WO2015151459A1

WO2015151459A1 - Optical driving device

Info

Publication number: WO2015151459A1
Application number: PCT/JP2015/001671
Authority: WO
Inventors: 池滝　慶記; 秀子小島
Original assignee: オリンパス株式会社; 国立大学法人愛媛大学
Priority date: 2014-04-01
Filing date: 2015-03-24
Publication date: 2015-10-08
Also published as: JP2015197602A

Abstract

This optical driving device includes a photomechanical driving unit (20) connected to a displaceable driven part (10), the photomechanical driving unit (20) having a spatial structure reversibly changeable in accordance with photoisomerization. The driven part (10) is displaced by a change in the photomechanical driving unit (20) responsive to driving light incident on the photomechanical driving unit (20).

Description

Optical drive device

Cross-reference of related applications

This application claims the priority of Japanese Patent Application No. 2014-75516 filed in Japan on April 1, 2014, the entire disclosure of which is incorporated herein by reference.

The present invention relates to an optical drive device.

For example, an endoscope is known as an inspection medical device. An endoscope is a technique developed for the purpose of examining the inside of a human body with minimal invasiveness. Initially, it started as an instrument for observing the inside of a body through a non-flexible tube, a so-called rigid endoscope. After that, a flexible endoscope was developed that can directly observe the inside of a body cavity by incorporating into the endoscope a glass fiber having the characteristic of transmitting light as it is from end to end even when bent. The so-called “fiberscope” has appeared.

The fiberscope guides the illumination light from the illumination light source through the light introduction fiber to illuminate the inside of the body cavity, and receives the scattered light from the affected area with a plurality of light receiving fibers (fiber bundles) bundled in a bundle. Transfer images. In the fiber bundle, each fiber constitutes a pixel to form an entire image. This enabled dynamic analysis by physicians and opened up a more advanced diagnosis path. Later, a “video scope (electronic scope)” with a CCD mounted on the distal end of the endoscope was developed, and an image of a portion to be examined (lesioned portion, etc.) can be displayed on a television monitor.

The electronic scope can display the condition of the test part, which could not be seen before, as an image on the TV monitor, so that multiple doctors and nurses can view it simultaneously. As a result, safety has been improved, oversight has been reduced, and diagnostic accuracy has been dramatically improved. In addition, image processing becomes possible, and processing that increases the sharpness of an image and processing that makes a test part easier to see by enhancing a specific color signal can be expanded, thereby expanding the possibility of diagnosis by an endoscope. Brought the result.

However, even an endoscope with improved functions still has significant technical issues. That is, even with an electronic scope, it places a burden on the subject when the endoscope is inserted into the body. In response to this problem, efforts have been made to reduce the diameter of the endoscope. As one of the efforts, for example, an attempt to scan a test portion with illumination light from one optical fiber, that is, an attempt to drive light has started.

Specifically, the illumination light transmitted from one optical fiber is condensed on the test site by a condenser lens. Signal light scattered or emitted from the test part is collected by the same lens and transmitted in the opposite direction to the illumination light through the same optical fiber. Alternatively, the signal light from the test part is received by a plurality of light receiving optical fibers and transmitted. The transmitted signal light is photoelectrically converted and stored as an information signal corresponding to one pixel of the test part. Illumination light from one optical fiber is spatially scanned to obtain a two-dimensional spatial image. This is called a scanning endoscope.

There are mainly three types of scanning endoscopes proposed so far. In the first method, the tip end portion of the optical fiber is spatially swung by an electromagnetic method using a coil and a magnet (see, for example, Patent Document 1). In the second method, the tip of the optical fiber is swung by a piezoelectric method using a piezoelectric element (see, for example, Patent Document 2). The third method is a MEMS method in which a MEMS (Micro Electro Mechanical Systems) optical scanner is mounted at the distal end of an endoscope to deflect the reflection direction of illumination light emitted from an optical fiber (for example, non-patent) Reference 1).

Special table 2008-514970 gazette Special table 2010-527028

However, each of the above methods has technical problems. For example, in the electromagnetic system, since a pulse with a high current needs to be applied to the coil, a secondary electromagnetic field pulse is generated in the body during use. Therefore, it is assumed that a subject wearing a pacemaker induces a malfunction of the pacemaker and is restricted in use.

