JP5235651B2 - Optical scanning endoscope apparatus, optical scanning endoscope, and optical scanning endoscope processor - Google Patents

Description

  The present invention relates to an optical scanning endoscope apparatus that can detect an actual displacement position of a light transmission path that is displaced to scan illumination light in an optical scanning endoscope.

  An optical scanning endoscope has been proposed (see Patent Document 1). In an optical scanning endoscope, the tip of an optical fiber that transmits illumination light is supported so as to be displaceable, and illumination light is scanned by continuously displacing the tip of the optical fiber.

  Since the distal end of the insertion tube that supports the distal end of the optical fiber is required to be thin, it is difficult to provide a position detection sensor. Therefore, the position of the tip of the displaced optical fiber cannot be accurately detected, and the position is estimated based on the drive signal for mutating the tip of the optical fiber.

When the tip of the optical fiber is accurately displaced along a predetermined displacement path, an accurate position can be estimated. However, it may be difficult to displace along an accurate displacement path due to ambient temperature or vibration at the tip of the optical fiber. In such a case, the displayed image may be distorted.
Japanese Patent No. 3934927

  Therefore, an object of the present invention is to provide an optical scanning endoscope apparatus that can detect the displacement position of the tip of an optical fiber that is displaced for scanning illumination light with a simple configuration.

  The optical scanning endoscope apparatus according to the present invention includes a light source that emits first light, and a first light that is transmitted from the first incident end to the first emission end by transmitting the first light emitted from the light source. Supply light transmission path for emitting the light from the first emission end in the form of a beam, a drive unit for displacing the light in the direction perpendicular to the emission direction of the light transmitted through the first emission end, and the first emission end A first optical filter that is provided on the optical path of the first light emitted from the first optical filter and reflects a part of the first light and transmits a part of the first light; and passes through the first optical filter. An imaging light transmission path for transmitting reflected light or fluorescence from the observation target region to the second incident end and transmitting the incident light to the second output end with respect to the first light applied to the observation target region; Provided on the optical path of the first light reflected by the optical filter, the first light is transmitted at a transmittance according to the incident position of the first light. A second optical filter that passes the second optical filter, and a detection light transmission path that transmits the first light transmitted by the second optical filter from the third incident end to the third outgoing end. A pixel signal in the observation target region is generated based on the first light emitted from the first light or the amount of fluorescence of the first light, and the first light is emitted based on the first light amount emitted from the third emission end. It is characterized in that the position of the end of 1 is detected.

  In addition, the 1st shutter which can switch permeation | transmission toward the observation object area | region and light-shielding of the 1st light which permeate | transmitted the 1st optical filter, and the 1st light reflected by the 1st optical filter A second shutter that can switch between transmission and light shielding toward the third incident end, a light receiving unit that generates a light reception signal according to the amount of light emitted from the second and third emission ends, and light reception A position detection unit that detects the position of the first emission end based on the signal, an image signal processing unit that creates an image of the entire observation target region based on the light reception signal, and shielding of the first light by the first shutter Transmission of the first light by the second shutter and transmission of the first light by the first shutter and execution of the position detection by the position detection unit, blocking of the first light by the second shutter, and image A second control for executing image creation by the signal processing unit; It is preferable that a control unit to return.

  Or the imaging light-receiving part which produces | generates the pixel signal according to the light quantity of the fluorescence by the 1st light or 1st light radiate | emitted from a 2nd output end, and the image of the whole observation object area | region is produced based on a pixel signal An image signal processing unit, a position detection light-receiving unit that generates a displacement position signal corresponding to the amount of first light emitted from the third emission end, and a position of the first emission end based on the displacement position signal It is preferable to provide the position detection part which performs.

  In addition, the light source can separately emit the second and third lights as the first light, and the transmittance of the second light changes along the first direction on the second optical filter. When the transmittance of the third light changes along a second direction different from the first direction on the optical filter, the position detection unit emits the second light to the light source and turns off the third light Based on the amount of the second light emitted from the third emission end, the position of the first emission end along the third direction corresponding to the first direction is detected, and the second light is sent to the light source. The position of the first emission end along the fourth direction corresponding to the second direction based on the amount of the third light emitted from the third emission end when turning off the light and emitting the third light Is preferably detected.

  The light source can separately emit the fourth light different from the first light by using the second and third lights as the first light, and the image signal processing unit causes the light source to emit the second light. 3. When the fourth light is turned off, the second light emitted from the second emission end or the optical information and the light source according to the second light based on the light quantity of the fluorescence by the second light Optical information and light source corresponding to the third light based on the third light emitted from the second emission end or the amount of fluorescence by the third light when the light is emitted and the second and fourth lights are extinguished In response to the fourth light emitted from the second emission end when the fourth light is emitted and the second and third lights are turned off, or the fourth light based on the amount of fluorescence of the fourth light It is preferable to create an entire image of the observation target area based on the optical information.

  In addition, when the scan control unit that controls the drive unit to displace the first emission end along the predetermined displacement path and the detected position of the first emission end are out of the predetermined displacement path It is preferable to include a correction unit that corrects the displacement position of the first emission end so as to return it to a predetermined displacement path.

  In addition, it is preferable to include a condensing lens that condenses the light in the first band transmitted through the second optical filter and emits the light toward the second incident end.

  The optical scanning endoscope according to the present invention supplies the first light transmitted from the first incident end to the first exit end and the transmitted first light in the form of a beam from the first exit end. A transmission path, a drive unit that is displaced in a direction perpendicular to the emission direction of the light transmitted through the first emission end, and a first light path provided on the optical path of the first light emitted from the first emission end. A first optical filter that reflects a part of the first light and transmits a part of the first light; and a first optical filter that passes through the first optical filter and is irradiated on the observation target area. An imaging light transmission path for transmitting reflected light or fluorescence to the second incident end and transmitting the incident light to the second output end, and an optical path for the first light reflected by the first optical filter. A second optical filter that transmits the first light at a transmittance according to the incident position of the first light; and a second optical filter It is characterized in that it comprises a detection light transmission path for transmitting the first light transmitted from the third incident end to the third exit end by.

