensor provided in the ophthalmic apparatus.

  In addition, the ophthalmologic apparatus may include notification means for notifying an operator of the part specified by the specifying means. The notification means may notify the surgeon of the part by voice (pronunciation) or may notify the surgeon by displaying the part on a monitor. The optical member may be a contact lens including an optical part having a predetermined refractive index, or may not include an optical part.

  It should be thought that embodiment disclosed this time is an illustration and restrictive at no points. The scope of the present invention is defined by the terms of the claims, rather than the description above, and is intended to include any modifications within the scope and meaning equivalent to the terms of the claims.

1: contact lens 2: housing 10: contact unit 20: optical unit 30: sensor unit 40: gripping unit 100: ophthalmic laser treatment apparatus A: shaft

Claims (4)

An ophthalmic contact lens that is rotatable in the circumferential direction with respect to the visual axis of a patient's eye, has a deflecting surface that deflects at least one of treatment light, observation light, and imaging light, and that contacts the patient's eye There,
Rotation detecting means for detecting a rotational position of the deflection surface in the circumferential direction;
An output means for outputting the detection result;
An ophthalmic contact lens comprising: The ophthalmic contact lens according to claim 1,
A wireless transmission unit for wirelessly transmitting information on the detection result;
An ophthalmic contact lens characterized by that. The ophthalmic contact lens according to claim 1 or 2,
Provided with a grasping portion that the operator grasps,
An ophthalmic contact lens characterized by that. The ophthalmic contact lens according to any one of claims 1 to 3,
The rotation detection means includes at least one of an angular velocity sensor, an acceleration sensor, and a geomagnetic sensor,
An ophthalmic contact lens characterized by that.

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