Also, the piezoelectric method has a problem in the composition of the piezoelectric element itself. That is, many piezoelectric elements contain lead harmful to the human body in order to improve time response and driving force. In recent years, the development of piezoelectric elements that do not contain lead is also progressing, but it cannot be denied that piezoelectric elements have a low function in time response.

In the MEMS method, a MEMS optical scanner has extremely high accuracy, and advanced processing, assembly, and control technology based on advanced composite technology is required (for example, http://www.marubun-zaidan.jp/pdf/ h20 # toshiy.pdf). Therefore, enormous production equipment and precision measurement equipment are required for production, and there is a concern that the cost may increase. In addition, since the MEMS optical scanner is larger in size than the optical fiber, the diameter of the distal end portion of the endoscope cannot be sufficiently reduced.

Therefore, an object of the present invention made in view of the above-described circumstances is to provide an optical drive device that is excellent in versatility and can be configured simply and inexpensively.

An optical driving device according to the present invention that achieves the above object is as follows.
Equipped with a displaceable driven part, equipped with a photomechanical driving part whose spatial structure reversibly changes by photoisomerization,
The driven part is displaced by a change of the photomechanical driving part due to incidence of light driving light to the photomechanical driving part.

It is preferable that a plurality of the photomechanical drive units are mounted on the driven unit so as to displace the driven unit in different directions.

An optical drive light source unit that emits the optical drive light of at least two wavelengths that reversibly change the photomechanical drive unit;
It is preferable to further include an introduction optical system that transmits the light driving light from the light driving light source unit to the photomechanical driving unit.

The light driving light source unit may switch the light driving light of two wavelengths in time series and introduce it into the introduction optical system.

The light-driven light source unit may be variable in intensity or time of the two-wavelength light-driven light to be emitted.

It is preferable that one of the two wavelengths of the light driving light has a long wavelength of 400 nm or longer and the other has a shorter wavelength than 400 nm.

The light-driven light source unit may include one light-driven laser light source, and a multiple wave having a different fundamental wave emitted from the light-driven laser light source may be used as the light drive light having two wavelengths.

The introduction optical system may be detachable from the light driving light source unit.

The driven part may be a light guide part.

The driven part comprises a light guide part,
It is preferable to further include a photodetector that detects a light response signal from the irradiated portion irradiated with light emitted from the light guide portion.

And further comprising a control unit that controls the light-driven light source unit to cause the light-driven light to enter the photomechanical drive unit and that processes the output of the photodetector in synchronization with the control of the light-driven light source unit. Good.

The control unit may display the output of the photodetector corresponding to the displacement of the light guide unit.

The light detector may detect scattered light or fluorescence as the light response signal.

The driven part may be a drug introduction tube.

The photomechanical drive unit may include a photochromic layer having salicylidene aniline, fulgide, azobenzene, diarylethene, spiropyran, bisimidazole, and derivatives of these molecules.

The photochromic layer is preferably bulky and has an optical plane on at least one surface.

The surface accuracy of the optical plane is preferably ¼ or more of the wavelength of the light driving light.

It is preferable that different optical members are bonded to the optical plane.

The optical member may be an optical thin film.

The optical thin film may be formed by sputtering or vapor deposition.

The driven part and the photomechanical driving part may be detachably mounted.

According to the present invention, it is possible to provide an optical drive device that is excellent in versatility and can be configured simply and inexpensively.

It is a figure which shows the structure of the principal part of the optical drive device which concerns on 1st Embodiment. It is a figure for demonstrating the modification of the optical drive laser beam introduction layer of FIG. It is a figure for demonstrating the other modification of the optical drive laser beam introduction layer of FIG. It is a figure which shows the structure of an example of the principal part of the light source system of the optical drive device of FIG. It is a figure which shows an example of the branch optical fiber of FIG. It is a figure which shows the structure of the principal part of the optical drive device which concerns on 2nd Embodiment. It is the figure which looked at FIG. 5A from the optical fiber emission end surface side. It is a figure which shows the structure of an example of the principal part of the light source system of the optical drive device which concerns on 2nd Embodiment. It is a figure which shows the structure of the principal part of the scanning endoscope which concerns on 3rd Embodiment. It is a figure which shows an example of the optical connector of FIG. It is a figure for demonstrating the modification of the optical drive device which concerns on this invention.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.

