JP2008125939A - Optical probe and optical treatment diagnostic system with it - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To make a measurement result with a light projection least affected by the other light projection when two beams of light are projected from an optic probe at the same time. <P>SOLUTION: A light guiding member 12 to guide a first light L1 and a second light Lt is provided on a probe outer tube 11 in an axial direction thereof. A first illumination part 14 illuminates a subject S on an outside of the probe outer tube 11 with the first light L1 while scanning thereon. A second illumination part 16 illuminates the subject S on the outside of probe outer tube 11 with the second light Lt so that the second light Lt could be on an optical track Ltrk of the first light formed on the subject S when the first illumination part 14 illuminates the subject S with scanning thereon. When the first light L1 and the second light Lt are simultaneously emitted from the light guiding member 12, the first illumination part 14 and the second illumination part 16 respectively illuminate different parts Pm, Pt on the subject S with each of the first light L1 and the second light Lt. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an optical probe having a cylindrical probe outer cylinder and a function of emitting light from its peripheral surface, and an optical therapy diagnostic system.

  Conventionally, as a biological treatment method using light, for example, a biological treatment method using the heat generated by irradiation of a laser beam such as cancer thermotherapy, collagen fiber bonding, protein coagulation / denaturation, hemostasis, tissue removal, incision, etc. A biological treatment method using a chemical reaction via a photosensitive substance such as mechanical treatment is known. When performing the laser treatment, the type of laser and an irradiation method such as irradiation to a wide range or local irradiation are appropriately selected according to the purpose of treatment. When irradiating a biological substance or the like in a body cavity with laser treatment, an optical probe is inserted into the body cavity and a treatment laser is irradiated from the optical probe to an irradiation target.

  Here, when irradiating the treatment laser in the body cavity as described above, an image of the irradiation site by an endoscope apparatus or an OCT (optical tomography measurement) apparatus or the like is provided prior to the irradiation of the treatment laser in order to accurately specify the irradiation site. Is acquired. For example, in Patent Document 1, an optical fiber for guiding a treatment laser and an optical fiber for guiding a diagnostic laser are accommodated in an optical probe, and the treatment lasers are respectively guided in two optical fibers. A method of acquiring a tomographic image and irradiating a treatment laser by irradiating the same part of the irradiation target with a diagnostic laser is disclosed (see Patent Document 1 and FIG. 7).

In Patent Document 2, the treatment laser emitted from the treatment laser device to the probe and the diagnostic laser emitted from the confocal laser light source to the probe are switched by a switch. A method of injecting from a probe to an irradiation object at different timings is disclosed (see Patent Document 2).
JP 2001-264246 A JP 2004-733337 A

  By the way, even during the laser treatment described above, it is desired to acquire an image of a site where the laser treatment is performed and check the progress of the treatment. However, in Patent Document 2, since only one of the treatment laser and the diagnostic laser can be irradiated from the optical probe, an image cannot be acquired during the treatment with the treatment laser, and the treatment is performed during the treatment. There is a problem that the state of the part cannot be confirmed in real time.

  On the other hand, in patent document 1, the treatment laser and the diagnostic laser are irradiated to the same site. For this reason, when the image is acquired by detecting the reflected light from the irradiation target when the diagnostic laser is irradiated, the reflected light from the treatment laser is also detected, and the image quality of the acquired image is deteriorated. There is a problem of end.

  Further, not limited to the case of the diagnostic laser and the treatment laser as described above, the two lights can irradiate the same part to be irradiated, and the measurement result obtained by the emission of one of the lights reflects the other light. The thing which can suppress the influence of this to the minimum is desired.

  Therefore, the present invention provides an optical probe capable of minimizing the influence of the other light on the measurement result of the emission of one light when the two lights are simultaneously emitted from the optical probe, and an optical treatment using the same. The object is to provide a diagnostic system.

  The optical probe of the present invention includes a cylindrical probe outer cylinder, and an optical waveguide that guides the first light and the second light disposed in the inner space of the probe outer cylinder in the axial direction of the probe outer cylinder. A first irradiating unit that irradiates the first light emitted from the tip of the optical waveguide member while scanning the irradiation target disposed on the outside of the probe outer cylinder; and a first irradiant emitted from the tip of the optical waveguide member. 2 is irradiated on the irradiation target arranged on the outer side of the probe outer cylinder and on the locus of the first light formed on the irradiation target when irradiated with scanning by the first irradiation unit. A second irradiating portion that enables the first irradiating portion and the second irradiating portion to be different on the irradiation target when the first light and the second light are simultaneously emitted from the optical waveguide member. Further, the first light and the second light are respectively irradiated.

  The phototherapy diagnosis system of the present invention includes an image acquisition device that acquires an image of an irradiation target using reflected light from the irradiation target when the irradiation target is irradiated with measurement light, and a treatment laser for irradiating the irradiation target A laser treatment device that emits light, a treatment laser emitted from the laser treatment device, and an optical probe that guides the measurement light emitted from the image acquisition device to the irradiation target, and the optical probe is a cylindrical probe An outer cylinder, an optical waveguide member that guides the measurement light and the treatment laser, disposed in the axial direction of the probe outer cylinder in the inner space of the probe outer cylinder, and the measurement light emitted from the tip of the optical waveguide member The first irradiation unit that irradiates while scanning on the irradiation target arranged outside the outer cylinder, and the treatment laser emitted from the tip of the optical waveguide member are arranged on the irradiation target arranged outside the probe outer cylinder. Run by the first irradiation unit A second irradiating section that enables irradiation on the trajectory of the measurement light formed on the irradiation target when irradiated, and when the measurement light and the treatment laser are simultaneously emitted from the optical waveguide member, The first irradiating unit and the second irradiating unit irradiate the measurement light and the treatment laser to different portions on the irradiation target, respectively.

  Here, as long as the optical waveguide member can guide the first light and the second light, the optical waveguide member is composed of one optical fiber that guides both the first light and the second light. The first optical fiber that guides the first light and the second optical fiber that guides the second light may be used.

  When the optical waveguide member is made of one optical fiber, the first light irradiation unit transmits the second light out of the first light and the second light emitted from the optical waveguide member and transmits the second light. The light of 1 may be irradiated while scanning on the irradiation target arranged outside the probe outer cylinder. The second irradiating unit may be configured to irradiate the irradiation target disposed outside the probe outer cylinder with the second light transmitted through the first light irradiating unit.

  Alternatively, the second irradiating unit transmits the first light out of the first light and the second light emitted from the optical waveguide member, and the second light is disposed outside the probe outer tube. You may irradiate while scanning on a target. And a 1st irradiation part may irradiate the irradiation object distribute | arranged to the outer side of the probe outer cylinder with the 2nd light which permeate | transmitted the 2nd irradiation part.