  The optical scanning endoscope processor of the present invention supplies the first light transmitted from the first incident end to the first emission end and emitted from the first emission end in the form of a beam. A drive unit for displacing the light transmission path and the first outgoing end in a direction perpendicular to the outgoing direction of the light transmitted through the first outgoing end and a first optical path provided on the optical path of the first light emitted from the first outgoing end. The first optical filter that reflects part of the light and transmits part of the first light, and the reflected light in the observation target region with respect to the first light that passes through the first optical filter and is irradiated on the observation target region Alternatively, the first optical filter is provided on the imaging light transmission path that transmits the incident light to the second incident end and transmits the incident light to the second output end and the first light path reflected by the first optical filter. The second optical filter and the second optical filter that transmit the first light with the transmittance according to the incident position of the light The first light is emitted to the first incident end in the optical scanning endoscope having the detection light transmission path that transmits the first light transmitted by the first incident end to the third emission end. A first light source including a light source, generating a pixel signal in the observation target region based on the first light emitted from the second emission end or the amount of fluorescence of the first light, and emitted from the third emission end; The position of the first end is detected on the basis of the amount of the light.

  According to the present invention, the displacement position of the light supply transmission path for scanning illumination light in the optical scanning endoscope can be detected with a simple configuration.

Embodiments of the present invention will be described below with reference to the drawings.
FIG. 1 is an external view schematically showing the external appearance of an optical scanning endoscope apparatus to which the first embodiment of the present invention is applied.

  The optical scanning endoscope apparatus 10 includes an optical scanning endoscope processor 20, an optical scanning endoscope 60, and a monitor 11. The optical scanning endoscope processor 20 is connected to the optical scanning endoscope 60 and the monitor 11.

  In the following description, the exit end (first exit end) of the light supply fiber (not shown in FIG. 1), the entrance end (second entrance end) of the reflection optical fiber (not shown in FIG. 1), The incident end (third incident end) of the position detection fiber (not shown in FIG. 1) is an end portion disposed on the distal end side of the insertion tube 61 of the optical scanning endoscope 60, and supplies light. The incident end of the fiber (first incident end), the exit end of the reflected optical fiber (second exit end), and the exit end of the position detection fiber (third exit end) are the same as those of the optical scanning endoscope processor 20. It is an end portion disposed on the connector 62 to be connected.

  Light to be applied to the observation target area OA is supplied from the optical scanning endoscope processor 20. The supplied light is transmitted to the distal end of the insertion tube 61 through a light supply fiber (supply light transmission path), and is irradiated toward a point in the observation target region. Reflected light at one point on the observation target region irradiated with light is transmitted from the distal end of the insertion tube 61 of the optical scanning endoscope 60 to the optical scanning endoscope processor 20.

  The direction in which the emission end of the light supply fiber faces is changed by a fiber driving unit (not shown in FIG. 1). By changing the direction of the tip, the light irradiated from the light supply fiber is scanned over the observation target region. The fiber driving unit is controlled by the optical scanning endoscope processor 20.

  The optical scanning endoscope processor 20 receives reflected light scattered at the light irradiation position, and generates a pixel signal (optical information) corresponding to the amount of received light. An image signal for one frame is generated by generating a pixel signal for the entire region to be scanned. The generated image signal is transmitted to the monitor 11 and an image corresponding to the image signal is displayed on the monitor 11.

  As shown in FIG. 2, the optical scanning endoscope processor 20 includes a light source unit 30 (light source), a light receiving unit 40 (light receiving unit), a signal processing unit 50 (image signal processing unit), a liquid crystal driving circuit 21, a scan. A drive circuit 22 (position detection unit, scan control unit, correction unit), timing controller 23 (control unit), system controller 24, and the like are provided.

  As will be described later, the light applied to the observation target region from the light source unit 30 and the light for detecting the displacement position of the light supply fiber 63 are supplied to the light supply fiber 63. The liquid crystal driving circuit 21 switches between transmission and light shielding of the first and second liquid crystal shutters 71a and 71b. The scan drive circuit 22 displaces the light supply fiber 63 in the fiber drive unit 72 (drive unit).

  The reflected light of the observation target region irradiated with the light is transmitted to the optical scanning endoscope processor 20 by the optical scanning endoscope 60. Further, light for detection corresponding to the position of the light supply fiber 63 is also transmitted to the optical scanning endoscope processor 20 by the optical scanning endoscope 60. The reflected light and the detection light transmitted to the optical scanning endoscope processor 20 are received by the light receiving unit 40.

  The light receiving unit 40 generates a light reception signal corresponding to the amount of light received. The received light signal is transmitted to the signal processing unit 50 as a pixel signal. The received light signal is transmitted to the scan drive circuit 22 as a displacement position signal.

  The signal processing unit 50 stores a pixel signal at an address on the image memory 25 according to a displacement control signal for controlling the displacement position of the emission end of the light supply fiber 63 transmitted from the timing controller 23 to the scan drive circuit 22. To do. When the pixel signal corresponding to the entire observation target region is stored, the signal processing unit 50 performs predetermined signal processing on the pixel signal, and transmits it to the monitor 11 via the encoder 26 as an image signal of one frame.

  As will be described later, the scan drive circuit 22 recognizes the actual displacement path of the emission end of the light supply fiber 63 based on the displacement position signal. When the recognized displacement path deviates from the predetermined displacement path, the fiber driving unit 72 is controlled so as to be displaced along the predetermined displacement path.

  When the optical scanning endoscope processor 20 and the optical scanning endoscope 60 are connected, the light source unit 30 and the light supply fiber 63 provided in the optical scanning endoscope 60 are replaced with the light receiving unit 40 and the reflected optical fiber 64. The (imaging light transmission path) and the position detection fiber 65 are optically connected.

  When the optical scanning endoscope processor 20 and the optical scanning endoscope 60 are connected, the scan driving circuit 22 and the fiber driving unit 72 provided in the optical scanning endoscope 60 are electrically connected. .

  In the light source unit 30, the light receiving unit 40, the signal processing unit 50, the liquid crystal drive circuit 21, the scan drive circuit 22, and the encoder 26, the operation timing of each part is controlled by the timing controller 23. The operation of each part of the timing controller 23 and the optical scanning endoscope apparatus 10 is controlled by the system controller 24. In addition, a user can input a command through the input unit 27 configured by a front panel (not shown) or the like.

  As shown in FIG. 3, the light source unit 30 includes a red light laser 31r, a green light laser 31g, a blue light laser 31b, first and second filters 32a and 32b, a condensing lens 33, a laser driving circuit 34, and the like. Composed.

  The red light laser 31r, the green light laser 31g, and the blue light laser 31b are respectively a red light laser beam (first light and second light), a green light laser beam, and a blue light laser beam (first light and first light). 3 light).