(First embodiment)
FIG. 1 is a diagram illustrating a configuration of a main part of the light driving device according to the first embodiment. This optical drive device shows a basic configuration in the case of driving a flexible optical fiber 10 as a displaceable driven part, and is a photomechanical drive part attached to the exit end 11 of the optical fiber 10. 20. The optical fiber 10 is supported so that the emission end 11 can be displaced, for example, at the tip of a tubular member. The optical fiber 10 is made of, for example, a single mode fiber or a multimode fiber. The light transmitted through the optical fiber 10 and emitted from the emission end face 12 is irradiated to an irradiated portion (not shown) via a condenser lens 30 attached to the distal end face of the tubular member, for example.

The photomechanical drive unit 20 is formed in a sheet-like rectangular shape, and is fused to the discharge end 11 that can be displaced with the extending direction of the optical fiber 10 as a long side. The photomechanical drive unit 20 includes a bulk-shaped photochromic layer 21 and a light-driven laser light introduction layer 22 made of an optical thin film constituting an optical member. The photochromic layer 21 is coated with a cladding layer 23 on the surface not in contact with the light-driven laser light introducing layer 22. Similarly, the cladding layer 23 is also coated on the surface of the light-driven laser light introducing layer 22 that is not in contact with the photochromic layer 21.

For example, an optical fiber 40 constituting an introduction optical system is coupled to the end face 24 in the optical drive laser light introduction layer 22, and the optical drive laser light is introduced in the extending direction of the optical fiber 10 through the optical fiber 40. The periphery of the photomechanical drive unit 20 except for the end face 24 side is preferably subjected to a light shielding process so that the light-driven laser light introduced into the light-driven laser light introduction layer 22 does not leak outside. In FIG. 1, the photochromic layer 21 side is fused to the optical fiber 10, but the light-driven laser light introduction layer 22 side may be fused to the optical fiber 10.

The photochromic layer 21 is composed of, for example, salicylidene aniline, fulgide, azobenzene, diarylethene, spiropyran, bisimidazole, and derivatives of these molecules. The crystal layer or polymer film composed of these molecules generates a strong torque or stress by greatly changing the molecular structure with photoisomerization by repeated irradiation with ultraviolet and visible light. In addition, the photomechanical material has excellent durability and cost.

On the other hand, the light-driven laser light introducing layer 22 is composed of, for example, an optical thin film layer of SiO ₂ that is transparent up to the ultraviolet region. In this case, for example, when the photochromic layer 21 is cut into a sheet shape, the bonding surface is an optical surface smoothed by optical polishing or ion smoothing in advance, and SiO ₂ is sputtered or deposited on the surface of the photochromic layer 21. The light-driven laser light introduction layer 22 may be formed by laminating. Alternatively, the light-driven laser light introduction layer 22 may be formed by coating an acrylic-based resist agent on the surface of the photochromic layer 21 and heating or photocuring it. At this time, it is preferable that the optical smoothness (surface accuracy) of the coated surface is at least λ / 4 which does not cause reversal of the phase of light.

The clad layer 23 is coated on a surface that is not a joint surface between the photochromic layer 21 and the light-driven laser light introducing layer 22. The clad layer 23 is made of, for example, a highly reflective metal layer (for example, gold, silver, aluminum, etc.), or magnesium fluoride having a refractive index lower than that of the photochromic layer 21 and the light-driven laser light introducing layer 22.

In FIG. 1, when visible light or ultraviolet light (light-driven laser light) is incident on the light-driven laser light introduction layer 22 from the end face 24 side, the incident light is reflected by the cladding layer 23, and the photochromic layer 21 and light It is completely confined in the drive laser light introducing layer 22. That is, the light incident from the light-driven laser light introducing layer 22 propagates while being sequentially absorbed by the photochromic layer 21.

As a result, light spreads over all the spatial regions of the photochromic layer 21 and the photochromic layer 21 bends. As a result, the optical fiber 10 that is mechanically integrated with the photochromic layer 21 is also bent. For example, when the photochromic layer 21 is composed of azobenzene, when ultraviolet light having a wavelength of 355 nm is incident as light-driven laser light, the photochromic layer 21 is bent and when visible light having a wavelength of 532 nm is incident, the photochromic layer 21 is incident. Returns to its original shape.