  At this time, the first light and the second light are made of light in different wavelength ranges, and the first irradiation unit transmits the second light and reflects the first light due to the difference in wavelength range, or the first light The two irradiating units may transmit the first light and reflect the second light. Alternatively, the first light and the second light are light having a polarization direction perpendicular to each other, and the optical waveguide member is formed of a polarization-maintaining optical fiber, and the first irradiation unit is caused by the difference in the polarization direction. The second light may be transmitted and the first light reflected, or the second irradiator may transmit the first light and reflect the second light.

  The first irradiating unit may scan the first light along the circumferential direction of the probe outer cylinder as long as it irradiates while scanning the first light. You may scan along the longitudinal direction of a pipe | tube. Furthermore, the first light may be scanned in the longitudinal direction of the probe outer cylinder while scanning along the circumferential direction.

  Here, when the first light scans along the circumferential direction of the probe outer cylinder, the second irradiation unit irradiates the second light on the locus of the first light formed in the circumferential direction. It is supposed to be possible. Specifically, the first irradiation unit and the second irradiation unit are disposed so as to be rotatable in the circumferential direction of the probe outer cylinder, and the first irradiation unit and the second irradiation unit are optical waveguides. When the first light and the second light are emitted from the member at the same time, the first light and the second light are respectively irradiated at positions approximately 180 ° apart from the circumferential direction of the probe outer cylinder. It is preferable that

  In addition, when the first light scans along the longitudinal direction of the probe outer cylinder, the first irradiation unit and the second irradiation unit are configured so that the first light and the second light are transmitted from the optical waveguide member. When the light is emitted at the same time, the first light and the second light may be irradiated to positions in the same direction and separated by a predetermined distance. Alternatively, the first irradiating unit has a first reflecting surface that reflects the first light that can swing with respect to the optical axis of the optical waveguide member, and the first irradiating unit swings the first reflecting surface to cause the first light. You may irradiate light scanning on the irradiation object distribute | arranged to the outer side of the probe outer cylinder. At this time, the second irradiating portion has a second reflecting surface that reflects the second light that can be swung with respect to the optical axis of the optical waveguide member, and the second reflecting surface is swung to make the second reflection. The arbitrary light on the locus of the first light may be irradiated.

  In the phototherapy diagnosis system, the irradiation position acquisition means for acquiring position information for irradiating the treatment laser in the image acquired by the image acquisition device, and the irradiation position acquired by the irradiation position acquisition means by the second irradiation section. It may further include a system control unit that controls the laser treatment apparatus so that the treatment laser is emitted when the treatment laser can be irradiated.

  According to the optical probe of the present invention, the first probe and the second beam disposed in the axial direction of the probe outer cylinder in the inner space of the cylindrical probe outer cylinder and the probe outer cylinder are guided. An optical waveguide member, a first irradiating unit that irradiates the first light emitted from the tip of the optical waveguide member on an irradiation target disposed outside the probe outer tube, and the light emitted from the tip of the optical waveguide member On the locus of the first light formed on the irradiation target when the second light is irradiated on the irradiation target arranged outside the probe outer cylinder while being scanned by the first irradiation unit A second irradiating portion that enables irradiation, and when the first light and the second light are simultaneously emitted from the optical waveguide member, the first irradiating portion and the second irradiating portion are on the irradiation target. By irradiating different portions with the first light and the second light, respectively, the same part of the irradiation target is irradiated with the first light and the second light. In addition, when the first light and the second light are irradiated at the same time, different portions are irradiated, so that the second measurement result obtained by the irradiation with the first light The influence of the reflected light from the irradiation target when the irradiation target is irradiated with light can be minimized.

  If the optical waveguide member is made of one optical fiber that guides the first light and the second light, the diameter of the optical probe can be reduced.

  The first irradiating unit transmits the second light out of the first light and the second light emitted from the optical waveguide member, and the first light is disposed outside the probe outer tube. Irradiating while scanning on the irradiation target, the second irradiation unit enables the second light transmitted through the first irradiation unit to be irradiated on the irradiation target arranged outside the probe outer tube Or the second irradiating part transmits the first light out of the probe outer cylinder and transmits the second light out of the first light and the second light emitted from the optical waveguide member. The irradiation target is irradiated while scanning, and the first irradiation unit can irradiate the irradiation target arranged outside the probe outer tube with the second light transmitted through the second irradiation unit. Even when the first light and the second light are simultaneously guided through one optical fiber, the first light and the second light are used. Reliably demultiplexed, it can be irradiated to different sites irradiation target.

  Further, if the optical waveguide member has a first optical fiber that guides the first light and a second optical fiber that guides the second light, each optical fiber, the first irradiation unit, the first optical fiber, An optical member optimized for each light can be used for the two irradiation sections.

  The first irradiation unit and the second irradiation unit are disposed so as to be rotatable in the circumferential direction of the probe outer cylinder, and in particular, the first irradiation unit and the second irradiation unit are optical waveguide members. When the first light and the second light are emitted at the same time, the first light and the second light are respectively irradiated at positions approximately 180 ° away from the circumferential direction of the probe outer cylinder. In some cases, the influence of the second light on the measurement result obtained by the irradiation of the first light can be reliably reduced.

  Furthermore, the first irradiation unit and the second irradiation unit are arranged so as to be movable in the longitudinal direction of the probe outer cylinder. In particular, the first irradiation unit and the second irradiation unit are separated from the optical waveguide member by the first irradiation unit. When the first light and the second light are emitted at the same time, the first light and the second light are irradiated in the same direction at a predetermined distance, The influence which the 2nd light exerts on the measurement result acquired by irradiation of the 1st light can be reduced reliably.

  According to the phototherapy diagnostic system of the present invention, an image acquisition device for acquiring an image of an irradiation target using reflected light from the irradiation target when the irradiation target is irradiated with measurement light, and an irradiation target for irradiation A laser treatment device that emits a treatment laser, a treatment laser emitted from the laser treatment device, and an optical probe that guides measurement light emitted from the image acquisition device to an irradiation target, and the optical probe is cylindrical A probe outer cylinder, an optical waveguide member that guides the first light and the second light in the axial direction of the probe outer cylinder in the inner space of the probe outer cylinder, and a tip of the optical waveguide member A first irradiating unit that irradiates the emitted first light while scanning an irradiation target arranged on the outside of the probe outer cylinder, and second light emitted from the tip of the optical waveguide member. On the irradiation object arranged in the direction of the first irradiation unit A second irradiating section that enables irradiation on the locus of the first light formed on the irradiation target when irradiated while scanning, and the measurement light and the treatment laser are simultaneously emitted from the optical waveguide member When the first irradiation unit and the second irradiation unit irradiate the measurement light and the treatment laser to different portions on the irradiation target, respectively, the measurement light and the treatment laser are irradiated to the same portion of the irradiation target. In addition, when the measurement light and the treatment laser are irradiated at the same time, different portions are irradiated, so that the measurement result obtained by irradiation of the measurement light is applied to the irradiation target of the treatment laser. The influence of the reflected light from the irradiation target can be minimized.