  The first filter 32a is an optical filter that reflects green light in the band emitted by the green light laser 31g and transmits light in other bands. The second filter 32b is an optical filter that reflects the blue light in the band emitted by the blue light laser 31b and transmits the light in the other band.

  In a state where the light supply fiber 63 and the light source unit 30 are connected, the first and second light paths are provided in the optical path for guiding the red light laser beam emitted from the red light laser 31 r to the incident end of the light supply fiber 63. Filters 32a and 32b and a condenser lens 33 are arranged. The first and second filters 32a and 32b are fixed in a state where they are inclined by 45 ° with respect to the optical path of the red laser beam.

  The green light laser 31g is arranged so that the green light laser beam emitted from the green light laser 31g is reflected by the first filter 32a, passes through the second filter 32b, and enters the incident end of the light supply fiber 63.

  The blue light laser 31b is arranged so that the blue light laser beam emitted from the blue light laser 31b is reflected by the second filter 32b and enters the incident end of the light supply fiber 63.

  The blue light laser beam, the green light laser beam, and the red light laser beam are condensed by the condenser lens 33 and enter the incident end of the light supply fiber 63.

  When observing a real-time image near the distal end of the insertion tube 61, the red light laser beam, the green light laser beam, and the blue light laser beam are supplied to the light supply fiber 63 at different timings. The emission of each laser beam, that is, the supply timing to the light supply fiber 63 will be described later.

  The red light laser 31r, the green light laser 31g, and the blue light laser 31b are driven by a laser driving circuit 34. The laser drive circuit 34 controls the timing of light emission and extinction by the timing controller 23.

  Next, the configuration of the optical scanning endoscope 60 will be described in detail. As shown in FIG. 4, the optical scanning endoscope 60 is provided with a light supply fiber 63, a reflected optical fiber 64, a position detection fiber 65, a tip unit 70, and the like.

  A tip unit 70 is disposed at the distal end of the insertion tube 61. The light supply fiber 63, the reflected optical fiber 64, and the position detection fiber 65 (detection light transmission path) are extended from the connector 62 to the tip unit 70.

  As shown in FIG. 5, the tip unit 70 includes first and second liquid crystal shutters 71a and 71b, a fiber driving unit 72, a hollow tube 73, a half mirror 74 (first optical filter), and a position detection filter 75 ( A second optical filter), a condenser lens 76, a mirror 77, and an exit lens 78.

  The hollow tube 73 is formed in a cylindrical shape by a rigid member, and the mounting posture of the hollow tube 73 is adjusted so that the axial direction of the insertion tube 61 and the axial direction of the hollow tube 73 at the distal end are parallel to each other. The

  In the following description, the light emission direction from the emission end when the axial direction of the emission end of the light supply fiber 63 is parallel to the axial direction of the hollow tube 73 is defined as a first direction. An arbitrary direction perpendicular to the first direction is defined as a second direction (second and fourth directions).

  The light supply fiber 63 is supported in the hollow tube 73 via the fiber driving unit 72. Note that the mounting posture of the light supply fiber 63 is adjusted so that the axial direction of the light supply fiber 63 is parallel to the first direction before the light supply fiber 63 is displaced by the fiber driving unit 72.

  As shown in FIG. 6, the fiber drive part 72 is formed by a fiber support part 72s and a bent part 72b. The bent portion 72b has a cylindrical shape, and the light supply fiber 63 is inserted into the cylinder. The light supply fiber 63 is supported by the end portion on the distal end side of the insertion tube 61 of the bent portion 72b by the fiber support portion 72s.

  As shown in FIG. 7, the bending portion 72b is provided with first and second bending sources 72b1 and 72b2. The first and second bending sources 72b1 and 72b2 are two sets of piezoelectric elements, respectively, and expand and contract in the cylindrical axis direction of the bending portion 72 based on the fiber drive signal transmitted from the scan drive circuit 22.

  The two piezoelectric elements constituting the first bending source 72b1 are fixed to the outer peripheral surface of the bent portion 72b so as to sandwich the center of the bent portion 72b while being aligned along the second direction. In addition, the two piezoelectric elements constituting the second bending source 72b2 are arranged along the third direction perpendicular to the first and second directions, and the bending portion 72b sandwiches the center of the cylinder of the bending portion 72b. It is fixed to the outer peripheral surface of the cylinder.

  As shown in FIG. 8, by simultaneously expanding and contracting the two piezoelectric elements constituting the first bending source 72b1 in the opposite directions, the bending portion 72b bends along the second direction. Further, by simultaneously expanding and contracting the two piezoelectric elements constituting the second bending source 72b2 in the opposite directions, the bending portion 72b bends along the third direction.

  The light supply fiber 63 is urged by the bent portion 72b through the fiber support portion 72s and bends in the second and third directions, that is, in two directions perpendicular to the light emission direction from the emission end of the light supply fiber 63. . When the light supply fiber 63 is bent, the emission end of the light supply fiber 63 is displaced.

  In addition, as shown in FIG. 9, the output end of the light supply fiber 63 is driven to vibrate while repeating the increase and decrease in amplitude along the second and third directions. The frequency of vibration is adjusted to be the same in the second and third directions. Also, the amplitude increase time and the decrease time are adjusted so as to coincide with each other in the first and second directions.

  By causing such vibration along the second and third directions, the tip of the light supply fiber 63 is displaced so as to pass through a spiral displacement path (predetermined displacement path) as shown in FIG. Light is scanned over the observation area.

  Note that the position of the emission end of the light supply fiber 63 when the light supply fiber 63 is not bent is determined as the reference point sp. During the period of oscillation from the reference point sp while increasing the amplitude (scanning period in FIG. 9), irradiation of each color light to the observation target region and collection of pixel signals are executed.

  Further, when the displacement is made until the maximum amplitude is reached, scanning for creating one image is finished, and the emission end of the light supply fiber 63 is returned to the reference point sp by oscillating while decreasing the amplitude (see the braking period in FIG. 9). ) A scan for creating the next image is executed again.

  The half mirror 74, the first liquid crystal shutter 71a, and the emission lens 78 are arranged in the light emission direction when the emission end of the light supply fiber 63 is positioned at the reference point sp (see FIG. 5). The half mirror 74 is formed in a plate shape, and is fixed to the hollow tube 73 in a state where the incident surface and the emission surface are inclined by 45 ° with respect to the first direction. The first liquid crystal shutter 71a is fixed to the hollow tube 73 with the light incident surface and the light exit surface being perpendicular to the first direction. The exit lens 78 is fixed to the hollow tube 73 with the optical axis parallel to the first direction.

