JP2008142346A - Fluorescence endoscope - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a fluorescence endoscope observing the internal circumferential face of a luminal subject in a plurality of directions at a fixed distance using fluorescence in fluorescence observation using a side-view type endoscope. <P>SOLUTION: This fluorescence endoscope is characterized in having: an insertion portion to be inserted into a body cavity 3; a balloon 15 positioning the insertion portion relative to the body cavity 3 in the radial direction of the insertion portion 5 by coming into contact with the inner wall of the body cavity 3 positioned radially to the insertion portion 5; light emission/guide sections 17 and 19 emitting an excitation light irradiated to the inner wall, radially outward the insertion portion, and guiding the fluorescence generated from the inner wall and transmitting through the balloon 15, to the inside of the insertion portion from a plurality of different radial directions of the insertion portion; an image pickup section 21 capturing the fluorescence introduced from the light emission/guide sections 17 and 19; and a moving section 23 moving the image pickup section 21 along the optical axis of the fluorescence entering the image pickup section 21 based on a distance between the contact face of the balloon 15 with the inner wall and the insertion portion 5. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a fluorescence endoscope.

  In recent years, techniques have been developed for diagnosing a disease state such as cancer in a living tissue using a drug that accumulates in a diseased part such as cancer and emits fluorescence by excitation light. In particular, by irradiating the living body with excitation light from a fluorescence endoscope or the like in a state where the drug is injected into the living body, the fluorescence emitted from the drug accumulated in the diseased part by the fluorescence endoscope or the like is detected as a two-dimensional image, A technique for diagnosing a diseased part from the detected fluorescence intensity is known.

  However, since the intensity of the detected fluorescence is inversely proportional to the square of the distance between the detection unit and the diseased part, it is difficult to diagnose the diseased part from the detected fluorescence intensity unless the distance is kept constant. there were. Also, in the other diseased part diagnosis method using an endoscope, it is important to keep the distance between the diseased part and the detection part at a predetermined distance for accurate diagnosis. Therefore, various techniques for maintaining a constant distance between a diseased part and a detection part in an endoscope have been proposed (for example, see Patent Document 1 or 2).

  In the techniques described in Patent Documents 1 and 2, by positioning the endoscope with respect to the lumen, the distance between the predetermined region of the lumen and the detection unit of the endoscope is kept constant, and the predetermined region Is disclosed.

Moreover, when inspecting a vascular tissue from the inside of a blood vessel, a technique for performing an inspection by inserting a probe into the blood vessel and irradiating the vascular tissue with illumination light from the probe is known (for example, Patent Document 3). reference.).
In this technique, a balloon is provided at the tip of the probe. When performing the above-described examination, the balloon was inflated and brought into close contact with the blood vessel wall.

Furthermore, in an endoscope that performs diagnosis using fluorescence, a distance measuring unit that generates a distance signal corresponding to the distance between the excitation light irradiation unit and the subject, and a fluorescence signal or a fluorescence image signal based on the distance signal There is also known a technique for diagnosing a lesion using a characteristic value calculating means for correction (see, for example, Patent Document 4).
According to this technique, it is disclosed that the lesioned part is diagnosed by the distance measuring unit and the characteristic value calculating unit without being affected by the distance between the irradiation unit and the subject.
JP 2001-275842 A Japanese Patent Laid-Open No. 2002-5822 JP 2002-219130 A JP 2006-43002 A

  However, in the techniques described in Patent Document 1 and Patent Document 2, when the lumen located in the radial direction of the insertion portion is observed in a plurality of directions, the inner peripheral surface of the lumen is divided into a plurality of regions, It was necessary to repeatedly perform endoscope positioning and lumen observation for each region. Therefore, there has been a problem that the operation of the endoscope becomes complicated.

  Further, with the technique described in Patent Document 3, the distance between the surface of the lumen and the detection unit of the endoscope cannot be kept constant. Therefore, the technique described in Patent Document 3 has a problem that it is difficult to perform fluorescence observation that requires the above-mentioned distance to be kept constant. Also, since the inner diameter of the lumen is not constant, the distance between the surface of the lumen and the detection part of the endoscope can be kept constant by changing the inner diameter of the lumen when the observation position is changed. There wasn't.

  Further, in the technique described in Patent Document 4, when the lumen located in the radial direction of the insertion portion is observed in a plurality of directions, the inner peripheral surface of the lumen is divided into a plurality of regions, Therefore, it has been necessary to repeatedly correct the fluorescence signal and the fluorescence image signal by the distance measuring means and the characteristic value calculating means. Therefore, there has been a problem that processing in the endoscope becomes complicated.

  The present invention has been made to solve the above-described problem, and in fluorescence observation using a side-view endoscope, even if the observation position is changed in the forward / backward direction, It is an object of the present invention to provide a fluorescence endoscope capable of observing fluorescence on a peripheral surface at a certain distance in a plurality of directions.

In order to achieve the above object, the present invention provides the following means.
The present invention positions the insertion portion relative to the body cavity in the radial direction of the insertion portion by contacting the insertion portion inserted into the body cavity and the inner wall of the body cavity located in the radial direction of the insertion portion. Excitation light emitted to the balloon and the inner wall is emitted radially outward of the insertion portion, and fluorescence generated from the inner wall and transmitted through the balloon is emitted from a plurality of different radial directions of the insertion portion. Between the light emission introduction part introduced into the insertion part, the imaging part for imaging fluorescence introduced from the light emission introduction part, the contact surface of the balloon with the inner wall, and the insertion part Provided is a fluorescence endoscope provided with a moving unit that moves the imaging unit along an optical axis of fluorescence incident on the imaging unit based on a distance.

According to the present invention, the balloon comes into contact with the inner wall located in the radial direction of the insertion portion, thereby positioning the insertion portion at the approximate center of the body cavity. That is, the balloon can equalize the distance between all the partial regions of the inner wall of the body cavity in the radial direction of the insertion portion and the insertion portion.
The excitation light emitted radially outward of the insertion portion from the light emission introduction portion is irradiated to the inner wall of the body cavity whose distance from the insertion portion is equalized by the balloon, and fluorescence is emitted from the inner wall irradiated with the excitation light. Generated. Fluorescence generated from the inner wall of the body cavity passes through the balloon and goes inward in the radial direction of the insertion portion, and is introduced into the insertion portion by the light emission introduction portion. Here, when fluorescence is generated from a plurality of locations on the inner wall of the body cavity, each fluorescence is introduced into the insertion portion from a plurality of different radial directions of the insertion portion. Then, the fluorescence introduced from the light emission introduction part into the insertion part is imaged by the imaging part.

At this time, the imaging unit can be moved along the optical axis of fluorescence incident on the imaging unit by the moving unit, so that the distance from the inner wall of the body cavity to the imaging unit can be kept constant.
Therefore, the distance between the inner wall of the body cavity located in a plurality of different radial directions of the insertion portion and the imaging portion can be made equal by the balloon and the moving portion. For example, even when the observation position is changed along the advancing / retreating direction of the insertion portion, the distance from the inner wall of the body cavity located in a plurality of different radial directions of the insertion portion to the imaging portion is kept at a predetermined constant distance, In this state, the fluorescence generated from the inner wall of the body cavity can be observed.

  In the above invention, the light emitting and introducing portion reflects the irradiation light that emits the excitation light radially outward of the insertion portion and the fluorescence generated from the inner wall toward the central axis direction of the insertion portion. In addition, a reflection unit arranged to be rotatable around the central axis may be provided, and the imaging unit may image the fluorescence reflected from the reflection unit.

According to the present invention, the excitation light is emitted radially outward of the insertion portion from the irradiation portion provided in the light emission introduction portion, and is applied to the inner wall of the body cavity that is in contact with the balloon. Fluorescence is generated from the inner wall of the body cavity irradiated with the excitation light, and the fluorescence is introduced into the insertion portion.
The fluorescence introduced into the insertion portion is reflected toward the central axis of the insertion portion by the reflection portion provided in the light emission introduction portion. In addition, since the reflecting portion is disposed so as to be rotatable around the central axis, the fluorescence generated from the inner wall of the body cavity located in a plurality of different radial directions of the insertion portion is reflected toward the central axis direction of the insertion portion.

The fluorescence reflected from the reflection unit is imaged by the imaging unit, and the imaging unit can acquire an image of the partial region of the inner wall located in the radial direction of the insertion unit. Therefore, according to the present invention, it is possible to image fluorescence generated from the inner walls of the body cavity located in a plurality of different radial directions of the insertion portion.
Note that the reflection unit may reflect only the fluorescence generated from the inner wall, or may transmit light having a wavelength unnecessary for diagnosis of a body cavity (for example, excitation light emitted from the irradiation unit).

In the said invention, the rotation drive part which rotates the said reflection part may be provided.
According to the present invention, by rotating the reflecting portion, the fluorescence generated from the partial regions of the inner wall of the body cavity located in a plurality of different radial directions of the insertion portion is reflected toward the imaging portion, and the fluorescence is reflected on the imaging portion. An image can be taken.

In the above invention, the light emission introduction portion is disposed at least inside the distal end portion of the insertion portion, and is provided in the rotation portion, and a rotation portion that is rotatably arranged around the central axis of the insertion portion. An irradiation unit that emits the excitation light radially outward of the insertion unit; and a reflection unit that is provided in the rotation unit and reflects fluorescence generated from the inner wall toward the central axis direction. The imaging unit may be provided in the rotating unit and may image fluorescence reflected from the reflecting unit.
The rotating unit may rotate only the reflecting unit, or rotate the light emitting introduction unit including the reflecting unit, for example, a tube-shaped unit including the light emitting introducing unit, You may arrange | position so that rotation with respect to an insertion part is possible.

According to the present invention, the excitation light is emitted radially outward of the insertion portion from the irradiation portion provided in the rotating portion, and is irradiated on the inner wall of the body cavity that is in contact with the balloon. Fluorescence is generated from the inner wall of the body cavity irradiated with the excitation light, and the fluorescence passes through the insertion portion and is introduced into the rotating portion. The fluorescence introduced into the inside of the rotating part is reflected toward the central axis of the insertion part by the reflecting part provided in the rotating part. The fluorescence reflected from the reflection unit is imaged by the imaging unit, and the imaging unit acquires an image of the partial region of the inner wall located in the radial direction of the insertion unit.
Here, since the rotation part is arranged inside the insertion part so as to be rotatable around the central axis of the insertion part, fluorescence can be introduced into the insertion part from a plurality of different radial directions of the insertion part. It is. Therefore, according to the present invention, it is possible to image fluorescence generated from the inner walls of the body cavity located in a plurality of different radial directions of the insertion portion.