  In addition, the irradiation position acquisition means which acquires the position information which irradiates a treatment laser in the image acquired by the image acquisition apparatus, and the 2nd irradiation part can irradiate a treatment laser to the irradiation position acquired by this irradiation position acquisition means By further including a system control unit that controls the laser treatment apparatus so that the treatment laser is emitted when the state is reached, it is possible to prevent the treatment laser from being irradiated to an unnecessary part.

  DESCRIPTION OF EMBODIMENTS Hereinafter, embodiments of a phototherapy diagnosis system of the present invention will be described in detail with reference to the drawings. FIG. 1 is a schematic view showing a preferred embodiment of the phototherapy diagnostic system of the present invention. The optical therapy diagnostic system 1 in FIG. 1 acquires an image of an irradiation target S by inserting an optical probe 10 into a body cavity, and irradiates the irradiation target (affected part) with a treatment laser Lt. Image acquisition device 1A that acquires an image of irradiation target S by irradiating measurement light L1 to S, laser treatment device 1B that emits treatment laser Lt to irradiation target S, and measurement light that is emitted from image acquisition device 1A An optical probe 10 that guides L1 and a treatment laser Lt emitted from the laser treatment apparatus 1B to the irradiation target S is provided.

  The image acquisition apparatus 1A has a function of acquiring a tomographic image of the irradiation target S by, for example, OCOptical Coherence Tomography) and displaying the tomographic image on the display apparatus 1C. Specifically, the image acquisition device 1A acquires a tomographic image by so-called SS-OCT (Swept source OCT). For example, the image acquisition device 1A sets a wavelength at a constant period in a wavelength range of 100 nm with a central wavelength of 1.3 μm. The measurement light L1 is emitted while sweeping. Then, the image acquisition device 1A generates a tomographic image based on the reflected light (backscattered light) Lr from the irradiation target S when the measurement light L1 is irradiated to the irradiation target, and displays the tomographic image on the display device 4. It has become.

  The laser treatment apparatus 1B emits a treatment laser Lt for irradiating the irradiation target S, and its operation is controlled by a system control unit. The treatment laser Lt is emitted from a light source made of, for example, an Nd: YAG laser and has a wavelength of 1.06 μm. Thus, in the phototherapy diagnosis system 1, the wavelength of the measurement light L1 emitted from the image acquisition device 1A (1.3 μm ± 100 nm) and the wavelength of the treatment laser Lt (1.06 μm) are in different wavelength ranges. It consists of a laser. Note that the laser treatment apparatus 1B uses, for example, a cancer thermotherapy that uses the heat generated by irradiation of laser light, collagen fiber bonding, protein coagulation / degeneration, hemostasis, tissue removal, incision, and the like via a photosensitive substance. A laser having a specific wavelength is emitted in accordance with an application such as a photodynamic therapy using a chemical reaction.

  The optical probe 10 guides the measurement light L1 emitted from the image acquisition device 1A and the treatment laser Lt emitted from the laser treatment device 1B to the irradiation target S inside the body cavity, and through the forceps opening. It is inserted into a body cavity. The treatment laser Lt and the measurement light L1 are incident on the optical probe 10 via the light incident means 5.

  This light incident means 1F is composed of, for example, a dichroic mirror, and reflects the measurement light L1 emitted from the image acquisition device 1A via the optical fiber FB2 and emits it to the optical probe 10 side, and the light from the laser treatment device 1B. The treatment laser Lt emitted through the fiber FB3 is transmitted and emitted to the optical probe 10 side.

  FIG. 2 is a schematic diagram showing a preferred embodiment of the optical probe of the present invention. The optical probe 10 will be described with reference to FIGS. 1 and 2. The optical probe 10 treats the cylindrical probe outer cylinder 11, the measurement light (first light) L <b> 1 and the irradiation target S that are accommodated in the probe outer cylinder 11 for acquiring a tomographic image of the irradiation target S. The optical waveguide member 12 that guides the treatment laser (second light) Lt to be irradiated, and the measurement light (first light) L1 guided in the optical waveguide member 12 is irradiated outside the probe outer tube 11 A first irradiation unit 14 that irradiates the target S, and a laser irradiation unit 16 that irradiates the irradiation target S outside the probe outer cylinder 11 with a treatment laser (second light) Lt guided in the optical waveguide member 12. And.

  The probe outer cylinder (sheath) 11 is made of a flexible cylindrical member, and the probe outer cylinder 11 is made of, for example, a transparent material through which the measurement light L1 and the treatment laser Lt are transmitted. The probe outer cylinder 11 has a structure in which the tip is closed by a cap 11a.

  The optical waveguide member 12 is composed of one optical fiber that guides the measurement light L1 and the treatment laser Lt, and operates in the direction of the arrow R1 with respect to the probe outer cylinder 11 at about 20 Hz, for example, by the operation of the scanning drive unit 31 of FIG. It is designed to rotate. As described above, since both the measurement light L1 and the treatment laser Lt are guided in one optical fiber, only one optical fiber is required to be accommodated in the probe outer tube 11, so that the diameter of the optical probe 10 is reduced. can do.

  The first irradiating unit 14 in FIG. 2 is formed of, for example, a dichroic mirror, and transmits the light in the wavelength band of the treatment laser Lt emitted from the optical waveguide member 12, and the measurement light L1 emitted from the optical waveguide member 12 is transmitted. The light is reflected and irradiated toward the irradiation target S located outside the probe outer cylinder 11. The first irradiation unit 14 is fixed to the tip of the optical waveguide member 12 via the measurement light condensing means 13. Therefore, when the optical waveguide member 12 is rotated in the direction of the arrow R1 by the operation of the scanning drive unit 20, the first irradiation unit 14 is also rotated in the direction of the arrow R1. Note that the measurement light condensing means 13 is composed of, for example, a GRIN lens (gradient refractive index lens), and the measurement light L1 emitted from the optical waveguide member 12 is irradiated on the irradiation target S separated from the probe outer cylinder 11 by about 1 mm. The light is condensed with respect to the position Pm.

  The second irradiation unit 16 is formed of, for example, a prism, and the treatment laser Lt emitted from the optical waveguide member 12 and transmitted through the first irradiation unit 14 is totally reflected and irradiated to the irradiation target S outside the probe outer tube 11. To do. The second irradiation unit 16 is fixed to the first irradiation unit 14 via the treatment laser condenser lens 15. Accordingly, when the optical waveguide member 12 is rotated in the direction of the arrow R1 by the operation of the scanning drive unit 20, the second irradiation unit 16 is also rotated in the direction of the arrow R1. The measurement light condensing means 15 is composed of, for example, a GRIN lens (gradient refractive index lens), and condenses the irradiation portion Pm of the irradiation target S that is about 1 mm away from the probe outer cylinder 11.