  The half mirror 74 reflects incident light with a predetermined reflectance of less than 100%, for example, 10%, and transmits 90%. Therefore, 90% of the light amounts of the red light, the green light, and the blue light emitted from the emission end of the light supply fiber 63 are transmitted through the half mirror 74. Further, 10% of the amount of each of the emitted red light, green light, and blue light is reflected by the half mirror 74 in the third direction.

  The red light, green light, and blue light transmitted through the half mirror 74 reach the first liquid crystal shutter 71a. The first liquid crystal shutter 71 a can switch between a light shielding state and a transmission state of incident light based on the control of the liquid crystal driving circuit 21. The switching between the light shielding state and the transmission state of the first liquid crystal shutter 71a will be described later.

  The red light, the green light, and the blue light transmitted through the first liquid crystal shutter 71a are transmitted through the emission lens 78 and emitted toward one point of the observation target region (see FIG. 11). The reflected light at one point of the observation target area OA irradiated with each color light is scattered, and the scattered reflected light enters the tip of the reflected optical fiber 64.

  The optical scanning endoscope 60 is provided with a plurality of reflection optical fibers 64. The incident end of the reflection optical fiber 64 is disposed so as to surround the periphery of the output lens 78. Scattered light at one point on the observation target area OA enters each reflected optical fiber 64.

  The reflected light incident on the reflected optical fiber 64 is transmitted to the exit end of the reflected optical fiber 64. As described above, the reflected optical fiber 64 is connected to the light receiving unit 40 at the emission end. The reflected light transmitted to the reflected optical fiber 64 is emitted toward the light receiving unit 40.

  A hole 73 h is formed in the hollow tube 73 in the direction of light reflection by the half mirror 74. A position detection filter 75, a condensing lens 76, and a second liquid crystal shutter 71b are fixed to the hole 73h.

  The position detection filter 75 is formed in a plate shape, and is fixed so that the surface thereof is parallel to the first and second directions. The condensing lens 76 is fixed so that the optical axis is parallel to the third direction. Further, the incident surface and the emission surface of the second liquid crystal shutter 71b are fixed so as to be parallel to the first and second directions.

  The position detection filter 75 transmits red light and blue light with a transmittance according to the incident position. As shown in FIG. 12, the position detection filter 75 is formed such that the transmittance of red light increases as the position of light irradiation on the position detection filter 75 is displaced in the first direction. In addition, the position detection filter 75 is formed so that the transmittance of the blue light increases as the light irradiation position on the position detection filter 75 is displaced in the second direction.

  The red light and blue light reflected by the half mirror 74 pass through the position detection filter 75 and are collected by the condenser lens 76. A mirror 77 is provided so as to reflect the collected infrared light in the axial direction of the hollow tube 73 outside the hollow tube 73.

  A second liquid crystal shutter 71 b is provided between the condenser lens 76 and the mirror 77. The second liquid crystal shutter 71 b can switch between blocking and transmitting incident light based on the control of the liquid crystal driving circuit 21.

  The incident end of the position detection fiber 65 is arranged in the direction in which the infrared light is reflected by the mirror 77. The red light and blue light incident on the position detection fiber 65 are transmitted to the light receiving unit 40 through the position detection fiber 65.

  As shown in FIG. 13, the light receiving unit 40 includes a collimating lens 41, a light receiver 42, and an A / D converter 43. The plurality of reflection optical fibers 64 and the single position detection fiber 65 are bundled and optically connected to the light receiving unit 40 as a bundle. The collimating lens 41 and the light receiver 42 are arranged in the light emission direction from the emission end of the fiber bundle of the reflected optical fiber 64 and the position detection fiber 65.

  The red light, the green light, and the blue light emitted from the emission end of the fiber bundle of the reflection optical fiber 64 and the position detection fiber 65 are transmitted through the collimator lens 41 and enter the light receiver 42. The light receiver 42 is a photomultiplier tube and generates a light reception signal having a signal intensity corresponding to the amount of received infrared light, green light, and blue light. The received light signal is converted into a digital signal by the A / D converter 43.

  The generation timing of the light reception signal by the light receiving unit 40 is controlled by the timing controller 23 so as to relate to the light emission / extinction timing in the light source unit 30 and the light shielding / transmission timing of the first and second liquid crystal shutters 71a and 71b.

  As shown in FIG. 14, the timing controller 23 causes the light source unit 30 to repeatedly emit red light, green light, and blue light alternately. While the light source unit 30 emits red light, the timing controller 23 causes the light receiving unit 40 to generate a light reception signal twice at different timings (see timings t1 and t2).

  Further, at the time of generation of the first light reception signal during red light emission, that is, at timing t1, the timing controller 23 switches the first liquid crystal shutter 71a to the transmissive state and the second liquid crystal shutter 71b to the light-shielded state. The liquid crystal drive circuit 21 is controlled. Further, the timing controller 23 causes the signal processing unit 50 to receive the generated light reception signal as a pixel signal.

  Further, at the time of generating the second light receiving signal during red light emission, that is, at the timing t2, the timing controller 23 switches the first liquid crystal shutter 71a to the light-shielding state and switches the second liquid crystal shutter 71b to the transmissive state. In addition, the liquid crystal driving circuit 21 is controlled. In addition, the timing controller 23 causes the scan drive circuit 22 to receive the generated light reception signal as a pixel signal.

  While the light source unit 30 emits green light, the timing controller 23 causes the light receiving unit 40 to generate a light reception signal once (see timing t3). Further, at the time of green light emission and light reception signal generation, that is, at the timing t3, the timing controller 23 drives the liquid crystal so that the first liquid crystal shutter 71a is switched to the transmission state and the second liquid crystal shutter 71b is switched to the light shielding state. The circuit 21 is controlled. Further, the timing controller 23 causes the signal processing unit 50 to receive the generated light reception signal as a pixel signal.

  When the light source unit 30 emits blue light, the timing controller 23 causes the light receiving unit 40 to generate a light reception signal twice at different timings (see timings t4 and t5) as in the case of red light emission.