  In the above invention, the light emission introduction portion is disposed at least inside the distal end portion of the insertion portion, and is provided in the rotation portion, and a rotation portion that is rotatably arranged around the central axis of the insertion portion. And an irradiation unit that emits the excitation light radially outward of the insertion unit, and the imaging unit may image the fluorescence introduced into the rotation unit.

According to the present invention, the excitation light is emitted radially outward of the insertion portion from the irradiation portion provided in the rotating portion, and is irradiated on the inner wall of the body cavity that is in contact with the balloon. Fluorescence is generated from the inner wall of the body cavity irradiated with the excitation light, and the fluorescence passes through the insertion portion and is introduced into the rotating portion. The fluorescence introduced into the rotating unit is imaged by an imaging unit provided in the rotating unit.
Here, since the rotation part is arranged inside the insertion part so as to be rotatable around the central axis of the insertion part, it is possible to introduce fluorescence into the insertion part from a plurality of different radial directions of the insertion part. It is. Therefore, according to the present invention, it is possible to image fluorescence generated from the inner walls of the body cavity located in a plurality of different radial directions of the insertion portion.

  In the above invention, the light emitting and introducing portion reflects the irradiation light that emits the excitation light radially outward of the insertion portion and the fluorescence generated from the inner wall toward the central axis direction of the insertion portion. A conical mirror that captures the fluorescence reflected from the conical mirror.

According to the present invention, the excitation light is emitted from the irradiating portion radially outward of the insertion portion, and is irradiated on the inner wall of the body cavity that is in contact with the balloon. Fluorescence is generated from the inner wall of the body cavity irradiated with the excitation light, and the fluorescence is introduced from the light emission introduction portion into the insertion portion.
The fluorescence introduced into the light emission introducing portion is reflected toward the central axis of the insertion portion by a conical mirror provided in the light emission introduction portion. The fluorescence reflected from the conical mirror is imaged by the imaging unit, and the imaging unit can obtain images of partial regions of the inner wall located in a plurality of different radial directions of the insertion unit. Therefore, according to the present invention, it is possible to image fluorescence generated from the inner walls of the body cavity located in a plurality of different radial directions of the insertion portion.

  In the above invention, an insertion length measurement unit for measuring the insertion length of the insertion unit with respect to the body cavity, an imaging signal output from the imaging unit, and a signal relating to the insertion length output from the insertion length measurement unit And an image processing unit that performs the expansion processing of the imaging signal based on the above.

According to the present invention, the movement distance of the imaging unit relative to the body cavity is measured by the insertion length measurement unit. A signal related to the insertion length output from the insertion length measurement unit is input to the image processing unit. The image processing unit receives the fluorescence image signal output from the imaging unit and the signal related to the insertion length output from the insertion length measurement unit, and processes the imaging signal based on both signals.
For example, when the imaging signal output from the imaging unit is a signal related to the fluorescence image of the entire inner peripheral surface of the inner wall reflected in the conical mirror, the image processing unit outputs the signal related to the fluorescence image reflected in the cone mirror. The signal can be converted into a signal related to the fluorescence image in a state where the body cavity is expanded.

  In the above invention, based on the flow rate signal output from the flow rate signal output from the flow rate measurement unit that measures the flow rate of the fluid flowed into the balloon, the flow rate measurement unit that measures the flow rate of the fluid that has flowed into the balloon, An operation unit for obtaining a distance between a contact surface with an inner wall and the insertion unit is provided, and the moving unit moves the imaging unit to the central axis based on the distance obtained by the operation unit. You may move along a direction.

According to the present invention, fluid flows into the balloon through the inflow portion. The balloon inflated by the fluid that has flowed in comes into contact with the inner wall of the body cavity located in the radial direction of the insertion section, thereby positioning the insertion section at the approximate center of the body cavity. The volume of the inflated balloon can be calculated from the flow rate of the fluid flowing into the balloon. Therefore, based on the flow rate signal measured by the flow rate measurement unit, the calculation unit can easily calculate the distance between the contact surface of the balloon with the inner wall and the insertion unit.
Then, the moving unit moves the imaging unit along the central axis direction based on the distance obtained by the calculation unit, so that the distance from the inner wall to the imaging unit can be kept at a predetermined constant distance.

  In the above invention, a fluorescent agent is disposed on a contact surface of the balloon with the inner wall, a fluorescence detection unit for detecting the intensity of fluorescence generated from the fluorescence agent is provided, and the moving unit is configured to include the fluorescence detection unit. The image pickup unit may be moved based on the fluorescence intensity signal output from.

According to the present invention, the excitation light emitted outward in the radial direction of the insertion portion is applied to the fluorescent agent disposed on the contact surface of the balloon with the inner wall. Fluorescence is generated from the fluorescent agent irradiated with the excitation light. The fluorescence intensity of the generated fluorescence is detected by the fluorescence detection unit. Here, since the fluorescence intensity is inversely proportional to the square of the distance from the fluorescent agent, the fluorescence intensity signal output from the fluorescence detection unit can be regarded as a signal related to the distance between the fluorescence agent and the fluorescence detection unit.
Therefore, when the moving unit moves the imaging unit based on the fluorescence intensity signal, the distance from the inner wall to the imaging unit can be maintained at a predetermined constant distance.

  In the above invention, the fluid flowing into the balloon is a liquid, and an ultrasonic signal generator that generates ultrasonic waves toward the contact surface of the balloon with the inner wall, and the ultrasonic wave reflected from the contact surface An ultrasonic signal detector to be detected, the ultrasonic signal generator is controlled, and based on a detection signal output from the ultrasonic signal detector, a contact surface of the balloon with the inner wall, and the insertion portion And a control unit for obtaining a distance between the imaging unit and the moving unit may move the imaging unit along the central axis direction based on the distance obtained by the control unit.

  According to the present invention, ultrasonic waves are generated from the ultrasonic signal generator toward the contact surface of the balloon and propagate in the balloon filled with liquid. Here, since the liquid is filled in the balloon, the attenuation rate of the ultrasonic wave is lower than in the case where the gas is filled. The ultrasonic wave propagated in the balloon is reflected on the contact surface and detected by the ultrasonic signal detector.

The control unit controls the ultrasonic wave generated by controlling the ultrasonic signal generator, and the detection signal output from the ultrasonic signal detector is input to the control unit. Therefore, the control unit determines whether the contact surface and the insertion unit are based on the phase difference between the phase of the ultrasonic wave generated from the ultrasonic signal generator and the phase of the ultrasonic wave detected by the ultrasonic signal detector. The distance can be determined.
Therefore, the moving unit moves the imaging unit based on the distance obtained by the control unit, so that the distance from the inner wall to the imaging unit can be kept at a predetermined constant distance.

  In the above invention, a microwave signal generator that generates a microwave toward a contact surface with the inner wall of the balloon, a microwave signal detector that detects a microwave reflected from the contact surface, and the microwave A control unit that controls the signal generator and obtains a distance between the contact surface of the balloon with the inner wall and the insertion unit based on a detection signal output from the microwave signal detector is provided. The moving unit may move the imaging unit along the central axis direction based on the distance obtained by the control unit.

  According to the present invention, microwaves are generated from the microwave signal generator toward the contact surface of the balloon and propagate in the balloon. Here, the microwave propagates in the balloon with a lower attenuation rate than the ultrasonic wave. The microwave propagated in the balloon is reflected on the contact surface and detected by the microwave signal detector.

The control unit controls the microwave generated by controlling the microwave signal generator, and the detection signal output from the microwave signal detector is input to the control unit. Therefore, the control unit determines whether the contact surface and the insertion unit are based on the phase difference between the phase of the microwave generated from the microwave signal generator and the phase of the microwave detected by the microwave signal detector. The distance can be determined.
Therefore, the moving unit moves the imaging unit based on the distance obtained by the control unit, so that the distance from the inner wall to the imaging unit can be kept at a predetermined constant distance.

  According to the fluorescence endoscope of the present invention, when the observation position is changed in the advancing / retreating direction in order to move the imaging unit along the optical axis based on the distance between the contact surface of the balloon with the inner wall and the insertion unit Even so, there is an effect that the inner wall of the body cavity can be observed with fluorescence at a predetermined constant distance.

[First Embodiment]
Hereinafter, the fluorescence endoscope according to the first embodiment of the present invention will be described with reference to FIGS.
FIG. 1 is a schematic diagram illustrating the configuration of the fluorescence endoscope of the present embodiment.
As shown in FIG. 1, the fluorescence endoscope 1 determines the distance between the insertion portion 5 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 5 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 11 for displaying the captured fluorescent image are provided.

FIG. 2 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
The insertion unit 5 is inserted into the body cavity 3 of the subject and observes the fluorescence generated from the inner wall of the body cavity 3. As shown in FIG. 2, the insertion portion 5 includes an outer tube 13, a balloon 15, an irradiation portion (light emission introduction portion) 17, an introduction portion (light emission introduction portion) 19, an imaging portion 21, and a movement Part 23 is provided.

  The outer tube 13 is a tube constituting the outer peripheral surface of the insertion portion 5. The insertion tube end portion (left end portion in FIG. 2) of the outer tube 13 is provided with an excitation light window 25 through which excitation light is transmitted and a fluorescence window 27 through which fluorescence is transmitted. A balloon 15 is disposed on the outer peripheral surface of the fluorescent window 27. Inside the outer tube 13, an irradiation unit 17, an introduction unit 19, an imaging unit 21 and a moving unit 23 are arranged. The fluorescence window 27 is disposed near the insertion side end of the outer tube 13 with respect to the excitation light window 25. The excitation light window 25 is a member formed in a substantially cylindrical shape, and is formed of a material that transmits the excitation light emitted from the light source 7. The fluorescence window 27 is a member formed in a substantially cylindrical shape, and is made of a material that transmits fluorescence generated from the body cavity 3.

  A metal tube 14 is disposed on the inner peripheral surface of the outer tube 13. The inner peripheral surface of the metal tube 14 is mirror-finished, and a holding portion 45 described later is made slippery.