  Here, when the measurement light L1 and the treatment laser Lt are simultaneously emitted from the optical waveguide member 12, the first irradiation unit 14 and the laser irradiation unit 16 irradiate the measurement light L1 and the treatment laser Lt to different parts, respectively. It has become. Specifically, as shown in FIG. 3, when the measurement light L1 and the treatment laser Lt are simultaneously emitted from the optical waveguide member 12, the first irradiation unit 14 irradiates the site Pm of the irradiation target S with the measurement light L1. And the 2nd irradiation part 16 irradiates the site | part Pt which shifted | deviated only about 180 degrees from the site | part Pm with the treatment laser Lt.

  Further, the second irradiation unit 16 irradiates the treatment laser Lt on the locus Ltrk formed on the irradiation target S when the measurement light L1 is irradiated while scanning the irradiation target S in the arrow R1 direction. It is like that. Therefore, the treatment laser Lt can be irradiated to the irradiation position where the tomographic image acquired by the irradiation of the measurement light L1 in the image acquisition device 1A is displayed.

  Next, operation examples of the optical therapy diagnostic system 1 and the optical probe 10 will be described with reference to FIGS. 1 and 2. First, the measurement light L1 is emitted from the image acquisition device 1A of FIG. 1, and is incident on the optical probe 10 via the optical fiber FB1, the light incident means 1F, and the optical fiber FB4. In the optical probe 10 of FIG. 2, the measurement light Lt is guided in the optical waveguide member 12, collected by the measurement light condensing means 13, and directed to the irradiation target S outside the probe outer cylinder 11 by the first irradiation unit 14. It is injected towards.

  When the measurement light L <b> 1 is irradiated onto the irradiation target S, reflected light (backscattered light) Lr from the irradiation target S is incident on the first irradiation unit 14. The reflected light Lr is incident on the optical waveguide member 12 via the measurement light condensing means 13 by the first irradiation unit 14. Then, the reflected light Lr is guided in the optical waveguide member 12, and is incident on the image acquisition device 1A via the optical fiber FB4, the light incident means 1F, and the optical fiber FB2 in FIG. In the image acquisition device 1A, the reflection intensity (reflectance) at each depth position of the irradiation target S is detected based on the reflected light Lr. The detection of the reflection intensity is performed by the scanning drive unit 31 irradiating the measurement light L1 while scanning the irradiation target S while the optical waveguide member 12 rotates in the direction of the arrow R1. In addition, the irradiation position of the measurement light L1 by the first irradiation unit 14 is constantly monitored by a rotary motor trigger signal in the system control unit 1D. Then, a tomographic image along the circumferential direction of the probe outer cylinder 11 as shown in FIG. 3 is acquired by the image acquisition device 1A and displayed on the display device 1C.

  Thereafter, the doctor makes a diagnosis based on the tomographic image displayed on the display device 1C, determines the irradiation position / region to irradiate the treatment laser Lt, and the irradiation position / region is input using an input means such as a mouse, The irradiation position / region input in the irradiation position acquisition means 1E is acquired. Then, the system control unit 1D calculates the ON / OFF timing of the treatment laser Lt based on the rotation speed and direction of the laser irradiation unit 16 from the irradiation position / region on the acquired tomographic image. Specifically, in FIG. 3, when the irradiation site Pt is set to be the site SP that irradiates the treatment laser Lt, the second irradiation unit 16 is directed to irradiate the treatment laser Lt to the irradiation site SP. 1 (SP = Pt), the laser control unit 1D in FIG. 1 performs control so that the treatment laser Lt is emitted from the laser treatment apparatus 1B.

  Thereby, only a required part can be irradiated, without irradiating the treatment laser Lt to an unnecessary part. In accordance with an instruction from the doctor, the treatment laser Lt is irradiated to the irradiation target S for a predetermined time / number of pulses to automatically stop, or the treatment laser Lt is monitored while the doctor monitors the progress of the laser treatment with an OCT image. The doctor may instruct the stop of irradiation of the treatment laser Lt at an appropriate timing.

  Here, when the treatment laser Lt is emitted from the laser treatment apparatus 1B, the treatment laser Lt and the measurement light L1 are simultaneously incident on the optical waveguide member 12, and from the first irradiation unit 14 and the second irradiation unit 16. Each will be injected at the same time. At this time, as shown in FIG. 3, the measurement light L1 is emitted to the irradiation position Pt of the irradiation object S, and the treatment laser Lt is irradiated to the irradiation site Pt different from the irradiation site Pt. That is, the treatment laser Lt is not irradiated to the site where the tomographic information is acquired by irradiating the measurement light L1. Therefore, since it is possible to reduce the reflected light Lr of the measurement light L1 from stray light due to the treatment laser Lt, it is possible to reduce image quality degradation due to stray light. In particular, since the irradiation position Pm of the measurement light L1 and the irradiation position Pt of the treatment laser Lt are approximately 180 ° apart from the circumferential direction of the probe outer cylinder 11, image quality degradation due to the treatment laser Lt is reliably reduced. be able to.

  Further, even while the treatment laser Lt is being irradiated, the measurement light L1 can be emitted to a site Pm different from the treatment laser irradiation site Pt, and tomographic information can be acquired. For this reason, while being able to acquire a tomographic image efficiently, laser treatment can be performed, monitoring the irradiation object S in real time using the tomographic image about the progress of the treatment by the treatment laser.

  In the above embodiment, due to the difference in wavelength range between the measurement light L1 and the treatment laser Lt, the light incident means 1F in FIG. 1 and the first irradiation unit 14 in FIG. 2 reflect the measurement light L1 to reflect the treatment laser Lt. To be transparent. Here, even if the measurement light L1 and the treatment laser Lt are in the same wavelength range, the polarization directions may be orthogonal to each other. At this time, in the light incident means 1F in FIG. 1 and the first irradiation unit 14 in FIG. 2, for example, a polarization beam splitter can be used to reflect the measurement light L1 and transmit the treatment laser Lt.

  In the above embodiment, the arrangement of the first irradiation unit 14 and the second irradiation unit 16 in FIG. 2 may be reversed. That is, in FIG. 2, 14 becomes the second irradiation unit so as to transmit the measurement light L1 (first light) and reflect the treatment laser Lt (second light), and 16 becomes the first irradiation unit. Then, the measurement light L1 transmitted through the second irradiation unit may be reflected to the irradiation target S.

  Moreover, although the case where the discrete angle between the irradiation position Pm of the measurement light L1 and the irradiation position Pt of the treatment laser Lt is 180 ° is illustrated, the measurement light L1 and the treatment laser Lt are, for example, 120 ° and 90 °. Any relationship may be used as long as the angles can be separated.

  FIG. 4 is a schematic view showing a second embodiment of the optical probe of the present invention. The optical probe 100 will be described with reference to FIG. In the optical probe 100 of FIG. 4, parts having the same configuration as that of the optical probe 10 of FIG. The optical probe 100 in FIG. 4 differs from the optical probe 10 in FIG. 1 in that the first irradiation unit 14 and the second irradiation unit 16 move in the longitudinal direction (arrow A direction) of the probe outer cylinder 11 with respect to the probe outer cylinder 11. In other words, it has a so-called linear scan type configuration.