The degree of bending of the photochromic layer 21 generally varies depending on the number of molecules excited and photoisomerized. That is, the angle of bending changes depending on the amount of light acting on the photochromic layer 21. Therefore, if the intensity or time of the optically driven laser beam to the photochromic layer 21 is controlled, the bending angle can be controlled reliably. In order to cause the light-driven laser light introduced into the light-driven laser light introduction layer 22 to act efficiently on the photochromic layer 21, for example, a light scatterer is formed on the surface of the light-driven laser light introduction layer 22 in contact with the photochromic layer 21. Alternatively, a cut may be formed on the surface opposite to the surface in contact with the photochromic layer 21 (see, for example, Japanese Patent Application Laid-Open No. 2011-244666).

2A and 2B are diagrams for explaining two modified examples of the light-driven laser light introduction layer 22. FIG. The light-driven laser light introducing layer 22 shown in FIG. 2A has a high refractive index sheet-like core layer 22a and low refractive index cladding layers 22b and 22c bonded to both surfaces thereof. The photoclock layer 21 is joined to one clad layer 22b. The other cladding layer 22c has a fine cut 22d that penetrates into the core layer 22a by etching or the like. A large number of the notches 22d are formed along the propagation direction of the optically driven laser beam.

The light-driven laser light introducing layer 22 shown in FIG. 2A propagates the light-driven laser light introduced into the core layer 22a while being totally reflected by the

clad layers

22b and 22c on both sides. At that time, the light-driven laser light is scattered by the notch 22d, and the reflection angle is greatly changed. As a result, light-driven laser light scattered at an angle at which total reflection is not possible passes through the cladding layer 22b and enters the photochromic layer 21 to induce deformation of the photochromic layer 21.

2B has a core layer 22a and low-refractive-index cladding layers 22b and 22c bonded to both surfaces, as in FIG. 2A. In one clad layer 22b, a large number of cuts 22d are formed so as to penetrate into the core layer 22a by etching or the like. The portion having the cut 22d is bent into a curved surface by thermoforming or the like, and the photochromic layer 21 is joined to the curved portion having the cut 22d.

The light-driven laser light introducing layer 22 shown in FIG. 2B propagates the light-driven laser light introduced into the core layer 22a while being totally reflected by the

clad layers

22b and 22c on both sides. At this time, the light-driven laser light is scattered by the cut 22 d in the curved surface portion, is emitted from the light-driven laser light introduction layer 22, and enters the photochromic layer 21. Thereby, the photochromic layer 21 is deformed. According to the light-driven laser light introducing layer 22 in FIG. 2B, the scattering angle of the light-driven laser light incident on the photochromic layer 21 can be adjusted more effectively by bending the whole. Further, since the generation position and intensity of the scattered light can be adjusted by the formation position and number of the notches 22d, the bending position and the deformation angle of the photochromic layer 21 can be easily adjusted.

FIG. 3 is a diagram showing a configuration of an example of a main part of the light source system of the light driving device shown in FIG. The light source system includes a light driving light source unit 50 and a control unit 60. The light drive light source unit 50 includes a light drive laser light source 51. As the light-driven laser light source 51, one that emits laser light having a required wavelength is used according to the characteristics of the photochromic layer 21. Here, for convenience of explanation, it is assumed that the photochromic layer 21 is made of azobenzene, and the light-driven laser light source 51 uses a semiconductor laser-pumped Nd: YVO 4 laser that emits a fundamental wave having a wavelength of 1064 nm.

The laser light emitted from the light-driven laser light source 51 is branched into two optical paths and is incident on a third harmonic generation unit 52a and a second harmonic generation unit 52b including a nonlinear optical crystal such as KDP. As a result, ultraviolet light having a wavelength of 355 nm, which is the third harmonic of the fundamental wave (wavelength 1064 nm), is emitted from the third harmonic generator 52a, and the second harmonic of the fundamental wave is emitted from the second harmonic generator 52b. Visible light having a wavelength of 532 nm is emitted. That is, two-wavelength active light (light-driven laser light) that reversibly photoisomerizes the photochromic layer 21 of the photomechanical drive unit 20 is obtained from one light-driven laser light source 51.

The light-driven laser light emitted from the third harmonic generation unit 52a is incident on the photoacoustic element (AOM) 53a. Similarly, the optically driven laser light emitted from the second harmonic generation unit 52b is incident on the AOM 53b. The light-driven laser light emitted from the AOM 53a and the AOM 53b is coupled to the optical fiber 40 via, for example, a branch optical fiber 54 as shown in FIG. 4 and, if necessary, an extension optical fiber.