  The balloon 15 is inflated in the body cavity 3 to fix the insertion part 5 to the body cavity 3 and to position the insertion side end of the insertion part 5 at a substantially center of the body cavity duct. As shown in FIG. 2, the balloon 15 is disposed on the outer peripheral surface of the excitation light window 25 and the fluorescence window 27 in the outer tube 13, and transmits the excitation light and the fluorescence window 27 that pass through the excitation light window 25. It is formed from a material that transmits fluorescence. An air supply pump 49 of the measurement control unit 9 to be described later is connected to the balloon 15.

  In FIG. 2, the balloon 15 before being inflated is indicated by a solid line, and the inflated balloon 15 is indicated by a two-dot chain line.

FIG. 3 is a perspective view illustrating the configuration of the irradiation lens of FIG. FIG. 4 is a perspective view illustrating the configuration of the reflecting mirror of FIG.
The irradiating unit 17 emits the excitation light emitted from the light source 7 toward the inner wall of the body cavity 3. As shown in FIG. 2, the irradiation unit 17 includes a light guide 29, an irradiation lens 31, and an irradiation mirror 33.

  The light guide 29 guides the excitation light emitted from the light source 7 to the irradiation lens 31 disposed at the insertion side end of the insertion portion 5. The light guide 29 is composed of a bundle of fibers for guiding excitation light, and is formed in a substantially cylindrical shape.

  The irradiation lens 31 is a lens that irradiates the entire observation region of the body cavity 3 with excitation light. The irradiation lens 31 is an insertion side end of the insertion portion 5 and is disposed between the light guide 29 and the irradiation mirror 33. The irradiation lens 31 is a lens that is formed in an annular shape as shown in FIG. 3 and has a concave groove formed on the surface facing the light guide 29.

  The irradiation mirror 33 is a mirror that reflects the excitation light emitted from the irradiation lens 31 in the central axis direction of the insertion portion 5 to the outside in the radial direction of the insertion portion 5. The irradiation mirror 33 is disposed inside the outer tube 13 and at a position facing the excitation light window 25. As shown in FIG. 4, the irradiation mirror 33 is a mirror that is formed in a substantially conical shape and has a conical surface as a reflection surface, and is a mirror in which a through hole is formed along the central axis. The irradiation mirror 33 is held by a mirror holding unit 34.

  The introduction unit 19 reflects fluorescence generated from the body cavity 3 toward the imaging unit 21. As shown in FIG. 2, the introduction unit 19 includes a dichroic mirror (reflection unit) 35, a drive motor (rotation drive unit) 37, and a motor control unit 39.

  The dichroic mirror 35 reflects the fluorescence transmitted through the fluorescence window 27 in a direction along the central axis of the insertion portion 5, and transmits light having a wavelength other than the fluorescence imaged by the imaging unit 21. . The dichroic mirror 35 is disposed in the outer tube 13 so as to be rotatable about the central axis of the insertion portion 5 at a position facing the fluorescent window 27. The dichroic mirror 35 is formed in a rectangular parallelepiped shape, and reflects fluorescence generated from a partial region of the body cavity 3 toward the imaging unit 21. The dichroic mirror 35 is held by a dichroic mirror holding unit 36. The dichroic mirror 35 can be a known one and is not particularly limited.

  The drive motor 37 rotates the dichroic mirror 35 around the center axis of the insertion portion 5 as the rotation center. The drive motor 37 is disposed at the distal end portion of the insertion portion 5 and is connected to the motor control portion 39. Note that a known motor can be used as the drive motor 37 and is not particularly limited.

  The motor control unit 39 controls the rotation of the dichroic mirror 35 by controlling the rotation of the drive motor 37. A phase signal of the dichroic mirror 35 is output from the motor control unit 39 to the fluorescence signal processing unit 57, and a control signal is output from the motor control unit 39 to the drive motor 37.

The imaging unit 21 captures an image of fluorescence generated from the body cavity 3. As shown in FIG. 2, the imaging unit 21 includes an imaging lens system 41 and an imaging element 43.
The imaging lens system 41 forms an image of the fluorescence reflected by the dichroic mirror 35 on the light receiving surface of the imaging element 43. The imaging lens system 41 is arranged between the dichroic mirror 35 and the imaging element 43 and is arranged inside the irradiation mirror 33, in other words, on the central axis of the insertion portion 5. In the present embodiment, as illustrated in FIG. 2, the description is applied to the case of an imaging lens system 41 including a plurality of lenses, but the configuration of the imaging lens system 41 is not particularly limited.

  The image sensor 43 captures an image of fluorescence generated from the body cavity 3. The image sensor 43 is disposed inside the irradiation lens 31, in other words, on the central axis of the insertion unit 5, and is connected to the fluorescence signal processing unit 57 of the display unit 11. The imaging element 43 may be a known element such as a CCD (Charge Coupled Devices) or a CMOS (Complementary Metal Oxide Semiconductor), and is not particularly limited.

FIG. 5 is a cross-sectional view taken along the line AA for explaining the configuration of the holding portion of FIG.
The moving unit 23 keeps the distance between the inner wall of the body cavity 3 and the image sensor 43 constant. As shown in FIG. 2, the moving unit 23 includes a holding unit 45 and an actuator 47.

  The holding unit 45 holds the irradiation lens 31, the imaging lens system 41, and the imaging device 43, and prevents the excitation light emitted from the irradiation lens 31 from directly entering the imaging device 43. . As shown in FIG. 5, a groove portion 46 through which a signal line for transmitting a control signal from the motor control unit 39 to the drive motor 37 is formed in the holding unit 45.

  The holding part 45 is arranged so as to be relatively movable along the central axis of the insertion part 5 with respect to the metal tube 14. An actuator 47 is connected to the holding unit 45.

  The actuator 47 moves the holding part 45 along the central axis of the insertion part 5. The actuator 47 is fixed to the metal tube 14 and is also fixed to the holding portion 45. For example, the actuator 47 and the holding portion 45 can be fixed by screwing a screw formed on one side and a screw hole formed on the other side. The actuator 47 can move the holding portion 45 relative to the outer tube 13, and the movement distance can be exemplified as a maximum of about 20 mm. A control signal is input to the actuator 47 from the actuator driving unit 53 of the measurement control unit 9.

  As shown in FIG. 1, the light source 7 irradiates the body cavity 3 and emits excitation light that generates fluorescence from the body cavity 3. In particular, excitation light that generates strong fluorescence is emitted from the lesioned part T of the body cavity 3. Excitation light emitted from the light source 7 is incident on the light guide 29 of the insertion portion 5.

  The measurement control unit 9 measures the distance between the insertion unit 5 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. As shown in FIG. 1, the measurement control unit 9 includes an air supply pump (inflow unit) 49, a flow meter (flow rate measurement unit) 51, and an actuator drive unit (calculation unit) 53.

  The air supply pump 49 inflates the balloon 15 by supplying air (fluid). The air supplied from the air supply pump 49 is sent to the balloon 15 through the air supply tube 55 disposed on the outer peripheral surface of the outer tube 13. The flow signal of the air supply pump 49 is output to the flow meter 51. A known pump can be used as the air supply pump 49, and is not particularly limited.

  The flow meter 51 measures the flow rate of the air supplied from the air supply pump 49 to the balloon 15. Specifically, the air flow rate is measured based on the flow rate signal of the air supply pump 49. The flow rate signal is information necessary for obtaining the flow rate of the supplied air, and examples include the driving time of the air supply pump 49 and the rotational speed of the pump. A signal related to the air flow rate measured by the flow meter 51 is output to the actuator driving unit 53.

  The actuator drive unit 53 measures the distance between the insertion unit 5 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. A signal related to the air flow rate is input from the flow meter 51 to the actuator driving unit 53, and the actuator driving unit 53 can obtain the distance between the insertion unit 5 and the inner wall of the body cavity 3 based on the signal. In addition, a control signal is output from the actuator driving unit 53 to the actuator 47, and the actuator 47 is driven and controlled, whereby the distance between the imaging element 43 and the inner wall of the body cavity 3 can be controlled to a predetermined constant distance.

  The display unit 11 displays a fluorescent image captured by the imaging unit 21. As shown in FIG. 1, the display unit 11 includes a fluorescence signal processing unit 57 and a monitor 59.

  The fluorescence signal processing unit 57 converts the image signal output from the image sensor 43 into an image signal to be displayed on the monitor 59. The fluorescence signal processing unit 57 receives the imaging signal output from the imaging device 43 and the phase signal of the dichroic mirror 35 from the motor control unit 39. An image signal is output from the fluorescence signal processing unit 57 to the monitor 59.

Next, a method for imaging the inner wall of the body cavity 3 by the fluorescence endoscope 1 having the above configuration will be described.
First, the insertion portion 5 of the fluorescence endoscope 1 is inserted into the body cavity 3. At this time, as shown by a solid line in FIG. 2, the balloon 15 is contracted so as not to obstruct insertion, and is in close contact with the outer peripheral surface of the insertion portion 5.

  When the insertion side end of the insertion portion 5 reaches the examination region of the body cavity 3, air is supplied from the air supply pump 49 to the balloon 15, and the balloon 15 is inflated and pressed against the inner wall of the body cavity 3. The insertion portion 5 is fixed to the body cavity 3 by the balloon 15, and the insertion side end portion of the insertion portion 5 is disposed at the approximate center of the duct in the body cavity 3. The air supply pump 49 continues air supply until the pressure in the balloon 15 reaches a predetermined pressure, and stops air supply after the pressure reaches the predetermined pressure.

  Since the balloon 15 is filled with air of a predetermined pressure, the balloon 15 presses the inner wall of the body cavity 3 outward in the radial direction. For example, when there is a fold on the inner wall of the body cavity 3 like the large intestine, the fold is pushed and expanded by being pressed by the balloon 15.

FIG. 6 is a flowchart illustrating a method for controlling the actuator of FIG.
The flow meter 51 measures the air flow rate based on the flow rate signal output from the air supply pump 49, and outputs information related to the air flow rate to the actuator driving unit 53 (step S1). The actuator drive unit 53 measures the distance between the insertion unit 5 and the inner wall of the body cavity 3 by obtaining the outer diameter of the balloon 15 based on the input information relating to the air flow rate (step S2).