  Specifically, the drive unit 120 in FIG. 1 moves the optical waveguide member 12 accommodated in the probe outer cylinder 11 in the direction of arrow A, thereby measuring the light collecting lens 13 fixed to the optical waveguide member 12. The first irradiation unit 14, the laser condenser lens 15, and the second irradiation unit 16 are integrally moved in the arrow A direction. Further, the reflection surface of the measurement light L1 in the first irradiation unit 14 and the reflection surface of the treatment laser Lt in the laser irradiation unit 16 are formed so as to be substantially parallel to each other. Therefore, when the first irradiation unit 14 irradiates the measurement light L1 while moving in the arrow A1 direction, the measurement light L1 emitted from the first irradiation unit 14 draws a substantially linear locus Ltrk along the probe outer cylinder 11. It is. And when the treatment laser Lt is irradiated from the laser irradiation part 16, the measurement light L1 will be irradiated on the locus | trajectory Ltrk formed on the irradiation object S. FIG.

  Even in this case, since the measurement light L1 and the treatment laser Lt are emitted to different irradiation positions Pm and Pt, the reflected light Lr of the measurement light L1 includes stray light caused by the treatment laser Lt. It is possible to reduce image quality deterioration due to stray light. Even while the treatment laser Lt is being irradiated, the measurement light L1 is applied to a site Pm different from the treatment laser irradiation site Pt, and tomographic information is acquired. Laser can be irradiated simultaneously, a tomographic image can be acquired efficiently, and laser treatment can be performed while monitoring the progress of treatment by the treatment laser in real time using the tomographic image.

  Although the drive unit 31 is illustrated as moving in the direction of arrow A, it may be moved in the direction of arrow A and rotated in the direction of arrow R1. As a result, the image acquisition apparatus 1A can acquire a three-dimensional tomographic image of the irradiation target S, and can identify and observe a site for laser treatment based on the three-dimensional tomographic image.

  FIG. 5 is a schematic view showing a third embodiment of the optical probe of the present invention. The optical probe 120 will be described with reference to FIG. In the optical probe 120 of FIG. 5, the same reference numerals are given to the portions having the same configuration as the optical probe 10 of FIG. The optical probe 120 in FIG. 4 differs from the optical probe 10 in FIG. 1 in the structure of the first irradiation unit 214 and the second irradiation unit 216.

  Specifically, the first irradiation unit 214 is made of, for example, a MEMS (Micro Electro Mechanical Systems) total reflection mirror, and reflects the measurement light L1 that can swing with respect to the optical axis of the optical waveguide member 12. The surface 216a has a surface 216a, and the first reflecting surface 214 is swung in the direction of the arrow R2 to scan the measuring light L1 in the direction of the arrow A on the irradiation object arranged outside the probe outer cylinder 11. Irradiation. On the other hand, the second irradiating unit is made of, for example, a MEMS dichroic mirror, and has a second reflecting surface 216a that reflects the treatment laser Lt that can swing with respect to the optical axis of the optical waveguide member 12, By oscillating the reflecting surface 216a in the direction of the arrow R2, the treatment laser Lt is irradiated on an arbitrary site on the locus Ltrk of the measurement light L1.

  Then, the doctor performs tomographic image diagnosis while viewing the tomographic image on the display device 1C. Then, the doctor instructs the irradiation position / region of the treatment laser Lt on the display device 1C. The irradiation position and the like are acquired by the irradiation position acquisition means 1E, the deflection angle and the deflection range of the second irradiation unit 16 are calculated by the system control unit 1D, and the treatment laser Lt is irradiated to the irradiation target S by the treatment laser device 1B. . Thereby, only the necessary part can be irradiated without irradiating the unnecessary part with the treatment laser Lt. When the measurement light L1 scans the irradiation target S, the treatment light scans other places or stops. Thereby, it is possible to reduce the occurrence of noise in the image by the treatment laser.

  In FIG. 5, the second light irradiation unit 216 transmits the measurement light L1 out of the probe outer tube 11 through the measurement light L1 out of the measurement light L1 and the treatment laser Lt emitted from the optical waveguide member 12. The second irradiation unit 214 distributes the measurement light L1 transmitted through the second light irradiation unit 216 to the outside of the probe outer cylinder 11 while scanning the irradiation target S arranged in the direction. Although the arrangement structure is such that the irradiation target S can be irradiated, this arrangement structure can be similarly applied to the optical probes 10 and 100 of FIGS. 2 and 4 described above.

  FIG. 6 is a schematic view showing a fourth embodiment of the optical probe of the present invention. The optical probe 140 will be described with reference to FIG. In the optical probe 140 of FIG. 6, parts having the same configurations as those of the optical probe 10 of FIG. The optical probe 140 in FIG. 6 differs from the optical probe 10 in FIG. 1 in that the optical waveguide member is composed of a plurality of optical fibers.

  In other words, the optical waveguide unit 312 includes a first optical fiber 312a that guides the measurement light L1, and a second optical fiber 312b that guides the treatment laser Lt. The first optical fiber 312a is a single mode optical fiber, and the second optical fiber 312b is a multimode optical fiber. Optical lenses 13 and 15 are fixed to the tips of the optical fibers 312a and 312b, respectively, and a total reflection mirror 301 is fixed to the optical lenses 13 and 15. The total reflection mirror 301 has two reflection surfaces that are substantially orthogonal to each other. One reflection surface functions as a first irradiation unit 314 that reflects the measurement light L1, and the other reflection surface receives the treatment laser Lt. It functions as the 2nd irradiation part 316 which reflects.

  Even in this case, while the treatment laser Lt is being irradiated, the measurement light L1 can be applied to a site Pm different from the irradiation site Pt of the treatment laser to obtain tomographic information. For this reason, while being able to acquire a tomographic image efficiently, laser treatment can be performed, monitoring the irradiation object S in real time using the tomographic image about the progress of the treatment by the treatment laser. Furthermore, since the optical paths of the measurement light L1 and the treatment laser Lt are different, the optical waveguide members 312a and 312b and the optical lenses 13 and 15 can be optical members optimized for each light.

  In the optical probe 140, the light incident means 1F in FIG. 1 is not necessary, and the image acquisition device 1A and the laser treatment device 1B are optically connected to the optical fibers 312a and 312b, respectively.

  Hereinafter, an example of an image acquisition apparatus to which the optical probe according to the present invention is applied will be described. An image acquisition apparatus 1A shown in FIG. 7 acquires a tomographic image to be measured by the above-described SS-OCT measurement.