  Further, at the time of generating the first light reception signal during the blue light emission, that is, at the timing t4, the timing controller 23 switches the first liquid crystal shutter 71a to the transmission state and the second liquid crystal shutter 71b to the light shielding state. The liquid crystal drive circuit 21 is controlled. Further, the timing controller 23 causes the signal processing unit 50 to receive the generated light reception signal as a pixel signal.

  Further, at the time of generating the second light reception signal during the blue light emission, that is, at the timing t5, the timing controller 23 switches the first liquid crystal shutter 71a to the light-shielding state and the second liquid crystal shutter 71b to the transmission state. The liquid crystal drive circuit 21 is controlled. In addition, the timing controller 23 causes the scan drive circuit 22 to receive the generated light reception signal as a pixel signal.

  As described above, when the light reception signal used as the pixel signal is generated, the first liquid crystal shutter 71a is transmitted, so that the observation target region OA is irradiated with the light, and the reflected light is incident on the reflection optical fiber 64. By shielding the liquid crystal shutter 71b, the light incident on the position detection fiber 65 is prevented. Therefore, only the reflected light in the observation target area OA irradiated with light is transmitted to the light receiving unit 40.

  On the other hand, when the light reception signal used as the displacement position signal is generated, the first liquid crystal shutter 71a is shielded from light so that the light is prevented from entering the reflection optical fiber 64 and transmitted through the second liquid crystal shutter 71b. Light having an intensity corresponding to the displacement position enters the position detection fiber 65. Therefore, only the light transmitted through the position detection filter 75 is transmitted to the light receiving unit 40.

  As shown in FIG. 15, the signal processing unit 50 includes a selector 51, a red memory 52r, a green memory 52g, a blue memory 52b, a coordinate conversion circuit 53, and an image processing circuit 54.

  The pixel signal output from the A / D converter 43 is transmitted to and stored in any of the red memory 52r, the green memory 52g, and the blue memory 52b. Based on the control of the timing controller 23, the selector 51 transmits the pixel signal received when the red light is emitted (see timing t1 in FIG. 14) to the red memory 52r for storage. Similarly, the selector 51 transmits the pixel signal received when green light is irradiated (see timing t3) to the green memory 52g for storage. Similarly, the selector 51 transmits the pixel signal received when the blue light is irradiated (see timing t4) to the blue memory 52b for storage.

  As shown in FIG. 16, the light irradiated at each point on the scanning path is light of any one color of red, green, and blue. Therefore, each received light signal has a signal intensity corresponding to any of the red light component, the green light component, and the blue light component at the irradiated position.

  For example, the pixel signal generated when red light is irradiated at the first point p1 corresponds to the red light component at the first point p1. Further, the pixel signal generated when the green light is irradiated at the second point p2 corresponds to the green light component at the second point p2. Further, the pixel signal generated when the blue light is irradiated at the third point p3 corresponds to the blue light component at the third point p3.

  On the other hand, a pixel signal corresponding to the green light component and the blue light component at the first point p1 is not generated. Further, the pixel signal corresponding to the red light component and the blue light component at the second point p2 is not generated. Further, the pixel signal corresponding to the red light component and the green light component at the third point p3 is not generated.

  Therefore, as the signal component corresponding to the color different from the color of the light irradiated at each point, the color signal component generated at the adjacent light irradiation point is used for creating an image.

  For example, at the first point p1, the pixel signal actually generated is used as the red light component, and the pixel signal generated at the next green light irradiation point, that is, the second point p2, is used as the green light component. The pixel signal generated at the blue light irradiation point immediately before the first point p1 is used as the blue light component.

  Similarly, at the second point p2, the pixel signal generated at the first point p1 is used as a red light component, and secondly, the pixel signal generated at the point p2 is used as a green light component, The pixel signal generated at the point p3 is used as a blue light component.

  The image memory 25 has a red light storage area 25r, a green light storage area 25g, and a blue light storage area 25b for storing a red light signal component, a green light signal component, and a blue light signal component, respectively (see FIG. 15). ). Note that the red light storage area 25r, the green light storage area 25g, and the blue light storage area 25b have addresses corresponding to respective points to which light is irradiated. That is, an address corresponding to the first point p1 is provided in each storage area 25r, 25g, 25b.

  When the pixel signal is stored in the red memory 52r, the coordinate conversion circuit 53 reads the pixel signal from the red memory 52r, and in the red light storage area 25r, the blue light immediately before the red light irradiation position and the red light irradiation position. Pixel signals are stored in three addresses corresponding to the light irradiation position and the green light irradiation position immediately behind the red light irradiation position. The light irradiation position is estimated based on the above-described displacement control signal.

  For example, when the pixel signal generated at the first point p1 is stored in the red memory 52r, the pixel signal is read from the red memory 52r by the coordinate conversion circuit 53, and the first point p1 in the red light storage region 25r, The pixel signal generated at the first point p1 is stored at addresses corresponding to the zeroth point p0 and the second point p2 (see FIG. 16), which are the irradiation points immediately before the first point p1. The

  Similarly, when the pixel signal is stored in the green memory 52g, the coordinate conversion circuit 53 reads the pixel signal from the green memory 52g, and in the green light storage area 25g, one of the green light irradiation position and the green light irradiation position. Pixel signals are stored in three addresses corresponding to the irradiation position of the blue light immediately after the irradiation position of the previous red light and the irradiation position of the green light.

  For example, when the pixel signal generated at the second point p2 is stored in the green memory 52g, the pixel signal is read from the green memory 52g by the coordinate conversion circuit 53, and the first point p1 in the green light storage region 25g is read. The pixel signal generated at the second point p2 is stored at addresses corresponding to the second point p2 and the third point p3.

  Similarly, when the pixel signal is stored in the blue memory 52b, the coordinate conversion circuit 53 reads the pixel signal from the blue memory 52b, and one of the blue light irradiation position and the blue light irradiation position in the blue light storage area 25b. Pixel signals are stored in three addresses corresponding to the irradiation position of the previous green light and the irradiation position of the red light immediately after the irradiation position of the blue light.

  For example, when the pixel signal generated at the third point p3 is stored in the blue memory 52b, the pixel signal is read from the blue memory 52b by the coordinate conversion circuit 53, and the second point p2 in the blue light storage region 25b, The pixel signal generated at the third point p3 is stored at the address corresponding to the third point p3 and the fourth point p4, which is the irradiation point immediately behind the third point p3.