  Specifically, the actuator drive unit 53 stores a lookup table regarding the flow rate of the air sent to the balloon 15 and the distance between the insertion unit 5 and the inner wall of the body cavity 3 corresponding to the flow rate. The actuator driving unit 53 can obtain the distance between the insertion unit 5 and the inner wall of the body cavity 3 by referring to the lookup table. The data constituting the lookup table can be obtained by actual measurement in advance through experiments or the like, for example.

  The actuator driving unit 53 generates a control signal to be output to the actuator 47 based on the obtained distance between the insertion unit 5 and the inner wall of the body cavity 3. That is, the actuator driving unit 53 controls the relative position of the holding unit 45 with respect to the outer tube 13 so that the distance between the imaging element 43 and the inner wall of the body cavity 3 is a predetermined constant distance.

  Specifically, the actuator driving unit 53 first holds the distance from the inner wall of the body cavity 3 to the dichroic mirror 35 obtained from the obtained distance between the insertion part 5 and the inner wall of the body cavity 3 and the holding to the outer tube 13. The distance from the dichroic mirror 35 to the image sensor 43 obtained based on the relative position of the unit 45 and the distance from the current inner wall of the body cavity 3 to the image sensor 43 are obtained. The actuator driving unit 53 obtains a difference between the obtained distance and the predetermined constant distance (step S3), and controls the actuator 47 so that the difference becomes zero (step S4).

  The actuator 47 changes the relative position of the holding unit 45 with respect to the outer tube 13 based on the control signal input from the actuator driving unit 53.

  Thereafter, excitation light is emitted from the light source 7, and the excitation light passes through the outer tube 13 by the light guide 29 and is guided to the distal end side end portion of the insertion portion 5. Excitation light is emitted from the light guide 29 in a direction along the central axis of the insertion portion 5, passes through the irradiation lens 31, and enters the irradiation mirror 33. The excitation light that has entered the irradiation mirror 33 is reflected outward in the radial direction of the insertion portion 5, passes through the excitation light window 25 and the balloon 15, and enters the body cavity 3. The excitation light can illuminate the entire observation region in the body cavity 3 by passing through the irradiation lens 31.

  Fluorescence is generated from the body cavity 3 where the excitation light is incident. In particular, the amount of fluorescent light generated from the lesion T is larger than the amount of fluorescent light generated from the normal body cavity 3. The fluorescence passes through the balloon 15 and the fluorescence window 27 and enters the outer tube 13. Of the incident fluorescence, the fluorescence incident on the dichroic mirror 35 is reflected in the direction of the central axis of the insertion portion 5. Light having a wavelength other than the fluorescence incident on the dichroic mirror 35 passes through the dichroic mirror 35 without being reflected.

  The fluorescence reflected by the dichroic mirror 35 is imaged on the light receiving surface of the image sensor 43 by the imaging lens system 41. The imaging element 43 outputs an imaging signal to the fluorescence signal processing unit 57 based on the formed fluorescence image.

  On the other hand, the rotation of the dichroic mirror 35 is controlled by the motor control unit 39. Specifically, the motor control unit 39 controls the phase of the dichroic mirror 35 by controlling the rotation of the drive motor 37. Fluorescence generated from the entire inner wall of the body cavity 3 is incident on the image sensor 43 when the dichroic mirror 35 is controlled to rotate around the central axis of the insertion portion 5.

  At the same time, the motor control unit 39 outputs information related to the rotational phase of the dichroic mirror 35 to the fluorescence signal processing unit 57.

  The fluorescence signal processing unit 57 generates an image signal based on the imaging signal input from the imaging element 43 and the signal related to the rotational phase input from the motor control unit 39. The imaging signal input from the imaging element 43 is a signal related to an image that rotates as the dichroic mirror 35 rotates. Based on the signal related to the rotation phase, the fluorescence signal processing unit 57 converts an imaging signal, which is a signal related to a rotating image, into an image signal related to a still image. The converted image signal is output from the fluorescence signal processing unit 57 to the monitor 59 and displayed on the monitor 59.

According to the above configuration, the balloon 15 contacts the inner wall positioned in the radial direction of the insertion portion 5, thereby positioning the insertion portion 5 at the approximate center of the body cavity 3. That is, the balloon 15 can equalize the distance between all the partial regions of the inner wall of the body cavity 3 in the radial direction of the insertion portion 5 and the insertion portion 5.
The excitation light emitted from the irradiation unit 17 outward in the radial direction of the insertion unit 5 is irradiated to the inner wall of the body cavity 3 whose distance from the insertion unit 5 is equalized by the balloon 15, and the inner wall irradiated with the excitation light. Fluorescence is generated from Fluorescence generated from the inner wall of the body cavity 3 passes through the balloon 15, travels radially inward of the insertion portion 5, and is introduced into the insertion portion 5 from the fluorescence window 27.

The fluorescence introduced into the insertion portion 5 is reflected toward the central axis of the insertion portion 5 by the dichroic mirror 35 provided in the introduction portion 19. Since the dichroic mirror 35 is disposed so as to be rotatable around the central axis, it reflects the fluorescence generated from the inner walls of the body cavity 3 located in a plurality of different radial directions of the insertion portion 5 toward the central axis direction of the insertion portion 5. be able to.
The fluorescence reflected by the dichroic mirror 35 is imaged by the imaging element 43 of the imaging unit 21, and the imaging element 43 can acquire an image of a partial region of the inner wall located in the radial direction of the insertion unit 5.

  Since the dichroic mirror 35 is rotated by the drive motor 37, the dichroic mirror 35 reflects the fluorescence generated from the inner walls of the body cavity 3 located in a plurality of different radial directions toward the image sensor 43, and the image sensor 43 Can image fluorescence.

  At this time, the image sensor 43 is moved by the moving unit 23 along the optical axis of fluorescence incident on the image sensor 43 so as to keep the distance from the inner wall of the body cavity 3 to the image sensor 43 constant. That is, the moving unit 23 determines the distance from the inner wall of the body cavity 3 to the image sensor 43 based on the distance between the contact surface with the inner wall of the balloon 15 obtained by the actuator driving unit 53 and the insertion unit 5. The image sensor 43 can be moved so as to be kept constant.

  Therefore, the balloon 15 and the moving part 23 can make the distance between the inner wall of the body cavity 3 located in a plurality of different radial directions of the insertion part 5 and the imaging element 43 equal. For example, even when the observation position is changed along the advancing / retreating direction of the insertion portion 5, the distance from the inner wall of the body cavity 3 located in a plurality of different radial directions of the insertion portion 5 to the imaging element 43 is a predetermined constant distance. In this state, the fluorescence generated from the inner wall of the body cavity 3 can be observed.

Air is introduced into the balloon 15 by an air supply pump 49. The balloon 15 inflated by the inflowing air comes into contact with the inner wall of the body cavity 3 located in the radial direction of the insertion part 5, so that the insertion part 5 can be positioned substantially at the center of the body cavity.
The flow rate of the air flowing into the balloon 15 is measured by the flow meter 51, and the flow signal output from the flow meter 51 is input to the actuator driving unit 53. The actuator driving unit 53 can calculate the distance between the contact surface of the balloon 15 with the inner wall and the insertion unit 5 by calculating the volume of the inflated balloon 15 based on the flow rate signal. .
Therefore, based on the distance obtained by the actuator driving unit 53, the moving unit 23 moves the image sensor 43 along the central axis direction, so that the distance from the inner wall to the image sensor 43 is set to a predetermined constant distance. Can keep.

  As a method of obtaining the distance, a correspondence between the volume of the balloon 15 and the distance described above may be obtained through an experiment, and an experiment result stored in the actuator drive unit 53 as a lookup table may be used. It may be calculated based on an equation, and is not particularly limited.

  Further, once the insertion portion 5 is fixed to the body cavity 3 using the balloon 15, even when the insertion portion 5 is moved in the advancing and retreating direction within the body cavity 3, the insertion portion 5 and the inner wall are not separated. The distance can be positioned at a certain distance. The balloon 15 is preferably transparent at least with respect to the excitation light irradiated from the irradiation unit 17 and the fluorescence generated from the body cavity 3.

  The balloon 15 fixes the insertion portion 5 to the body cavity 3 by pressing the inner wall of the body cavity 3 outward in the radial direction. The folds on the inner wall of the body cavity 3 are stretched because they are pressed radially outward by the balloon 15. Therefore, the fluorescence endoscope of the present invention can observe a region hidden between folds.

[First Modification of First Embodiment]
Next, a first modification of the first embodiment of the present invention will be described with reference to FIGS.
The basic configuration of the fluorescence endoscope of the present modification is the same as that of the first embodiment, but the configuration of the reflecting portion is different from that of the first embodiment. Therefore, in this modified example, only the periphery of the reflecting portion will be described using FIGS. 7 to 10, and description of other components and the like will be omitted.
FIG. 7 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to this modification.
In addition, about the component same as 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 7, the fluorescence endoscope 101 determines the distance between the insertion portion 105 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 5 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 111 for displaying the captured fluorescent image are provided.

As shown in FIG. 7, the insertion unit 105 includes an outer tube 13, a balloon 15, an irradiation unit (light emission introduction unit) 17, an introduction unit (light emission introduction unit) 119, an imaging unit 21, and a movement Part 23 is provided.
The introduction unit 119 reflects the fluorescence generated from the body cavity 3 toward the imaging unit 21. The introduction part 119 includes a conical mirror (reflection part) 135.

FIG. 8 is a schematic diagram illustrating the configuration of the conical mirror of FIG.
The conical mirror 135 reflects the fluorescence transmitted through the fluorescence window 27 in a direction along the central axis of the insertion portion 5. The conical mirror 135 is disposed in the outer tube 13 at a position facing the fluorescent window 27. Further, as shown in FIG. 8, the conical mirror 135 is a mirror formed in a conical shape and having a conical surface as a reflecting surface. Therefore, the conical mirror 135 reflects the fluorescence generated from the entire inner wall of the body cavity 3 toward the imaging unit 21. The conical mirror 135 is disposed at the distal end portion of the insertion portion 105.

  As shown in FIG. 7, the display unit 111 displays a fluorescent image captured by the imaging unit 21. As shown in FIG. 7, the display unit 111 includes a fluorescence signal processing unit (image processing unit) 157, a monitor 59, and an image sensor (insertion length measurement unit) 161.