  The light source unit 310 in this apparatus emits laser light La while sweeping the frequency at a constant period. Specifically, the light source unit 310 includes a semiconductor optical amplifier (semiconductor gain medium) 311 and an optical fiber FB10, and the optical fiber FB10 is connected to both ends of the semiconductor optical amplifier 311. The semiconductor optical amplifier 311 has a function of emitting weak emission light to one end side of the optical fiber FB10 by injecting drive current and amplifying light incident from the other end side of the optical fiber FB10. When a drive current is supplied to the semiconductor optical amplifier 311, a pulsed laser beam La is emitted to the optical fiber FB 1 by an optical resonator formed by the semiconductor optical amplifier 311 and the optical fiber FB 10. .

  Further, an optical branching device 312c is coupled to the optical fiber FB10, and a part of the light guided in the optical fiber FB10 is emitted from the optical branching device 312c to the optical fiber FB11 side. Light emitted from the optical fiber FB11 is reflected by a rotating polygon mirror (polygon mirror) 316 via a collimator lens 313, a diffraction grating element 314, and an optical system 315. Then, the reflected light is incident on the optical fiber FB11 again via the optical system 315, the diffraction grating element 314, and the collimator lens 313.

  Here, the rotary polygon mirror 316 rotates in the direction of the arrow R1, and the angle of each reflecting surface changes with respect to the optical axis of the optical system 315. As a result, only light in a specific frequency region out of the light dispersed by the diffraction grating element 314 returns to the optical fiber FB11 again. The frequency of light returning to the optical fiber FB11 is determined by the angle between the optical axis of the optical system 315 and the reflecting surface. Then, light in a specific frequency range incident on the optical fiber FB11 is incident on the optical fiber FB10 from the optical splitter 312c, and as a result, laser light La in a specific frequency range is emitted to the optical fiber FB1 side. .

  Therefore, when the rotary polygon mirror 316 rotates at a constant speed in the direction of the arrow R1, the wavelength λ of light incident on the optical fiber FB11 again changes with a constant period as time passes. Thus, the wavelength-swept laser beam La is emitted from the light source unit 310 to the optical fiber FB1 side.

  The light splitting means 3 is composed of, for example, a 2 × 2 optical fiber coupler, and splits the light La guided from the light source unit 210 through the optical fiber FB1 into the measurement light L1 and the reference light L2. The light splitting means 3 is optically connected to the two optical fibers FB2 and FB3, respectively. The measurement light L1 is guided through the optical fiber FB2, and the reference light L2 is guided through the optical fiber FB3. The light splitting means 3 in this example also functions as the multiplexing means 4.

  1 is optically connected to the optical fiber FB2, and the measurement light L1 is guided from the optical fiber FB2 to the optical probe 10. The optical probe 10 is inserted into a body cavity from a forceps opening through a forceps channel, for example, and is detachably attached to the optical fiber FB2 by an optical connector 31.

  On the other hand, the optical path length adjusting means 220 is disposed on the side of the optical fiber FB3 from which the reference light L2 is emitted. The optical path length adjusting unit 220 changes the optical path length of the reference light L2 in order to adjust the position at which tomographic image acquisition is started, and reflects the reference light L2 emitted from the optical fiber FB3. 22, a first optical lens 21 a disposed between the reflection mirror 22 and the optical fiber FB 3, and a second optical lens 21 b disposed between the first optical lens 21 a and the reflection mirror 22. Yes.

  The first optical lens 21a has a function of converting the reference light L2 emitted from the core of the optical fiber FB3 into parallel light and condensing the reference light L2 reflected by the reflection mirror 22 onto the core of the optical fiber FB3. ing. Further, the second optical lens 21b condenses the reference light L2 converted into parallel light by the first optical lens 21a on the reflection mirror 22, and makes the reference light L2 reflected by the reflection mirror 22 into parallel light. have. That is, a confocal optical system is formed by the first optical lens 21a and the second optical lens 21b.

  Therefore, the reference light L2 emitted from the optical fiber FB3 is converted into parallel light by the first optical lens 21a, and is condensed on the reflection mirror 22 by the second optical lens 21b. Thereafter, the reference light L2 reflected by the reflection mirror 22 becomes parallel light by the second optical lens 21b, and is condensed on the core of the optical fiber FB3 by the first optical lens 21a.

  Furthermore, the optical path length adjusting means 220 includes a base 23 on which the second optical lens 21b and the reflecting mirror 22 are fixed, and a mirror moving means 24 for moving the base 23 in the optical axis direction of the first optical lens 21a. is doing. The optical path length of the reference light L2 can be changed by moving the base 23 in the arrow A direction.

  Further, the multiplexing means 4 is composed of a 2 × 2 optical fiber coupler as described above, and the reference light L2 whose frequency shift and optical path length have been changed by the optical path length adjusting means 220 and the reflected light L3 from the irradiation target S. Are combined and emitted to the interference light detection means 240 side via the optical fiber FB4.

  The interference light detection unit 240 detects the interference light L4 between the reflected light L3 combined by the combining unit 4 and the reference light L2. And the image acquisition means 250 detects the intensity | strength of the reflected light L3 in each depth position of the irradiation target S by Fourier-transforming the interference light L4 detected by the interference light detection means 240, and the tomography of the irradiation target S Get an image. The acquired tomographic image is displayed on the display device 260. The apparatus of this example has a mechanism that guides the light obtained by dividing the interference light L4 into two by the optical fiber coupler 3 to the photodetectors 40a and 40b, and performs balance detection in the calculation means 241. As described above, in this example, the interference light detection means 240 is configured by the photodetectors 40 a and 40 b and the calculation means 241.

  Here, the detection of the interference light L4 and the generation of the image in the interference light detection means 240 and the image acquisition means 250 will be briefly described. Details of this point are described in “Mitsuo Takeda,“ Optical Frequency Scanning Spectrum Interference Microscope ”, Optical Technology Contact, 2003, Vol. 41, No. 7, p426-p432”.

Interference fringes with respect to each optical path length difference l when the reflected light L3 and the reference light L2 from the respective depths of the irradiation target S interfere with each other with various optical path length differences when the measurement light L1 is irradiated onto the irradiation target S. S (l) is the light intensity I (k) detected by the interference light detection means 240.
I (k) = ∫ ₀ ^∞ S (l) [1 + cos (kl)] dl
It is represented by Here, k is the wave number, and l is the optical path length difference. It can be considered that the above equation is given as an interferogram in the optical frequency domain with the wave number k = ω / c as a variable. For this reason, in the image acquisition means 250, the spectral interference fringes detected by the interference light detection means 240 are subjected to Fourier transform, and the light intensity S (l) of the interference light L4 is determined. Distance information and reflection intensity information can be acquired, and a tomographic image can be generated. The optical probe 10 is also used in this image acquisition apparatus 1A.

  Next, another example of the image acquisition apparatus to which the optical probe according to the present invention is applied will be described with reference to FIG. An image acquisition apparatus 200 shown in FIG. 8 acquires, for example, a tomographic image of a measurement target such as a living tissue or a cell in a body cavity by the above-described SD-OCT (Spectral Domain OCT) measurement. The difference from the image acquisition device 1 is the configuration of the light source unit and the interference light detection means.