  When the pixel signals at each irradiation point from the scanning start point to the scanning end point are stored in the image memory 25, the pixel signals at all addresses in all the storage areas 25r, 25g, and 25b are subjected to image processing as an image signal of one frame. Read to circuit 54.

  The image processing circuit 54 performs predetermined signal processing on the image signal. The image signal subjected to the predetermined signal processing is transmitted to the encoder 26 as described above.

  As described above, the displacement position signal output from the A / D converter 43 is transmitted to the scan drive circuit 22. The displacement position signal is used for correcting the displacement position of the light supply fiber 63 as described below.

  In order to create an image with high reproducibility, it is necessary that the emission end of the light supply fiber 63 be displaced along the spiral displacement path described above. However, it may deviate from a predetermined spiral displacement path due to the influence of external factors such as temperature and vibration around the fiber driving unit 72.

  For example, as shown in FIG. 17, the first mutation path (refer to the solid line) that is not sufficiently displaced in the third direction and is shifted in the third direction from the predetermined spiral displacement path (refer to the two-dot chain line). May pass.

  The scan drive circuit 22 detects the actual displacement position of the emission end of the light supply fiber 63 based on the continuously received displacement position signal. Further, the scan drive circuit 22 determines whether or not the scan drive circuit 22 deviates from a predetermined spiral displacement path based on a continuously displaced displacement position. If there is a deviation from the spiral displacement path, the scan drive circuit 22 generates a fiber drive signal adjusted to correct the deviation and transmits it to the fiber drive unit 72.

  As described above, according to the optical scanning endoscope apparatus of the first embodiment, the displacement position of the emission end of the light supply fiber 63 can be detected. In addition, when the displacement path based on the displacement position is deviated from the predetermined displacement path, it is possible to correct the displacement path along the predetermined displacement path, so that distortion of the displayed image can be reduced.

  Further, since imaging and position detection can be performed by the single light receiver 41, the configuration can be simplified and the manufacturing cost can be reduced.

  In the optical scanning endoscope apparatus according to the first embodiment, it is difficult to detect a position at the moment when light for photographing is irradiated, but a position adjacent to the light irradiation position for photographing is detected. Therefore, it is possible to approximately detect the actual light irradiation position.

  Next, an optical scanning endoscope apparatus to which the second embodiment of the present invention is applied will be described. In the second embodiment, the configurations of the tip unit and the optical scanning endoscope processor are different from those of the first embodiment. The optical scanning endoscope according to the second embodiment will be described focusing on the differences from the first embodiment. In addition, the same code | symbol is attached | subjected to the site | part which has the same function as 1st Embodiment.

  As shown in FIG. 18, the optical scanning endoscope processor 200 includes a light source unit 30, an imaging light receiving unit 40 (imaging light receiving unit), a signal processing unit 50, and a scan drive circuit 22 as in the first embodiment. , A timing controller 23, a system controller 24, and the like are provided. Unlike the first embodiment, the liquid crystal driving circuit is not provided, and the position detection light receiving unit 80 (position detection light receiving unit) is provided.

  As in the first embodiment, when the optical scanning endoscope processor 200 and the optical scanning endoscope 60 are connected, the light source unit 30 and the light supply fiber 63 are optically connected, and the scan drive circuit 22 is connected. And the fiber driving unit 72 are electrically connected.

  Unlike the first embodiment, when the optical scanning processor 200 and the optical scanning endoscope 60 are connected, the imaging light receiving unit 40 and the reflected optical fiber 64 are optically connected, and the position detecting unit 80 and the position detecting fiber 65 are optically connected. Connected to.

  The configuration and function of the light source unit 30 are the same as those in the first embodiment. Therefore, based on the control of the timing controller 23, the red light, the green light, and the blue light can be switched on and off.

  The portions other than the tip unit 700 in the optical scanning endoscope 60 and the configuration of the emission ends of the reflected optical fiber 64 and the position detection fiber 65 are the same as those in the first embodiment.

  As shown in FIG. 19, the tip unit 700 includes a hollow tube 73, a fiber driving unit 72, a half mirror 74, a position detection filter 75, a condensing lens 76, a mirror 77, and an exit, as in the first embodiment. A lens 78 is provided. Unlike the first embodiment, the first and second liquid crystal shutters are not provided.

  The arrangement and functions of the hollow tube 73, the fiber driving unit 72, the half mirror 74, the position detection filter 75, the condenser lens 76, the mirror 77, and the emission lens 78 are the same as those in the first embodiment.

  Accordingly, when light is emitted from the emission end of the light supply fiber 63, 90% of the total light quantity is transmitted through the half mirror 74 and the emission lens 78 and irradiated onto the observation target area OA. The reflected light of the irradiated light enters the incident end of the reflected optical fiber 64 and is transmitted to the imaging light receiving unit 40.

  When light is emitted from the emission end of the light supply fiber 63, 10% of the total light amount is reflected by the half mirror 74 and reaches the position detection filter 75. As in the first embodiment, the red light irradiation position that reaches the position detection filter 75 is transmitted with a larger transmittance as the position is displaced in the first direction, and the blue light irradiation position that reaches the position detection filter 75 is The larger the displacement in the second direction, the greater the transmittance (see FIG. 12). The red light and blue light transmitted through the position detection filter 75 are incident on the incident end of the position detection fiber 65 and transmitted to the position detection light receiving unit 80.

  The configuration and function of the imaging light receiving unit 40 are the same as those of the light receiving unit of the first embodiment. Therefore, a pixel signal corresponding to the amount of reflected light transmitted by the reflected optical fiber 64 is generated. Similar to the first embodiment, the generated pixel signal has a signal intensity corresponding to the light amount of any one of red light, green light, and blue light. Note that, unlike the first embodiment, the imaging light receiving unit 40 is not connected to the scan drive circuit 22. The pixel signal is converted into a digital signal and then transmitted to the signal processing unit 50.

  As shown in FIG. 20, the position detection unit 80 includes a collimating lens 81, a light receiver 82, and an A / D converter 83. Red light, green light, and blue light emitted from the emission end of the position detection fiber 65 pass through the collimator lens 81 and enter the light receiver 82. The light receiver 82 is a photomultiplier tube and generates a displacement position signal having a signal intensity corresponding to the amount of received infrared light, green light, and blue light. The displacement position signal is converted into a digital signal by the A / D converter 83. The displacement position signal converted into the digital signal is transmitted to the scan drive circuit 22.