  The fluorescence signal processing unit 157 converts the image signal output from the image sensor 43 into an image signal to be displayed on the monitor 59. The fluorescence signal processing unit 157 receives an image signal output from the image sensor 43 and a signal related to the insertion length output from the image sensor 161. In addition, an image signal is output from the fluorescence signal processing unit 157 to the monitor 59.

  The image sensor 161 measures the insertion length of the insertion portion 5 with respect to the body cavity 3. The image sensor 161 measures the insertion length of the insertion unit 5 by capturing an image of a scale provided on the insertion unit 5. A signal related to the insertion length is output from the image sensor 161 to the fluorescence signal processing unit 157. Note that a known sensor or the like can be used as the image sensor 161, and a known method can be used as a method for calculating the insertion length, which is not particularly limited.

Next, a method for imaging the inner wall of the body cavity 3 by the fluorescence endoscope 101 having the above configuration will be described.
The method for fixing the insertion portion 5 with the balloon 15 and the method for controlling the distance from the inner wall of the body cavity 3 to the image sensor 43 are the same as those in the first embodiment, and thus the description thereof is omitted.
The operation until the body cavity 3 is irradiated with the excitation light emitted from the light source 7 is also the same as that in the first embodiment, and a description thereof will be omitted.

  The fluorescence generated from the body cavity 3 passes through the balloon 15 and the fluorescence window 27 and enters the outer tube 13. The incident fluorescence is reflected by the conical mirror 135 in the direction of the central axis of the insertion portion 105. That is, the fluorescence generated from the entire inner peripheral surface of the body cavity 3, which is a region facing the fluorescence window 27, enters the conical mirror 135 and is reflected toward the image sensor 43.

  The fluorescence reflected by the conical mirror 135 is imaged on the light receiving surface by the imaging lens system 41 on the imaging device 43. The imaging element 43 outputs an imaging signal to the fluorescence signal processing unit 157 based on the formed fluorescence image.

FIG. 9 is a diagram illustrating a fluorescent image captured by the image sensor of FIG. FIG. 10 is a diagram showing an image after being converted by the fluorescence signal processing unit of FIG.
The fluorescence signal processing unit 157 generates an image signal based on the imaging signal input from the imaging element 43 and the signal relating to the insertion length input from the image sensor 161. Here, the image related to the imaging signal input from the imaging element 43 is an image of the inner wall of the body cavity 3 reflected on the circumferential surface of the conical mirror 135, as shown in FIG. The fluorescence signal processing unit 157 performs processing such as expansion processing and expansion processing on the imaging signal based on the signal related to the insertion length, and an image related to the image in which the body cavity 3 is expanded as shown in FIG. Generate a signal. The generated image signal is output to the monitor 59 and displayed on the monitor 59 as shown in FIG.

According to said structure, excitation light is radiate | emitted from the irradiation part 17 to the radial direction outward of the insertion part 105, and is irradiated to the inner wall of the body cavity 3 which is contacting the balloon. Fluorescence is generated from the inner wall of the body cavity 3 irradiated with the excitation light, and the fluorescence is introduced into the insertion portion 105.
The fluorescence introduced into the insertion portion 105 is reflected toward the central axis of the insertion portion 105 by the conical mirror 135 provided in the introduction portion 119. The fluorescence reflected from the conical mirror 135 is picked up by the image pickup device 43, and the image pickup device 43 can acquire an image of the entire inner peripheral surface of the inner wall located in the radial direction of the insertion portion 105.

  Further, as compared with the fluorescence endoscope 1 according to the first embodiment, since it is not necessary to provide the drive motor 37 at the distal end side end portion of the insertion portion 103, the configuration of the insertion portion 103 can be simplified. .

  The insertion length of the insertion portion 5 with respect to the body cavity is measured by the image sensor 161. A signal related to the insertion length output from the image sensor 161 is input to the fluorescence signal processing unit 157. The fluorescence signal processing unit 157 receives the fluorescence image signal output from the image sensor 43 and the signal related to the insertion length output from the image sensor 161, and performs processing for developing the image signal based on both signals. Is called. That is, the signal related to the fluorescence image reflected on the conical mirror 135 can be converted into the signal related to the fluorescence image in a state where the body cavity 3 is expanded.

[Second Modification of First Embodiment]
Next, a second modification of the first embodiment of the present invention will be described with reference to FIG. 11 and FIG.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the first embodiment, but the configuration of the insertion portion is different from that of the first embodiment. Therefore, in this modification, only the periphery of the insertion portion will be described using FIG. 11 and FIG. 12, and description of other components and the like will be omitted.
FIG. 11 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to this modification.
In addition, about the component same as 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 11, the fluorescence endoscope 201 determines the distance between the insertion portion 205 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 205 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 11 for displaying the captured fluorescent image are provided.

FIG. 12 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 12, the insertion portion 205 is provided with an outer insertion portion (insertion portion) 213A and a rotation insertion portion (light emission introduction portion, rotation portion) 213B.

  The outer insertion portion 213 </ b> A is a tube that forms the outer peripheral surface of the insertion portion 205. A balloon 15 is disposed on the outer peripheral surface of the insertion side end (the left end in FIG. 11) in the outer insertion portion 213A. At least the region where the balloon 15 of the outer insertion portion 213A is disposed and the region facing the excitation light window 225 and the fluorescence window 227, which will be described later, is used for excitation light and fluorescence transmitted through the excitation light window 225. It is good also as forming from the material which permeate | transmits the fluorescence which permeate | transmits the window 227. FIG. The outer insertion portion 213A is preferably formed as a so-called rigid endoscope insertion portion that does not bend. By doing in this way, the rotation insertion part 213B inserted in the inside can be easily rotated with respect to the outer insertion part 213A.

  The rotation insertion portion 213B is inserted into the outer insertion portion 213A. The rotation insertion unit 213B includes an excitation light window 225, a fluorescence window 227, an irradiation unit (light emission introduction unit) 217, an introduction unit (light emission introduction unit) 219, an imaging unit 21, and a movement unit 23. And are provided.

  The excitation light window 225 is a window through which excitation light exits from the inside to the outside of the rotation insertion portion 213B. The excitation light window 225 is formed in the vicinity of the distal end side end portion of the rotation insertion portion 213B, and is formed so that the circumferential length of the rotation insertion portion 213B is about 1/4 of the circumference. Yes.

  The fluorescence window 227 is a window through which fluorescence enters from the outer side to the inner side of the rotary insertion portion 213B. The fluorescent window 227 is formed in the vicinity of the distal end side end portion of the rotary insertion portion 213B, and is formed so that the circumferential length of the rotary insertion portion 213B is about 1/4 of the circumference. . Further, the fluorescence window 227 is formed closer to the distal end side of the rotation insertion portion 213B than the excitation light window 225 is.

  The circumferential lengths of the excitation light window 225 and the fluorescence window 227 may be about ¼ of the circumference as described above, or may be longer or less. There is no particular limitation.

  The irradiation unit 217 emits the excitation light emitted from the light source 7 toward the inner wall of the body cavity 3. As shown in FIG. 12, the irradiation unit 217 includes a light guide 229, an irradiation lens 231, and an irradiation mirror 233.

  The light guide 229 guides the excitation light emitted from the light source 7 to the irradiation lens 231 disposed at the insertion side end of the rotation insertion portion 213B. The light guide 229 is composed of a bundle of fibers that guide excitation light.

  The irradiation lens 231 is a lens that irradiates the entire observation region of the body cavity 3 with excitation light. The irradiation lens 231 is an insertion-side end portion of the rotation insertion portion 213B and is disposed between the light guide 229 and the irradiation mirror 233. The irradiation lens 231 is a lens having a concave surface facing the light guide 229.

  The irradiation mirror 233 is a mirror that reflects the excitation light emitted from the irradiation lens 231 in the direction of the central axis of the insertion portion 5 to the outside in the radial direction of the rotation insertion portion 213B. The irradiation mirror 233 is disposed inside the rotation insertion portion 213B and at a position facing the excitation light window 225. The irradiation mirror 233 is a mirror having a three-dimensional shape in which the cross section cut by the plane including the central axis of the rotary insertion portion 213B is triangular, and the cross sectional shape is rotated about the central axis as the rotation axis. The irradiation mirror 233 is held by a mirror holding unit 234.

  The introduction unit 219 reflects the fluorescence generated from the body cavity 3 toward the imaging unit 21. The introduction unit 219 includes a dichroic mirror (reflection unit) 35 as shown in FIG. The dichroic mirror 35 is directly fixed to the distal end portion of the rotary insertion portion 213B.

  Next, a method for imaging the inner wall of the body cavity 3 by the fluorescence endoscope 201 having the above configuration will be described.

First, the outer insertion portion 213 </ b> A of the fluorescence endoscope 201 is inserted into the body cavity 3. You may insert into a body cavity in the state which put the direct-view type endoscope which is not illustrated in the inside of the outer side insertion part 213A. During insertion, the user can see the front, making insertion easier. When the observation position is reached, the direct-view type endoscope is pulled out and the rotation insertion portion 213B is inserted. At this time, the balloon 15 is contracted so as not to obstruct insertion, and is in close contact with the outer peripheral surface of the outer insertion portion 213A. When the insertion side end of the outer insertion portion 213A reaches the examination region of the body cavity 3, air is sent from the air feeding pump 49 to the balloon 15, and the balloon 15 is inflated and pressed against the inner wall of the body cavity 3. The outer insertion portion 213 </ b> A is fixed to the body cavity 3 by the balloon 15, and the insertion side end of the outer insertion portion 213 </ b> A is disposed at the approximate center of the duct in the body cavity 3.
Thereafter, the rotation insertion portion 213B is inserted into the outer insertion portion 213A.

  Note that the operation of the balloon 15 and the control method of the actuator 47 are the same as those in the first embodiment, and thus the description thereof is omitted.

  Thereafter, excitation light is emitted from the light source 7, and the excitation light is guided by the light guide 229 through the rotation insertion portion 213 </ b> B to the distal end side end portion of the rotation insertion portion 213 </ b> B. Excitation light is emitted from the light guide 229 in a direction along the central axis of the rotary insertion portion 213B, passes through the irradiation lens 231 and enters the irradiation mirror 233. The excitation light that has entered the irradiation mirror 233 is reflected outward in the radial direction of the rotary insertion portion 213B, passes through the excitation light window 225, the outer insertion portion 213A, and the balloon 15 and enters the body cavity 3. The excitation light can illuminate the entire observation region in the body cavity 3 by passing through the irradiation lens 231.