  A light source unit 210 that emits light La, a light dividing unit 3 that divides the light La emitted from the light source unit 210 into measurement light L1 and reference light L2, and an optical path of the reference light L2 divided by the light dividing unit 3 The optical path length adjusting means 220 for adjusting the length, the optical probe 10 for irradiating the irradiation object S with the measurement light L1 divided by the light dividing means 3, and the irradiation object S when the irradiation light S is irradiated with the measurement light L1. And a light combining means 4 for combining the reflected light L3 reflected by the reference light L2 and the reference light L2, and an interference light detecting means 240 for detecting the interference light L4 between the combined reflected light L3 and the reference light L2. is doing.

  The light source unit 210 emits low-coherent light La, for example, SLD (Super Luminescent Diode), ASE (Amplified Spontaneous Emission), or a supercontinuum light source 111 that obtains broadband light by irradiating a nonlinear medium with ultrashort pulse laser light. And an optical system 112 for causing the light emitted from the light source 111 to enter the optical fiber FB1.

  On the other hand, the interference light detection means 240 detects the interference light L4 between the reflected light L3 combined by the multiplexing means 4 and the reference light L2, and uses the interference light L4 emitted from the optical fiber FB4 as parallel light. The collimator lens 141 to be converted, the spectroscopic means 142 for dispersing the interference light L4 having a plurality of wavelength bands for each wavelength band, and the light detection means 144 for detecting the interference light L4 of each wavelength band split by the spectroscopic means 142. And have.

  The spectroscopic means 144 is composed of, for example, a diffraction grating element, etc., and splits the interference light L4 incident thereon and emits the light toward the light detection means 144. The light detection means 144 is composed of, for example, an element such as a CCD in which light sensors are arranged one-dimensionally or two-dimensionally. Each light sensor separates the interference light L4 separated as described above for each wavelength band. It comes to detect.

  The light detection means 144 is connected to an image acquisition means 250 made up of a computer system such as a personal computer. The image acquisition means 250 is connected to a display device 260 made up of a CRT or a liquid crystal display device.

  Hereinafter, the operation of the image acquisition apparatus 1A having the above configuration will be described. When acquiring a tomographic image, the optical path length is adjusted so that the irradiation target S is positioned within the measurable region by first moving the base 23 in the direction of arrow A. Thereafter, the light La is emitted from the light source unit 210, and the light La is split into the measurement light L1 and the reference light L2 by the light splitting means 3. The measurement light L1 is emitted from the optical probe 10 into the body cavity and irradiated on the irradiation target S. At this time, the measurement light L1 emitted from the optical probe 10 operating as described above scans the irradiation target S one-dimensionally. Then, the reflected light L3 from the irradiation target S is combined with the reference light L2 reflected by the reflecting mirror 22, and the interference light L4 between the reflected light L3 and the reference light L2 is detected by the interference light detection means 240. The detected interference light L4 is subjected to appropriate waveform compensation and noise removal in the image acquisition means 250 and then subjected to Fourier transform, whereby reflected light intensity distribution information in the depth direction of the irradiation target S is obtained.

  Then, if the measurement light L1 is scanned on the irradiation target S as described above by the optical probe 10, information in the depth direction of the irradiation target S can be obtained at each portion along the scanning direction. A tomographic image of a tomographic plane including The tomographic image acquired in this way is displayed on the display device 260. For example, by moving the optical probe 10 in the left-right direction in FIG. 7 and causing the measurement light L1 to scan the irradiation target S in a second direction orthogonal to the scanning direction, It is also possible to obtain a tomographic image of a tomographic plane including the direction.

  Next, still another example of the image acquisition apparatus to which the optical probe according to the present invention is applied will be described. An image acquisition apparatus 300 shown in FIG. 9 acquires a tomographic image to be measured by the above-described TD-OCT measurement, and includes a light source unit 210 including a light source 111 and a condensing lens 112 that emit laser light La; A light splitting means 2 for splitting the laser light La emitted from the light source unit 210 and propagating through the optical fiber FB1, a light splitting means 3 for splitting the laser light La passing therethrough into the measurement light L1 and the reference light L2, Light path length adjusting means 220 for adjusting the optical path length of the reference light L2 split by the light splitting means 3 and propagated through the optical fiber FB3, and the measurement light L1 split by the light splitting means 3 and propagated through the optical fiber FB2 to be irradiated The optical probe 10 that irradiates S and the reflected light L3 and the reference light L2 from the measurement target when the measurement light L1 is irradiated from the optical probe 10 to the irradiation target S are combined. And an interference light detection means 240 for detecting the interference light L4 of the reflected light L3 and the reference light L2 that are multiplexed by the multiplexing means 4. Yes.

  The optical path length adjusting means 220 is a mirror that is movable in the direction of arrow A in the figure so as to change the distance between the collimator lens 21 that collimates the reference light L2 emitted from the optical fiber FB3 and the collimator lens 21. 23 and mirror moving means 24 for moving the mirror 23, and has a function of changing the optical path length of the reference light L2 in order to change the measurement position in the irradiation target S in the depth direction. . Then, the reference light L 2 whose optical path length has been changed by the optical path length adjusting means 220 is guided to the multiplexing means 4.

  The interference light detection means 240 detects the light intensity of the interference light L4 that has propagated from the multiplexing means 4 through the optical fiber FB2. Specifically, when the difference between the total optical path length of the measuring light L1 and the reflected light L3 reflected or backscattered at a certain point of the irradiation target S and the optical path length of the reference light L2 is shorter than the coherence length of the light source Only an interference signal with an amplitude proportional to the amount of reflected light is detected. Further, by scanning the optical path length by the optical path length adjusting unit 220, the reflection point position (depth) of the irradiation target S from which the interference signal is obtained changes, and accordingly, the interference light detection unit 240 detects the irradiation target S. The reflectance signal at each measurement position is detected. The information on the measurement position is output from the optical path length adjustment unit 220 to the image acquisition unit. Then, based on the information on the measurement position in the mirror moving unit 24 and the signal detected by the interference light detection unit 240, the reflected light intensity distribution information in the depth direction of the irradiation target S is obtained by the image acquisition unit 250.

  Then, if the measurement light L1 is scanned on the irradiation target S as described above by the optical probe 10, information in the depth direction of the irradiation target S can be obtained at each portion along the scanning direction. A tomographic image of a tomographic plane including The tomographic image acquired in this way is displayed on the display device 260. For example, by moving the optical probe 10 in the left-right direction in FIG. 7 and causing the measurement light L1 to scan the irradiation target S in a second direction orthogonal to the scanning direction, the second direction is changed. It is also possible to further acquire a tomographic image of the tomographic plane including it.

  Also in this image acquisition device 300, the optical probe 10 having the same configuration as that used in the device of FIG. 7 is used, and the operation thereof is the same as that in the device of FIG.