  The generation timing of the pixel signal by the imaging light-receiving unit 40 and the generation timing of the displacement position signal by the position detection light-receiving unit 80 are controlled by the timing controller 23 so as to be related to the light emission / light-off timing in the light source unit 30.

  As shown in FIG. 21, the timing controller 23 causes the light source unit 30 to repeatedly emit red light, green light, and blue light alternately. In different periods when the light source unit 30 emits red light, the timing controller 23 causes the imaging light receiving unit 40 to generate a pixel signal (see timing t1) and the position detection light receiving unit 80 to generate a displacement position signal (see timing t2). .

  While the light source unit 30 emits green light, the timing controller 23 causes the imaging light receiving unit 40 to generate a pixel signal (see timing t3).

  The timing controller 23 outputs the pixel signal to the imaging light receiving unit 40 (see timing t4) and the position detection light receiving unit 80 to the displacement position in the same period as when the light source unit 30 emits blue light. A signal is generated (see timing t5).

  The configuration and function of the signal processing unit 50 are also the same as those in the first embodiment. Therefore, the signal processing unit 50 stores the pixel signal at three addresses determined for the irradiation positions in the storage areas 25r, 25g, and 25b of the image memory 25. Similar to the first embodiment, an image signal of one frame is formed by storing pixel signals at each irradiation point from the scanning start point to the scanning end point.

  The displacement position signal is transmitted to the scan drive circuit 22. As in the first embodiment, based on the displacement position signal, the scan drive circuit 22 detects the displacement position of the emission end of the light supply fiber 63 and corrects the displacement path.

  As described above, the optical scanning endoscope apparatus according to the second embodiment can detect the displacement position of the emission end of the light supply fiber 63 and can correct the displacement of the displacement path. . Further, unlike the first embodiment, the first unit 700 is not provided with the first and second liquid crystal shutters 71a and 71b, so that the configuration can be simplified and the manufacturing cost can be reduced.

  Further, as in the first embodiment, it is difficult to detect the position at the moment when the light for shooting is irradiated, but it is possible to detect a position adjacent to the irradiation position of the light for shooting. It is possible to approximately detect the actual light irradiation position.

  In the first and second embodiments, the first and second directions, which are directions in which the transmittance is changed by the position detection filter 75, are perpendicular to each other. However, the transmittance changes in the displacement direction of the reflected light by the half mirror 74 when the emission end is displaced in the bending direction by the first and second bent portions 72b1 and 72b2, thereby driving the light supply fiber 63. This is preferable.

  In the first and second embodiments, the transmittance is changed along two different directions in the position detection filter 75, but any number of directions or one direction may be used. In the case of one direction, only the displacement amount in the direction corresponding to that direction can be detected. However, in the conventional optical scanning endoscope apparatus, the position of the emission end of the light supply fiber 63 is estimated based only on the fiber drive signal for driving the light supply fiber 63. Therefore, by using an accurate position in one direction, the position estimation accuracy is improved as compared with the conventional optical scanning endoscope apparatus.

  In the first and second embodiments, the light whose transmittance varies depending on the position irradiated on the position detection filter 75 is red light and blue light, but other bands emitted from the light source unit 30. It may be light.

  Further, in the first and second embodiments, when the displacement path of the emission end of the light supply fiber 63 is deviated from the predetermined spiral displacement path, it is corrected so as to return to the predetermined spiral displacement path. There is no need to modify it. As described above, if the displacement position is obtained, it can be used for image processing or the like.

  In the first and second embodiments, the emission end of the light supply fiber 63 is displaced along the spiral displacement path, but the displacement path is not limited to the spiral. It is possible to obtain the same effect as the present embodiment even if it is displaced along another displacement path.

  In the first and second embodiments, red light, green light, and blue light are emitted from the light source unit 30, but excitation light that excites fluorescence in the living tissue is emitted. May be. The autofluorescence incident on the incident end of the reflected optical fiber 64 may be transmitted to the light receiving unit 40 and the imaging light receiving unit 40 to form an image based on the autofluorescence.

  In the optical scanning endoscope apparatus according to the first and second embodiments, a laser is used as a light source that emits red light, green light, and blue light. However, other types of light sources are used. Also good. However, in the optical scanning endoscope, it is preferable that light is applied to one minimal point in the observation target region, and it is preferable to use a laser to emit light having strong directivity.

1 is an external view schematically showing an external appearance of an optical scanning endoscope apparatus to which a first embodiment of the present invention is applied. FIG. It is a block diagram which shows roughly the internal structure of the optical scanning type endoscope processor of 1st Embodiment. It is a block diagram which shows roughly the internal structure of the light source unit of 1st, 2nd embodiment. It is a block diagram which shows roughly the internal structure of the optical scanning endoscope of 1st, 2nd embodiment. FIG. 3 is a structural diagram schematically showing an internal configuration of a tip unit according to the first embodiment. It is sectional drawing along the axial direction of the light supply fiber which shows the structure of the fiber drive part of 1st, 2nd embodiment. It is the external view which looked at the fiber drive part of 1st, 2nd embodiment from the output end side of the light supply fiber. It is a perspective view of the fiber drive part of 1st, 2nd embodiment. It is a graph which shows the displacement amount along the 2nd, 3rd direction of the output end of the light supply fiber of 1st, 2nd embodiment. It is a displacement path | route of the light supply fiber driven by the fiber drive part of 1st, 2nd embodiment. It is a figure for demonstrating the state in which light radiate | emits from an output lens in 1st, 2nd embodiment. It is a graph which shows the optical characteristic of the position detection filter of 1st, 2nd embodiment. It is a block diagram which shows roughly the internal structure of the light-receiving unit of 1st Embodiment. 6 is a timing chart showing the operating states of the light source unit, the light receiving unit, the first and second liquid crystal shutters, and the signal receiving unit or the scan drive circuit in the first embodiment. It is a block diagram which shows roughly the internal structure of the signal processing unit of 1st, 2nd embodiment. In 1st, 2nd embodiment, it is a figure which shows the light irradiated at each point on a scanning path | route. It is a figure which shows the example of the 1st displacement path | route which shifted | deviated from the spiral type displacement path | route. It is a block diagram which shows roughly the internal structure of the optical scanning endoscope processor of 2nd Embodiment. It is a block diagram which shows roughly the internal structure of the front-end | tip unit of 2nd Embodiment. It is a block diagram which shows roughly the internal structure of the position detection light-receiving unit of 2nd Embodiment. In 2nd Embodiment, it is a timing chart which shows the operating state of a light source unit, an imaging light-receiving unit, and a position detection light-receiving unit.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Optical scanning endoscope apparatus 20, 200 Optical scanning endoscope processor 21 Liquid crystal drive circuit 22 Scan drive circuit 23 Timing controller 25 Image memory 25r, 25g, 25b Red light storage area, Green light storage area, Blue light storage Area 30 Light source unit 40 Light receiving unit, imaging light receiving unit 42 Light receiver 50 Signal processing unit 51 Selector 52r, 52g, 52b Red memory, green memory, blue memory 53 Coordinate conversion circuit 60 Optical scanning endoscope 63 Light supply fiber 64 Reflection Optical fiber 65 Position detection fiber 70, 700 Tip unit 71a, 71b First and second liquid crystal shutters 74 Half mirror 75 Position detection filter 80 Position detection light receiving unit 82 Light reception