  Fluorescence is generated from the body cavity 3 where the excitation light is incident. In particular, the amount of fluorescent light generated from the lesion T is larger than the amount of fluorescent light generated from the normal body cavity 3. The fluorescence passes through the balloon 15, the outer insertion portion 213A, and the fluorescence window 227 and enters the rotation insertion portion 213B. Of the incident fluorescence, the fluorescence incident on the dichroic mirror 35 is reflected in the direction of the central axis of the rotary insertion portion 213B. Light having a wavelength other than the fluorescence incident on the dichroic mirror 35 passes through the dichroic mirror 35 without being reflected.

The fluorescence reflected by the dichroic mirror 35 is imaged on the light receiving surface by the imaging lens system 41 on the imaging device 43. The imaging element 43 outputs an imaging signal to the fluorescence signal processing unit 57 based on the formed fluorescence image.
The fluorescence signal processing unit 57 generates an image signal based on the imaging signal input from the imaging element 43. The image signal is output from the fluorescence signal processing unit 57 to the monitor 59 and displayed on the monitor 59.

  On the other hand, the rotation insertion portion 213B is arranged so as to be rotatable around the central axis with respect to the outer insertion portion 213A. Therefore, by rotating the rotation insertion portion 213B, fluorescence generated from a predetermined inner wall of the body cavity 3 is emitted. Can be observed.

  According to the above configuration, the excitation light is emitted radially outward of the outer insertion portion 213A from the irradiation portion 217 provided in the rotation insertion portion 213B, and is irradiated on the inner wall of the body cavity that is in contact with the balloon. Fluorescence is generated from the inner wall of the body cavity irradiated with the excitation light, and the fluorescence passes through the outer insertion portion 213A and is introduced into the rotation insertion portion 213B.

  The fluorescence introduced into the rotation insertion portion 213B is reflected toward the central axis of the rotation insertion portion 213B by the dichroic mirror 35 provided in the rotation insertion portion 213B. The fluorescence reflected from the dichroic mirror 35 is captured by the image sensor 43, and the image sensor 43 can acquire an image of a partial region of the inner wall located in the radial direction of the insertion portion 205.

  Here, since the rotation insertion portion 213B is disposed inside the outer insertion portion 213A so as to be rotatable around the central axis of the outer insertion portion 213A, the rotation insertion portion 213B is rotated from a plurality of different radial directions of the insertion portion 205. It is possible to introduce it into the inside of 213B.

[Third Modification of First Embodiment]
Next, a third modification of the first embodiment of the present invention will be described with reference to FIGS.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the second modification of the first embodiment, but the structure of the rotary insertion portion is different from that of the first embodiment. Therefore, in this modification, only the periphery of the rotary insertion portion will be described using FIGS. 13 and 14, and description of other components will be omitted.
FIG. 13 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to this modification.
In addition, about the component same as the 2nd modification of 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 13, the fluorescence endoscope 901 has a distance between the insertion portion 905 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 905 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 11 for displaying the captured fluorescent image are provided.

FIG. 14 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 14, the insertion portion 905 is provided with an outer insertion portion 213A and a rotation insertion portion (light emission introduction portion, rotation portion) 913B.

  The rotary insertion portion 913B is disposed inside the distal end portion of the outer insertion portion 213A so as to be rotatable around the central axis of the insertion portion 905. The rotation insertion unit 913B includes an excitation light window 225, a fluorescence window 227, an irradiation unit (light emission introduction unit) 217, an introduction unit (light emission introduction unit) 219, an imaging unit 21, and a movement unit 23. And are provided. Furthermore, the rotary insertion portion 913B is provided with an optical rotary joint 915, a signal rotary joint 917, and an insertion portion drive motor 919.

  The optical rotary joint 915 is a joint that guides excitation light from the outer insertion portion 213A to the rotation insertion portion 913B that rotates in the outer insertion portion 213A. The optical rotary joint 915 is disposed on the central axis of the insertion portion 905 and is disposed so as to connect the light guide 229 in the outer insertion portion 213A and the light guide 229 of the rotation insertion portion 913B. The optical rotary joint 915 includes lenses 916A and 916B arranged to face each other, the lens 916A is disposed in the outer insertion portion 213A, and the lens 916B is disposed in the rotation insertion portion 913B. Therefore, the excitation light emitted from the light guide 229 in the outer insertion portion 213A passes through the lens 916A and the lens 916B and enters the light guide 229 of the rotation insertion portion 913B.

  In the present embodiment, a known optical rotary joint can be used as the optical rotary joint 915, and is not limited to the optical rotary joint of the aspect exemplified in the present embodiment.

  The signal rotary joint 917 is a joint that electrically connects the outer insertion portion 213A and the rotation insertion portion 913B that rotates in the outer insertion portion 213A. The signal rotary joint 917 receives the imaging current collecting ring 921 and imaging brush 923 that guides the imaging signal output from the imaging element 43 to the fluorescence signal processing unit 57, and the control signal output from the actuator driving unit 53 as the actuator 47. A control current collecting ring 925 and a control brush 927 are provided.

  The current collecting ring for imaging 921 and the current collecting ring for control 925 are circular or cylindrical members provided in the rotary insertion portion 913B, and the central axes of the current collection rings 921 and 921 are the rotation insertion portion 913B. It is arrange | positioned so that it may correspond with the center axis line of. The imaging current collecting ring 921 is electrically connected to the imaging element 43, and the control current collecting ring 925 is electrically connected to the actuator 47.

The imaging brush 923 and the control brush 927 are brushes provided in the outer insertion portion 213A. The imaging brush 923 is slidably disposed on the circumferential surface or the cylindrical surface of the imaging current collecting ring 921 and is electrically connected to the fluorescence signal processing unit 57. The control brush 927 is slidably disposed on the circumferential surface or the cylindrical surface of the control current collecting ring 925 and is electrically connected to the actuator driving unit 53.
In the present embodiment, a known current collector such as a slip ring can be used as the signal rotary joint 917, and the present invention is not limited to the signal rotary joint of the aspect exemplified in the present embodiment.

The insertion portion drive motor 919 is disposed in the outer insertion portion 213A and rotates the rotation insertion portion 913B in the outer insertion portion 213A. The insertion portion drive motor 919 is disposed so as to rotationally drive the rotation insertion portion 913B via a gear (not shown) or the like, and is connected to the motor control portion 39.
In addition, as an insertion part drive motor 919, a well-known motor can be used and it does not specifically limit.

Next, a method for imaging the inner wall of the body cavity 3 using the fluorescence endoscope 901 having the above configuration will be described.
Note that the method for fixing the insertion portion 905 by the balloon 15 and the method for controlling the distance from the inner wall of the body cavity 3 to the image sensor 43 are the same as those in the first embodiment, and a description thereof will be omitted.

Here, the operation of the optical rotary joint 915 which is a characteristic part of this modification will be described.
The excitation light emitted from the light source 7 is guided by the light guide 229 through the outer insertion portion 213A to the optical rotary joint 915. Excitation light is emitted from the light guide 229 of the outer insertion portion 213A toward the lens 916A. The excitation light incident on the lens 916A becomes parallel light and enters the lens 916B.

Since the optical axes of the lenses 916A and 916B coincide with the central axis of the rotation insertion portion 913B, all the excitation light emitted from the lens 916A rotates even when the rotation insertion portion 913B is rotationally driven by the insertion portion drive motor 919. The light enters the lens 916B that rotates together with the insertion portion 913B.
The excitation light incident on the lens 916B is collected on the light guide 229 of the rotary insertion portion 913B. The condensed excitation light is emitted through the irradiation lens 231. Hereinafter, the action of the excitation light illuminating the body cavity 3 is the same as that of the second modification example, and the description thereof is omitted.

Next, the operation of the signal rotary joint 917, which is another feature of this modification, will be described. In addition, since the effect | action until the fluorescence generate | occur | produced from the body cavity 3 image-forms on the image pick-up element 43 is the same as that of a 2nd modification, the description is abbreviate | omitted.
Based on the formed fluorescent image, the imaging device 43 outputs an imaging signal to the signal rotary joint 917. The imaging signal from the imaging element 43 is input from the imaging current collecting ring 921 of the signal rotary joint 917 through the imaging brush 923 to the fluorescence signal processing unit 57.

  On the other hand, the motor control unit 39 outputs a control signal to the signal rotary joint 917. The control signal is input from the control brush 927 of the signal rotary joint 917 through the control current collecting ring 925 to the actuator 47.

  Since the central axes of the imaging current collecting ring 921 and the control current collecting ring 925 coincide with the central axis of the rotation insertion portion 913B, even if the rotation insertion portion 913B is rotationally driven by the insertion portion drive motor 919, The imaging current collection ring 921 and the imaging brush 923, and the control current collection ring 925 and the control brush 927 can be kept in sliding contact without leaving. Therefore, the current collecting ring for imaging 921 and the brush for imaging 923, and the current collecting ring for control 925 and the brush for controlling 927 can continue to be electrically connected.

  According to the above configuration, the excitation light is emitted radially outward of the insertion portion 905 from the irradiation portion 217 provided in the rotary insertion portion 913 B, and is irradiated on the inner wall of the body cavity 3 in contact with the balloon 15. Fluorescence is generated from the inner wall of the body cavity 3 irradiated with the excitation light, and the fluorescence passes through the outer insertion portion 213A and is introduced into the rotation insertion portion 913B. The fluorescence introduced into the rotation insertion portion 913B is imaged by the image sensor 43 provided in the rotation insertion portion 913B.

  Here, since the rotation insertion portion 913B is disposed inside the outer insertion portion 213A so as to be rotatable around the central axis of the insertion portion 905, the rotation insertion portion 913B is rotated from a plurality of different radial directions of the insertion portion 905. It is possible to introduce inside.