The light-driven laser light source 51, the AOM 53a, and the AOM 53b are controlled by the control unit 60. The control unit 60 is configured by a host computer, for example. Thereby, the current of the pumping semiconductor laser of the light-driven laser light source 51 is controlled to control the output intensity of the third harmonic and the second harmonic obtained from the third harmonic generator 52a and the second harmonic generator 52b. Can do. Further, when the light-driven laser light source 51 has an optical filter automatic replacement function, a shutter opening / closing function, and the like, these can also be controlled. Further, by independently controlling the AOM 53a and the AOM 53b, the irradiation time of ultraviolet light and visible light can be controlled independently.

According to the optical drive device according to the present embodiment, the intensity or time is adjusted to the optical drive laser light introduction layer 22 of the photomechanical drive unit 20 from the optical drive laser light source 51 through the optical fiber 40 by the AOM 53a and AOM 53b. When ultraviolet light and visible light are incident alternately in time series, the dynamically integrated optical fiber 10 can be repeatedly swung in a one-dimensional direction. Therefore, for example, if the light (probe light) emitted from the optical fiber 10 through the forceps channel of the endoscope is condensed on the test portion such as the stomach wall via the condenser lens 30, the surface inside the body cavity is desired by the probe light. Can be spatially scanned at a single speed. Then, if scattered light or fluorescence generated from the test part is detected through the optical fiber 10 or other light receiving fiber, the detection output is processed by the control unit 60 in accordance with the scanning position and output to, for example, a monitor. The test part can be inspected.

(Second Embodiment)
FIG. 5A and FIG. 5B are diagrams illustrating a configuration of a main part of the light driving device according to the second embodiment. In the configuration shown in FIG. 1, this optical driving device enables the emission end 11 of the optical fiber 10 to be driven in a two-dimensional direction within an XY plane orthogonal to the extending direction of the emission end 11. . Therefore, the photomechanical drive unit 20X for driving in the X direction and the photomechanical drive unit 20Y for driving in the Y direction are fused to the outer periphery of the injection end portion 11 in a perpendicular positional relationship. The photomechanical drive unit 20X and the photomechanical drive unit 20Y are configured similarly to the photomechanical drive unit 20 shown in FIG.

In the photomechanical drive unit 20X, the optical drive laser beam is introduced into the optical drive laser beam introduction layer via the optical fiber 40X constituting the introduction optical system. Similarly, light-driven laser light is introduced into the light-driven laser light introduction layer via the optical fiber 40Y constituting the introduction optical system into the photomechanical drive unit 20Y. FIG. 5B shows a view of FIG. 5A viewed from the exit end face 12 side of the optical fiber 10.

FIG. 6 is a diagram illustrating a configuration of an example of a main part of the light source system of the light driving device according to the second embodiment. This light source system can emit ultraviolet light and visible light for driving in the X direction and ultraviolet light and visible light for driving in the X direction from the light driving light source unit 50, and the light source system shown in FIG. Different. Therefore, the same reference numerals are given to components having the same functions as those in FIG.

In FIG. 6, the third harmonic wave emitted from the third harmonic wave generation unit 52a is branched into two optical paths by a branch optical fiber 55a as shown in FIG. 4, for example, for the AOM 53aX for driving in the X direction and for driving in the Y direction. Is incident on the AOM 53aY. Similarly, the second harmonic wave emitted from the second harmonic wave generation unit 52b is branched into two optical paths by a branch optical fiber 55b similar to the branch optical fiber 55a, and the AOM 53bX for X direction driving and the AOM 53bY for Y direction driving Is incident on.

The optically driven laser light emitted from the AOM 53aX and the AOM 53bX is coupled to the optical fiber 40X via a branch optical fiber 54X similar to the branch optical fiber 54 and an extension optical fiber as necessary. Similarly, the optically driven laser light emitted from the AOM 53aY and the AOM 53bY is coupled to the optical fiber 40Y via a branch optical fiber 54Y similar to the branch optical fiber 54 and an extension optical fiber as necessary.

The light-driven laser light source 51, AOM 53aX, AOM 53aY, AOM 53bX, and AOM 53bY are controlled by the control unit 60.