  The image acquisition apparatuses 1A, 200, and 300 using the optical probe 10 have been described above. Instead of the optical probe 10, the optical probes 100, 120, and 140 according to another embodiment of the present invention described above are used. Of course, it can be used.

  The embodiment of the present invention is not limited to the above embodiment. For example, the image acquisition device 1A is not limited to acquiring a tomographic image by OCT measurement, but may be, for example, a confocal microscope device, or by irradiating excitation light (first light) as fluorescence as an image. It may be a fluorescence detection device for detection. Furthermore, two different types of images are displayed, and a tomographic image is acquired by OCT measurement by irradiating measurement light (first light) L1, and excitation light (second light) is irradiated. The optical probes 10, 100, 120, and 140 described above can also be used when simultaneously performing fluorescence detection.

The block diagram which shows preferable embodiment of the phototherapy diagnostic system of this invention Schematic diagram showing a preferred embodiment of the optical probe of the present invention Sectional drawing which shows the III-III cross section of FIG. The partially broken side view which shows the optical probe by 2nd Embodiment of this invention The partially broken side view which shows the optical probe by 3rd Embodiment of this invention The partially broken side view which shows the optical probe by 4th Embodiment of this invention The schematic block diagram which shows an example of the image acquisition apparatus by SD-OCT measurement using the optical probe of this invention The schematic block diagram which shows an example of the image acquisition apparatus by SS-OCT measurement using the optical probe of this invention The schematic block diagram which shows an example of the image acquisition apparatus by TD-OCT measurement using the optical probe of this invention

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Phototherapy diagnosis system 1A, 200, 300 Image acquisition apparatus 1B Laser treatment apparatus 1C Display apparatus 1D System control part 1E Irradiation position acquisition means 10, 100, 120, 140 Optical probe 11 Probe outer cylinder 12, 312 Optical waveguide member 14, 214 1st irradiation part 16,216 2nd irradiation part L1 Measurement light Lt Treatment laser

Claims (14)

A cylindrical probe outer tube,
An optical waveguide member that guides the first light and the second light, disposed in the axial direction of the probe outer cylinder in the inner space of the probe outer cylinder;
A first irradiating unit that irradiates the first light emitted from the tip of the optical waveguide member while scanning the irradiation target disposed on the outside of the probe outer cylinder;
Irradiation when the second light emitted from the tip of the optical waveguide member is irradiated while being scanned by the first irradiation unit on the irradiation object arranged outside the probe outer cylinder A second irradiating part that enables irradiation on the locus of the first light formed on the object,
When the first light and the second light are simultaneously emitted from the optical waveguide member, the first light and the second light are placed on different portions on the irradiation target. And the second light, respectively.   The optical probe according to claim 1, wherein the optical waveguide member is formed of a single optical fiber that guides the first light and the second light. Of the first light and the second light emitted from the optical waveguide member, the first irradiation unit transmits the second light and transmits the first light to the outside of the probe outer tube. Irradiating while scanning on the irradiation object arranged in,
The said 2nd irradiation part enables the said 2nd light which permeate | transmitted the said 1st irradiation part to be able to be irradiated on the said irradiation object distribute | arranged to the outer side of the said probe outer cylinder. Item 3. The optical probe according to Item 1 or 2. Of the first light and the second light emitted from the optical waveguide member, the second irradiation unit transmits the first light and transmits the second light to the outside of the probe outer tube. It is possible to irradiate on the irradiation object arranged in,
The first irradiating unit irradiates the second light transmitted through the second irradiating unit while scanning the irradiation target arranged outside the probe outer tube. The optical probe according to claim 1 or 2.   5. The optical probe according to claim 1, wherein the first light and the second light are light having different wavelength ranges. 6.   The first light and the second light are lights having polarization directions perpendicular to each other, and the optical waveguide member is made of a polarization-maintaining optical fiber. The optical probe according to claim 1.   2. The optical waveguide member according to claim 1, wherein the optical waveguide member includes a first optical fiber that guides the first light and a second optical fiber that guides the second light. Optical probe. The said 1st irradiation part and the said 2nd irradiation part are arrange | positioned so that rotation in the circumferential direction of the said probe outer cylinder is possible, The any one of Claim 1 to 7 characterized by the above-mentioned. Optical probe.   When the first light and the second light are simultaneously emitted from the optical waveguide member, the first light and the second light are approximately 180 with respect to the circumferential direction of the probe outer tube. 9. The optical probe according to claim 8, wherein the first light and the second light are respectively irradiated at positions separated by [deg.].   9. The optical probe according to claim 1, wherein the first irradiation unit and the second irradiation unit are arranged so as to be movable in a longitudinal direction of the probe outer cylinder. .   When the first irradiation unit and the second irradiation unit emit the first light and the second light simultaneously from the optical waveguide member, the first light and the second light, The optical probe according to claim 10, wherein each of the optical probes is irradiated in a same direction and at a predetermined distance. The first irradiating portion has a first reflecting surface that reflects the first light that can swing with respect to the optical axis of the optical waveguide member, and the first reflecting surface is swung to Irradiating the first light while scanning on the irradiation object arranged outside the probe outer cylinder,
The second irradiating portion has a second reflecting surface that reflects the second light that can swing with respect to the optical axis of the optical waveguide member, and the second reflecting surface swings the second light. The optical probe according to any one of claims 1 to 9, wherein the optical probe irradiates an arbitrary part on a locus of the first light. An image acquisition device that acquires an image of the irradiation target using reflected light from the irradiation target when the irradiation target is irradiated with measurement light;
A laser treatment apparatus for emitting a treatment laser for irradiating the irradiation object;
An optical probe that guides the treatment laser emitted from the laser treatment device and the measurement light emitted from the image acquisition device to the irradiation target;
The optical probe is
A cylindrical probe outer tube,
An optical waveguide member that guides the measurement light and the treatment laser disposed in the axial direction of the probe outer cylinder in the inner space of the probe outer cylinder;
A first irradiating unit that irradiates the measurement light emitted from the tip of the optical waveguide member while scanning the irradiation target disposed on the outside of the probe outer cylinder;
The treatment laser emitted from the distal end of the optical waveguide member is on the irradiation target disposed outside the probe outer cylinder, and is irradiated on the irradiation target while being scanned by the first irradiation unit. A second irradiating portion that enables irradiation on the trajectory of the measurement light formed on
When the measurement light and the treatment laser are simultaneously emitted from the optical waveguide member, the first irradiation unit and the second irradiation unit apply the measurement light and the treatment laser to different sites on the irradiation target. A phototherapy diagnostic system characterized in that each is irradiated.   Irradiation position acquisition means for acquiring position information for irradiating the treatment laser in the image acquired by the image acquisition device, and the irradiation position acquired by the second irradiation unit by the irradiation position acquisition means. The phototherapy diagnosis system according to claim 13, further comprising a system control unit that controls the laser treatment apparatus so that the treatment laser is emitted when a possible state is reached.

Images