[Fourth Modification of First Embodiment]
Next, a fourth modification of the first embodiment of the present invention will be described with reference to FIGS.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the second modification of the first embodiment, but the structure of the rotary insertion portion is different from that of the first embodiment. Therefore, in this modification, only the periphery of the rotary insertion unit will be described using FIGS. 15 to 17 and description of other components and the like will be omitted.
FIG. 15 is a schematic diagram illustrating the configuration of the fluorescence endoscope in the present modification.
In addition, about the component same as the 2nd modification of 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 15, the fluorescence endoscope 301 determines the distance between the insertion portion 305 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 305 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 11 for displaying the captured fluorescent image are provided.

FIG. 16 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 16, the insertion portion 305 is provided with an outer insertion portion 213A and a rotation insertion portion (light emission introduction portion, rotation portion) 313B.

FIG. 17 is a front view for explaining the configuration of the insertion portion in FIG. 16.
The rotation insertion portion 313B is inserted into the outer insertion portion 213A. The rotation insertion unit 313B includes an excitation light window 225, a fluorescence window 227, an irradiation unit (light emission introduction unit) 217, an introduction unit (light emission introduction unit) 219, an imaging unit 21, and a movement unit 23. And forceps holes 325 are provided.

  The forceps hole 325 is a through hole provided in the rotary insertion portion 313B through which the direct-view scope 327, forceps, and the like are inserted. The forceps hole 325 is a through hole formed in the vicinity of the outer peripheral surface of the rotary insertion portion 313B (see FIG. 17) along the central axis.

Next, a method for imaging the inner wall of the body cavity 3 using the fluorescence endoscope 301 having the above configuration will be described.
Note that the method of fixing the outer insertion portion 213A by the balloon 15 and the fluorescence imaging of the body cavity 3 by the rotation insertion portion 313B are the same as those in the second modification of the first embodiment, and thus the description thereof is omitted.

Next, a method of using the forceps hole 325 of the rotary insertion portion 313B will be described.
For example, the direct-view scope 327 is inserted into the forceps hole 325, and the distal end of the direct-view scope 327 protrudes from the distal end side end of the rotation insertion portion 313B. By using the direct-view scope 327 as described above, an image in the central axis direction of the insertion unit 305 can be acquired.
Alternatively, medical treatment of the body cavity 3 can be performed by inserting various forceps through the forceps hole 325.

[Fifth Modification of First Embodiment]
Next, a fifth modification of the first embodiment of the present invention will be described with reference to FIGS.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the first embodiment, but the configuration of the insertion portion is different from that of the first embodiment. Therefore, in this modification, only the periphery of the insertion portion will be described with reference to FIGS. 18 and 19, and description of other components will be omitted.
FIG. 18 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to this modification.
In addition, about the component same as 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 18, the fluorescence endoscope 401 measures the distance between the insertion portion 405 inserted into the body cavity 3 of the subject, the power source 407 that supplies power, and the insertion portion 405 and the inner wall of the body cavity 3. A measurement control unit 9 for performing the measurement, and a display unit 11 for displaying the captured fluorescent image.

FIG. 19 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 19, the insertion portion 405 is provided with an outer insertion portion (insertion portion) 413A and a rotation insertion portion (light emission introduction portion, rotation portion) 413B.

  The outer insertion portion 413A is a tube constituting the outer peripheral surface of the insertion portion 405. A balloon 15 is arranged on the outer peripheral surface of the insertion side end (the left end in FIG. 19) in the outer insertion portion 413A. At least the region where the balloon 15 of the outer insertion portion 413A is disposed, and the region facing the window portion 425, which will be described later, is formed of a material that transmits excitation light and fluorescence that pass through the window portion 425. It is good. The outer insertion portion 413A is preferably formed as an insertion portion of a so-called rigid endoscope that does not bend. By doing in this way, the rotation insertion part 413B inserted in the inside can be easily rotated with respect to the outer insertion part 413A.

  The rotation insertion portion 413B is inserted into the outer insertion portion 413A. As shown in FIG. 19, the rotation insertion unit 413 </ b> B includes an outer tube 413, an irradiation unit (light emission introduction unit) 417, an imaging unit 421, a moving unit 423, and a window unit 425 through which excitation light and fluorescence are transmitted. And are provided.

  The outer tube 413 is a tube that constitutes the outer peripheral surface of the rotary insertion portion 413B. A window portion 425 through which excitation light and fluorescence are transmitted is provided at an insertion side end portion (left end portion in FIG. 19) of the outer tube 413. An irradiation unit 417, an imaging unit 421, and a moving unit 423 are arranged inside the outer tube 413. The window 425 is formed of a material that transmits the excitation light emitted from the light source 7 and the fluorescence generated from the body cavity 3.

  The irradiation unit 417 emits excitation light toward the inner wall of the body cavity 3. As illustrated in FIG. 19, the irradiation unit 417 includes an LED (Light Emitting Diode) 429.

  The LED 429 emits excitation light when power is supplied from the power supply 407. The LED 429 is arranged so as to emit excitation light toward the window 425 side, on the radially outer side of the rotation insertion portion 413B. The LED 429 and the power source 407 are connected by a power wiring 430. In addition, as the irradiation part 417, LED429 may be used as mentioned above, and the element which radiate | emits other excitation light may be used, and it does not specifically limit.

  The imaging unit 421 captures an image of fluorescence generated from the body cavity 3. As illustrated in FIG. 19, the imaging unit 421 includes an imaging lens system 441 and an imaging element 443.

  The imaging lens system 441 forms a fluorescent image transmitted through the window 425 on the light receiving surface of the imaging element 443. The imaging lens system 441 is disposed between the window 425 and the imaging element 443. The optical axis of the imaging lens system 441 is disposed so as to be parallel to the radial direction of the insertion portion 405.

  The image sensor 443 captures an image of fluorescence generated from the body cavity 3. The image sensor 443 is disposed so as to image fluorescence incident from the window 425. In other words, the image sensor 443 is arranged so as to image fluorescence incident from the outside in the radial direction of the rotary insertion portion 413B. In addition, the image sensor 443 is connected to the fluorescent signal processing unit 57 of the display unit 11 by a signal wiring 444.

  The moving unit 423 keeps the distance between the inner wall of the body cavity 3 and the image sensor 443 constant. As illustrated in FIG. 19, the moving unit 423 includes a holding unit 445 and an actuator 447.

  The holding unit 445 holds the LED 429 and the image sensor 443. The holding portion 445 is disposed so as to be relatively movable with respect to the insertion portion 405 along the radial direction of the rotation insertion portion 413B. An actuator 447 is connected to the holding portion 445.

  The actuator 447 moves the holding portion 445 along the radial direction of the rotary insertion portion 413B. The actuator 447 is fixed to the wall portion 406 of the rotation insertion portion 413B and is also fixed to the holding portion 445. For example, the actuator 447 and the holding portion 445 can be fixed by screwing a screw formed on one side and a screw hole formed on the other side. A control signal is input to the actuator 447 from the actuator driving unit 53 of the measurement control unit 9.

Next, a method of imaging the inner wall of the body cavity 3 using the fluorescence endoscope 401 having the above configuration will be described.
First, the outer insertion portion 413A of the fluorescence endoscope 401 is inserted into the body cavity 3. You may insert into a body cavity in the state which put the direct-view type endoscope which is not illustrated in the inside of the outer side insertion part 413A. During insertion, the user can see the front, making insertion easier. When the observation position is reached, the direct-view type endoscope is pulled out and the rotation insertion portion 413B is inserted. At this time, the balloon 15 is contracted so as not to obstruct insertion, and is in close contact with the outer peripheral surface of the outer insertion portion 413A. When the insertion side end portion of the outer insertion portion 413A reaches the examination region of the body cavity 3, air is supplied from the air supply pump 49 to the balloon 15, and the balloon 15 is inflated and pressed against the inner wall of the body cavity 3. The outer insertion portion 413A is fixed to the body cavity 3 by the balloon 15, and the insertion side end portion of the outer insertion portion 413A is disposed at the approximate center of the duct in the body cavity 3.
Thereafter, the rotation insertion portion 413B is inserted into the outer insertion portion 413A.

  Note that the method for fixing the outer insertion portion 413A by the balloon 15 and the method for measuring the distance from the inner wall of the body cavity 3 to the image sensor 443 are the same as those in the first embodiment, and a description thereof is omitted.

The actuator driving unit 53 obtains a difference between the distance from the inner wall of the body cavity 3 to the image sensor 43 and a predetermined constant distance from the inner wall of the body cavity 3 to the image sensor 43, and sets the actuator 447 so that the difference becomes zero. I have control.
The actuator 447 changes the relative position of the holding unit 445 with respect to the insertion unit 405 based on the input control signal.

  Thereafter, power is supplied from the power source 407 to the LED 429, and excitation light is emitted from the LED 429. The excitation light is emitted outward in the radial direction of the rotary insertion portion 413B, passes through the window portion 425, the outer insertion portion 413A, and the balloon 15 and enters the body cavity 3.

  Fluorescence is generated from the body cavity 3 where the excitation light is incident. The fluorescence passes through the balloon 15, the outer insertion portion 413A, and the window portion 425, and enters the rotation insertion portion 413B. The incident fluorescence is imaged on the light receiving surface by the imaging lens system 441 on the imaging device 443. The imaging element 443 outputs an imaging signal to the fluorescence signal processing unit 57 based on the formed fluorescent image.

  The fluorescence signal processing unit 57 generates an image signal based on the imaging signal input from the imaging element 43. The converted image signal is output from the fluorescence signal processing unit 57 to the monitor 59 and displayed on the monitor 59.

  According to the above configuration, the excitation light is emitted radially outward of the insertion portion 405 from the irradiation portion 417 provided in the rotary insertion portion 413B, and is irradiated on the inner wall of the body cavity 3 that is in contact with the balloon 15. Fluorescence is generated from the inner wall of the body cavity 3 irradiated with the excitation light, and the fluorescence passes through the outer insertion portion 413A and is introduced into the rotation insertion portion 413B. The fluorescence introduced into the rotation insertion portion 413B is imaged by the imaging device 443, and the imaging device 443 can acquire an image of a partial region of the inner wall located in the radial direction of the insertion portion 405.

  Here, since the rotation insertion portion 413B is disposed inside the outer insertion portion 413A so as to be rotatable around the central axis of the insertion portion 405, the fluorescent light is inserted into the insertion portion 405 from a plurality of different radial directions. It can be introduced inside.