According to the optical drive device according to the present embodiment, for example, the light of the photomechanical drive unit 20X is generated while the optical fiber 10 is displaced in the Y direction by making ultraviolet light incident on the optical drive laser light introduction layer of the photomechanical drive unit 20Y. If ultraviolet light and visible light are alternately incident on the drive laser light introduction layer and the optical fiber 10 is reciprocally displaced in the X direction, the light emitted from the optical fiber 10 causes, for example, the test portion to move at a desired speed. Raster scanning is possible. In addition, it is possible to control the optically driven laser light incident on the photomechanical drive unit 20X and the photomechanical drive unit 20Y so that the spurious scan is performed by the light emitted from the optical fiber 10, and two-dimensional scanning along various trajectories. Is possible. Therefore, for example, the test portion is two-dimensionally scanned with light (probe light) mounted on an endoscope and emitted from the optical fiber 10, thereby scattering light or fluorescence generated from the test portion to the optical fiber 10 or If detection is performed via another light receiving fiber, a two-dimensional image of the test part can be obtained, and thereby the test part can be inspected (diagnosed).

(Third embodiment)
FIG. 7 is a diagram illustrating a configuration of a main part of a scanning endoscope according to the third embodiment. This scanning endoscope includes the light driving device described in the second embodiment. Hereinafter, the same reference numerals are given to components having the same actions as the components described in the second embodiment, and description thereof is omitted.

7, the optical fiber 10 is disposed so as to extend into the insertion portion of the endoscope, and the emission end portion 11 is supported in a displaceable manner in the distal end portion of the insertion portion. Further, the condenser lens 30 is attached to the distal end portion of the insertion portion. 7 shows a so-called direct-view type in which light (probe) emitted from the optical fiber 10 is directly incident on the condenser lens 30, but is reflected in a side surface (circumferential surface) direction or an oblique side surface direction by a reflecting mirror. In the case of the so-called side view type or perspective type, the condensing lens 30 is mounted on the peripheral surface of the distal end portion of the insertion portion.

The optical fiber 10 is coupled to the optical connector of the optical fiber 80 via an optical connector 71 such as an FC connector and a relay adapter 72 as shown in FIG. Probe light emitted from the probe light laser light source 90 is incident on the optical fiber 80. The probe light incident on the optical fiber 80 is transmitted from the optical fiber 80 and the optical fiber 10 and is emitted from the emission end face 12 of the optical fiber 10. As a result, the probe light is irradiated to the test portion through the condenser lens 30.

As the probe light laser light source 90, one that emits laser light having a required wavelength is used in accordance with the part to be examined. Here, for convenience, a He—Ne laser is used, and a fundamental wave with a wavelength of 633 nm is used as the probe light. In the probe light laser light source 90, the control unit 60 controls the emission timing and intensity of the probe light.

In the present embodiment, the optical fiber 10 is also used as a light receiving fiber. Therefore, the probe light emitted from the probe light laser light source 90 is reflected by the beam splitter 91 and enters the optical fiber 80. As the beam splitter 91, for example, a dichroic mirror is used. Signal light such as scattered light and autofluorescence generated from the test part by probe light irradiation is collected by the condenser lens 30 and incident on the optical fiber 10, and transmitted through the optical fiber 10 and the optical fiber 80. Then, the light is emitted from the optical fiber 80, further passes through the beam splitter 91, and is received by the photodetector 92. For the photodetector 92, for example, a photomultiplier tube is used. The output of the photodetector 92 is input to the control unit 60.

On the other hand, the optical fiber 40X coupled to the photomechanical drive unit 20X is disposed so as to extend into the insertion portion of the endoscope, and is connected to the optical connector 71X outside the endoscope. Accordingly, it is detachably coupled to the output end of the branch optical fiber 54X of the light driving light source unit 50 through an extending optical fiber. Similarly, the optical fiber 40Y coupled to the photomechanical drive unit 20Y is disposed so as to extend into the insertion portion of the endoscope, and is connected to the optical connector 71Y outside the endoscope. Accordingly, it is detachably coupled to the output end of the branch optical fiber 54Y of the light driving light source unit 50 through an extending optical fiber.

The entire operation of the scanning endoscope according to the present embodiment is controlled by the control unit 60. That is, when the insertion portion of the endoscope is inserted into a desired portion to be examined such as a stomach wall and the start of scanning (examination) by the endoscope operator is operated, Control of the probe light laser light source 90 is started. Thereby, the optical fiber 10 is driven, and the test part is two-dimensionally scanned by the probe light. Then, the signal light generated at each scanning point is received by the photodetector 92 and input to the control unit 60, and required signal processing is performed.