Claims (9)

A light source that emits first light;
Supply light transmission for transmitting the first light emitted from the light source from a first incident end to a first emission end and emitting the transmitted first light in a beam form from the first emission end. Road,
A drive unit that displaces the first emission end in a direction perpendicular to the emission direction of the transmitted light;
A first optical filter provided on an optical path of the first light emitted from the first emission end, reflects a part of the first light, and transmits a part of the first light. When,
Reflected light or fluorescence in the observation target region with respect to the first light that passes through the first optical filter and is irradiated on the observation target region is incident on the second incident end, and the incident light is output to the second emission. An imaging light transmission path that transmits to the end;
A second optical filter provided on an optical path of the first light reflected by the first optical filter and transmitting the first light at a transmittance according to an incident position of the first light; ,
A detection light transmission path for transmitting the first light transmitted by the second optical filter from a third incident end to a third emission end,
Based on the amount of fluorescence emitted by the first light or the first light emitted from the second emission end, a pixel signal in the observation target region is generated,
An optical scanning endoscope apparatus, wherein the position of the first end portion is detected based on the amount of the first light emitted from the third emission end. A first shutter capable of switching between transmission and shading of the first light transmitted through the first optical filter toward the observation target region;
A second shutter capable of switching between transmission and shielding of the first light reflected by the first optical filter toward the third incident end;
A light receiving unit that generates a light reception signal according to the amount of light emitted from the second and third emission ends;
A position detector for detecting a position of the first emission end based on the light reception signal;
An image signal processing unit that creates an image of the entire observation target region based on the received light signal;
A first control for executing shielding of the first light by the first shutter, transmission of the first light by the second shutter, and position detection by the position detector; and the first shutter A controller that repeats the transmission of the first light by the first light, the shielding of the first light by the second shutter, and the second control for causing the image signal processing unit to create the image. The optical scanning endoscope apparatus according to claim 1. An imaging light-receiving unit that generates a pixel signal according to the amount of fluorescence emitted by the first light or the first light emitted from the second emission end;
An image signal processing unit that creates an image of the entire observation target region based on the pixel signal;
A position detection light-receiving unit that generates a displacement position signal according to the amount of the first light emitted from the third emission end;
The optical scanning endoscope apparatus according to claim 1, further comprising: a position detection unit that detects a position of the first emission end based on the displacement position signal. The light source can separately emit second and third light as the first light,
The transmittance of the second light varies along a first direction on the second optical filter, and the second light varies along a second direction different from the first direction on the second optical filter. The transmittance of the third light changes,
The position detector is configured to output the first light based on a light amount of the second light emitted from the third emission end when the light source emits the second light and turns off the third light. When the position of the first emission end along a third direction corresponding to the direction of the first light is detected and the second light is turned off by the light source and the third light is emitted, the third emission is performed. The position of the first emission end along a fourth direction corresponding to the second direction is detected based on the amount of the third light emitted from the end. The optical scanning endoscope apparatus according to claim 3. The light source is capable of separately emitting second and third lights as the first light and a fourth light different from the first light,
The image signal processing unit emits the second light emitted from the second emission end or the second light when the second light is emitted from the light source and the third and fourth lights are turned off. Optical information corresponding to the second light based on the amount of fluorescence by the light, and the second emission when the third light is emitted to the light source and the second and fourth lights are turned off. Optical information corresponding to the third light based on the amount of the fluorescence emitted by the third light or the third light emitted from the end, and the second and second light emitted from the light source to the light source. When the third light is turned off, the fourth light emitted from the second emission end or the optical information corresponding to the fourth light based on the amount of the fluorescence by the fourth light. An entire image of the observation target region is created. Item 4. The optical scanning endoscope apparatus according to Item 3. A scan control unit that controls the drive unit to displace the first emission end along a predetermined displacement path;
A correction unit that corrects the displacement position of the first emission end to return to the predetermined displacement path when the detected position of the first emission end is out of the predetermined displacement path; The optical scanning endoscope apparatus according to any one of claims 1 to 5, further comprising:   The condensing lens which condenses the light of the 1st zone which permeate | transmitted the said 2nd optical filter, and radiate | emits it toward the said 2nd incident end is provided. 7. The optical scanning endoscope apparatus according to claim 6. A supply light transmission path for transmitting the first light from the first incident end to the first emission end and emitting the transmitted first light in a beam form from the first emission end;
A drive unit that displaces the first emission end in a direction perpendicular to the emission direction of the transmitted light;
A first optical filter provided on an optical path of the first light emitted from the first emission end, reflects a part of the first light, and transmits a part of the first light. When,
Reflected light or fluorescence in the observation target region with respect to the first light that passes through the first optical filter and is irradiated on the observation target region is incident on the second incident end, and the incident light is output to the second emission. An imaging light transmission path that transmits to the end;
A second optical filter provided on an optical path of the first light reflected by the first optical filter and transmitting the first light at a transmittance according to an incident position of the first light; ,
An optical scanning endoscope comprising: a detection light transmission path configured to transmit the first light transmitted by the second optical filter from a third incident end to a third emission end. A light source that emits the first light is provided at the first incident end in the optical scanning endoscope according to claim 8,
The pixel signal in the observation target region based on the first light emitted from the second emission end in the optical scanning endoscope according to claim 8 or the light quantity of the fluorescence by the first light. Produces
The light of the optical scanning endoscope according to claim 8, wherein a position of the first emission end is detected based on a light amount of the first light emitted from the third emission end. Scanning endoscope processor.

Images