The control unit 60 converts the output intensity of the optical drive laser light source 51 that drives the

photomechanical drive units

20X and 20Y into the bending angle of the optical fiber 10, that is, scans the output intensity of the optical drive laser light source 51 with probe light. It has a calibration table for converting to point position information. Based on this calibration table, the control unit 60 performs the required signal processing and stores the output signal from the photodetector 92 at a corresponding address in the frame memory. Then, the control unit 60 displays the two-dimensional image information stored in the frame memory on the monitor. Thereby, the doctor can perform a real-time examination (diagnosis) in the body by operating the control unit 60 after inserting the endoscope.

According to the present embodiment, the endoscope insertion portion that is inserted into the body does not have an electromagnetic wave generation source, and the optically driven laser light is transmitted from outside the body to the

photomechanical drive portions

20X and 20Y via the

optical fibers

40X and 40Y. To drive the optical fiber 10. Therefore, the diameter of the endoscope tip can be easily reduced as compared with the case where the MEMS optical scanner is used, and the pain of the subject can be reduced. Further, since all electrical control can be operated outside the body, secondary electromagnetic field pulses are not generated in the body as in the electromagnetic system, and no high voltage is introduced into the body as in the piezoelectric system. Therefore, it can be used for a subject wearing a pacemaker or the like, and versatility can be improved. In addition, since the photochromic layers of the

photomechanical drive units

20X and 20Y are composed of non-toxic molecules such as salicylideneaniline, fulgide, azobenzene, diarylethene, spiropyran, and bisimidazole, the safety can be further improved.

Further, the optical fiber 10 can be attached to and detached from the probe light laser light source 90 by the optical connector 71 outside the body. Similarly, the

optical fibers

40X and 40Y coupled to the

photomechanical drive units

20X and 20Y are also detachable from the light drive light source unit 50 by the

optical connectors

71X and 71Y outside the body. Therefore, the probe light laser light source 90, the light drive light source unit 50, and the endoscope unit can be easily attached and detached outside the body. Thereby, the endoscope unit can be easily made “disposable”, and the problem of cleaning the endoscope can be solved.

That is, in an endoscopic examination, for example, an examination of the stomach, when the endoscope is inserted into the stomach, the subject's gastric juice, vomit, and bacteria and viruses adhere to the endoscope. Therefore, when the endoscope is used repeatedly, careful cleaning and disinfection is required for each inspection in order to prevent secondary infection, which is a heavy burden in terms of safety and cost.

On the other hand, in the scanning endoscope according to the present embodiment, the portion to be inserted into the body is the insertion portion (tube), the

optical fibers

10, 40X, 40Y, the

photomechanical drive units

20X, 20Y, and the condenser lens. At 30 mag, everything can basically be made of a very inexpensive material, so it can be “disposable”. Therefore, safety and inspection costs can be reduced by using a new endoscope unit for each inspection.

It should be noted that the present invention is not limited to the above embodiment, and many variations or modifications are possible. For example, in the above embodiment, the light source unit 50 obtains two-wavelength light-driven laser light (active light) that reversibly isomerizes the photochromic layer 21 from one light-driven laser light source 51. You may make it obtain the optical drive laser beam of a wavelength using a laser beam for exclusive use, respectively.

In addition, the present invention can be applied to various treatments of a living body by emitting therapeutic laser light from the optical fiber 10, which is limited to the inspection of a living body. Further, the present invention can be applied not only to medical use but also to industrial endoscopes and processing apparatuses, and can also be applied to uses for distributing light emitted from an optical fiber. Furthermore, the light guide part displaced by the photomechanical drive part is not limited to an optical fiber, but may be a sheet-like optical waveguide. Therefore, the present invention can also be applied to uses for modulating the optical characteristics of the optical waveguide. Further, the photomechanical drive unit 20 shown in FIG. 1 and the

photomechanical drive units

20X and 20Y shown in FIG. 4 may be detachably coupled to the optical fiber 10.

Further, the displaceable driven part is not limited to the light guide part such as an optical fiber or an optical waveguide, but may be a flexible drug introduction tube 100 that can be inserted into a body cavity as shown in FIG. Good. In this case, the X-direction drive photomechanical drive unit 20X and the Y-direction drive photomechanical drive unit 20Y are fused to the distal end portion of the drug introduction tube 100 in the same manner as in the second embodiment, and the drug introduction tube. By driving the distal end portion of 100 to be deformed in the X direction and the Y direction, the drug 101 can be sprayed on the visceral sites aimed from outside the body. In the photomechanical drive unit, the light drive light introduction layer may be fused to the driven unit.

DESCRIPTION OF SYMBOLS 10

Optical fiber

20, 20X, 20Y Photomechanical drive part 21 Photochromic layer 22 Optical drive laser

light introduction layer

40, 40X, 40Y Optical fiber 50 Optical drive light source part 51 Optical drive

laser light source

53a, 53b, 53aX, 53bX, 53aY, 53bY Photoacoustic element (AOM)
60 Control Unit 80 Optical Fiber 90 Probe Optical Laser Light Source 92 Photodetector 100 Drug Introducing Tube

Claims

A photomechanical drive unit that is coupled to a displaceable driven unit and whose spatial structure changes reversibly by photoisomerization,
An optical driving device that displaces the driven part by a change of the photomechanical driving part due to incidence of light driving light to the photomechanical driving part.
The light driving device according to claim 1,
An optical drive device, wherein a plurality of the photomechanical drive units are coupled to the driven unit so as to displace the driven unit in different directions.
The light driving device according to claim 1 or 2,
An optical drive light source unit that emits the optical drive light of at least two wavelengths that reversibly change the photomechanical drive unit;
An optical drive device further comprising: an introduction optical system that transmits the optical drive light from the optical drive light source unit to the photomechanical drive unit.
The light driving device according to claim 3,
The light drive light source unit is a light drive device that switches the light drive light of two wavelengths to the introduction optical system by switching in time series.
The light driving device according to claim 3 or 4,
The optical drive light source unit is an optical drive device in which the intensity or time of the emitted optical drive light of two wavelengths is variable.
The light driving device according to any one of claims 3 to 5,
One of the two-wavelength light driving light has a long wavelength of 400 nm or more and the other has a wavelength shorter than 400 nm.
The light driving device according to any one of claims 3 to 6,
The optical drive light source unit includes an optical drive laser light source, and uses multiple wave different from the fundamental wave emitted from the optical drive laser light source as the optical drive light having two wavelengths.
The light driving device according to any one of claims 3 to 7,
The optical drive device, wherein the introduction optical system is detachable from the optical drive light source unit.
The light driving device according to any one of claims 1 to 8,
The driven unit is a light driving device including a light guide unit.
The light driving device according to any one of claims 3 to 8,
The driven part comprises a light guide part,
An optical driving device further comprising a photodetector for detecting a light response signal from an irradiated portion irradiated with light emitted from the light guide portion.
The light driving device according to claim 10,
The optical drive light source unit is controlled to cause the light drive light to enter the photomechanical drive unit, and further includes a control unit that processes the output of the photodetector in synchronization with the control of the light drive light source unit. Light drive device.
The light driving device according to claim 11,
The said control part is a light drive device which displays the output of the said photodetector corresponding to the displacement of the said light guide part.
The light driving device according to any one of claims 10 to 12,
The light detector is a light driving device that detects scattered light or fluorescence as the light response signal.
The light driving device according to any one of claims 1 to 8,
The optically driven device, wherein the driven part comprises a drug introduction tube.
The light driving device according to claim 1,
The photomechanical drive unit includes a photochromic layer having salicylidene aniline, fulgide, azobenzene, diarylethene, spiropyran, bisimidazole, and derivatives of these molecules.
The light driving device according to claim 15,
The optical driving device, wherein the photochromic layer is bulky and has an optical plane on at least one surface.
The light driving device according to claim 16, wherein
The optical driving device, wherein the surface accuracy of the optical plane is ¼ or more of the wavelength of the optical driving light.
The light driving device according to claim 16 or 17,
An optical driving device in which different optical members are bonded to the optical plane.
The light driving device according to claim 18,
An optical driving device, wherein the optical member is an optical thin film.
The light driving device according to claim 19,
An optical driving device in which the optical thin film is formed by sputtering or vapor deposition.
The light driving device according to any one of claims 1 to 20,
The optical driving device, wherein the driven part and the photomechanical driving part are detachably mounted.