  When the outer insertion portion 413A is fixed by the balloon 15, the distance from all the partial regions in the circumferential direction of the inner wall to the outer insertion portion 413A can be made equal, but the distance from the inner wall to the imaging unit 421 is always constant. I can't keep it. Therefore, the distance from the inner wall to the imaging unit 421 is controlled by the moving unit 423 based on the distance from the inner wall to the outer insertion portion 413A, so that the distance from the inner wall to the imaging unit 421 is a predetermined constant. Can be kept at a distance. Therefore, the fluorescence endoscope 401 of this modification can perform fluorescence observation of the entire inner wall of the body cavity at a predetermined constant distance even when the observation position is changed in the forward / backward direction.

[Sixth Modification of First Embodiment]
Next, a sixth modification of the first embodiment of the present invention will be described with reference to FIG.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the first embodiment, but the configuration of the insertion portion is different from that of the first embodiment. Therefore, in this modification, only the periphery of the insertion portion will be described with reference to FIG. 20, and description of other components and the like will be omitted.
FIG. 20 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to this modification.
In addition, about the component same as 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 20, the fluorescence endoscope 501 has an insertion portion 505 inserted into the body cavity 3 of the subject, a light source 7 that emits excitation light, and a distance between the insertion portion 505 and the inner wall of the body cavity 3. A measurement control unit 9 for measuring and a display unit 11 for displaying the captured fluorescent image are provided.

  The insertion unit 505 is inserted into the body cavity 3 of the subject and observes fluorescence generated from the inner wall of the body cavity 3. As shown in FIG. 20, the insertion portion 505 includes an outer tube 513, a balloon 15, an irradiation portion (light emission introduction portion) 517, an introduction portion (light emission introduction portion) 19, an imaging portion 521, and a movement Part 523.

  The outer tube 513 is a tube that constitutes the outer peripheral surface of the insertion portion 505. A window portion 525 through which excitation light and fluorescence are transmitted is provided at the insertion side end portion (left end portion in FIG. 20) of the outer tube 513, and the balloon 15 is disposed on the outer peripheral surface of the window portion 525. An irradiation unit 517, an imaging unit 521, and a moving unit 523 are disposed inside the outer tube 513. The window 525 is formed in a cylindrical shape, and is formed of a material that transmits the excitation light emitted from the light source 7 and the fluorescence generated from the body cavity 3.

  The irradiation unit 517 emits the excitation light emitted from the light source 7 (see FIG. 1) toward the inner wall of the body cavity 3. As shown in FIG. 20, the irradiation unit 517 includes a light guide 29, an irradiation lens 531, and an irradiation mirror 533.

  The irradiation lens 531 is a lens that irradiates the entire observation region of the body cavity 3 with excitation light. The irradiation lens 531 is an insertion side end of the insertion portion 505 and is disposed between the light guide 29 and the irradiation mirror 533. The irradiation lens 531 is a lens formed in an annular shape, and is a lens in which a surface facing the irradiation mirror 533 is formed in a convex shape.

  The irradiation mirror 533 is a mirror that reflects the excitation light emitted from the irradiation lens 531 in the central axis direction of the insertion portion 505 to the outside in the radial direction of the insertion portion 505. The irradiation mirror 533 is disposed inside the insertion portion 505 and at a position facing the window portion 525. The irradiation mirror 533 is a mirror that is formed in a substantially conical shape and has a conical surface as a reflection surface, and is a mirror in which a through hole is formed along the central axis. The conical surface is formed in a curved surface that protrudes outward as shown in the figure. The cross section cut by the plane including the central axis of the insertion portion 505 is a triangle, and the mirror has a three-dimensional shape in which the cross sectional shape is rotated about the central axis as a rotation axis. Further, the irradiation mirror 533 is held by the distal end portion 534 of the insertion portion 505.

The imaging unit 521 captures an image of fluorescence generated from the body cavity 3. As illustrated in FIG. 20, the imaging unit 521 includes an imaging lens system 541 and an imaging element 43.
The imaging lens system 541 forms an image of fluorescence reflected by the dichroic mirror 35 on the light receiving surface of the imaging element 43. The imaging lens system 541 is disposed between the dichroic mirror 35 and the imaging element 43.

The moving unit 523 keeps the distance between the inner wall of the body cavity 3 and the image sensor 43 constant. The moving part 523 includes a holding part 545 and an actuator 47 as shown in FIG.
The holding unit 545 holds the irradiation lens 531, the imaging lens system 541, and the imaging element 43. The holding portion 545 is disposed so as to be relatively movable with respect to the metal tube 14 along the central axis of the insertion portion 505. An actuator 47 is connected to the holding portion 545.

Next, a method of imaging the inner wall of the body cavity 3 using the fluorescence endoscope 501 having the above configuration will be described.
Note that the method for fixing the insertion portion 505 by the balloon 15 and the method for controlling the distance from the inner wall of the body cavity 3 to the image sensor 43 are the same as those in the first embodiment, and a description thereof will be omitted.

Excitation light is emitted from the light source 7, and the excitation light is guided by the light guide 29 through the insertion portion 505 to the distal end side end portion of the insertion portion 5. The excitation light is emitted from the light guide 29 in a direction along the central axis of the insertion portion 5, passes through the irradiation lens 531, and enters the irradiation mirror 33. The excitation light is emitted as parallel light from the irradiation lens 531. The excitation light that has entered the irradiation mirror 533 is reflected toward the outside in the radial direction of the insertion portion 505, passes through the excitation light window 25 and the balloon 15, and enters the body cavity 3. The excitation light can illuminate the entire observation region in the body cavity 3 because the reflecting surface of the irradiation mirror 533 is a convex curved surface.
Since the subsequent effects are the same as those of the first embodiment, the description thereof is omitted.

  According to the above configuration, the lens diameter of the imaging lens system 541 that forms an image of fluorescence on the image sensor 43 can be increased as compared with the first embodiment, and the fluorescence of the image formed on the image sensor 43 can be increased. The amount of fluorescence can be increased. That is, a brighter fluorescent image can be captured as compared with the first embodiment.

[Second Embodiment]
Next, a second embodiment of the present invention will be described with reference to FIG. 21 and FIG.
The basic configuration of the fluorescence endoscope of the present embodiment is the same as that of the second modification of the first embodiment, but the configuration of the insertion portion is different from that of the second modification of the first embodiment. . Therefore, in this embodiment, only the periphery of the insertion portion will be described with reference to FIGS. 21 and 22, and description of other components and the like will be omitted.
FIG. 21 is a schematic diagram illustrating the configuration of the fluorescence endoscope in the present embodiment.
In addition, about the component same as the 2nd modification of 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 21, the fluorescence endoscope 601 has a distance between the insertion portion 605 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the distance between the insertion portion 605 and the inner wall of the body cavity 3. A measurement control unit 609 that performs measurement and a display unit 11 that displays the captured fluorescent image are provided.

FIG. 22 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 21, the insertion portion 605 is provided with an outer insertion portion (insertion portion) 613A and a rotation insertion portion (light emitting introduction portion, rotation portion) 613B.

  The outer insertion portion 613A is a tube that forms the outer peripheral surface of the insertion portion 605. A balloon 615 is disposed on the outer peripheral surface of the insertion side end (the left end in FIG. 22) of the outer insertion portion 613A. At least the region where the balloon 615 of the outer insertion portion 613A is disposed, and the region facing the excitation light window 225 and the fluorescence window 227, which will be described later, is used for excitation light and fluorescence transmitted through the excitation light window 225. It is desirable to be made of a material that transmits fluorescence that passes through the window 227.

  A fluorescent agent that generates fluorescence is disposed on the outer peripheral surface of the balloon 615 that contacts the body cavity 3. The fluorescent agent generates fluorescence when irradiated with excitation light emitted from the light source 7. The fluorescence generated from the fluorescent agent is fluorescence having a wavelength different from that generated from the body cavity 3 and is not reflected by the dichroic mirror 35. The fluorescent agent may be applied to the balloon 615 or may be included as a part of a film component constituting the balloon 615, and is not particularly limited.

  The rotation insertion portion 613B is inserted into the outer insertion portion 613A. As shown in FIG. 22, the rotation insertion unit 613 </ b> B includes an excitation light window 225, a fluorescence window 227, an irradiation unit (light emission introduction unit) 217, an introduction unit (light emission introduction unit) 219, and imaging. A unit 21, a moving unit 23, and a fluorescence detection unit 624 are provided.

  The fluorescence detection unit 624 detects the fluorescence intensity of the fluorescence generated from the fluorescent agent disposed on the balloon 615. The fluorescence detection unit 624 is disposed at a position facing the fluorescence window 227 so that the dichroic mirror 35 is sandwiched between the fluorescence detection unit 624 and the fluorescence window 227. A signal related to the fluorescence intensity detected by the fluorescence detection unit 624 is output to the actuator drive unit 653 as shown in FIG. The actuator driving unit 653 can be a known element such as a CCD or CMOS, and is not particularly limited.

  The measurement control unit 609 measures the distance between the insertion unit 605 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. As shown in FIG. 21, the measurement control unit 609 includes an air supply pump 49 and an actuator driving unit (calculation unit) 653.

  The actuator driving unit 653 measures the distance between the insertion unit 605 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. A signal related to the fluorescence intensity is input from the actuator driving unit 653 to the actuator driving unit 653, and the actuator driving unit 653 can obtain the distance between the insertion unit 605 and the inner wall of the body cavity 3 based on the signal.

Next, a method for imaging the inner wall of the body cavity 3 using the fluorescence endoscope 601 having the above configuration will be described.
Note that the method of fixing the outer insertion portion 613A to the body cavity 3 by the balloon 615 and the operation until the excitation light is emitted from the light source 7 to the body cavity 3 are the same as those in the first embodiment, so the description thereof will be given. Omitted.

When the excitation light is applied to the body cavity 3, the excitation light is also applied to the fluorescent agent of the balloon 615 at the same time. Therefore, fluorescence is generated from the body cavity 3 and the fluorescent agent.
The fluorescence generated from the fluorescent agent passes through the outer insertion portion 613A and the fluorescence window 227 and enters the rotation insertion portion 613B. The incident fluorescence passes through the dichroic mirror 35 and enters the fluorescence detection unit 624. The fluorescence detection unit 624 outputs a signal related to the fluorescence intensity to the actuator driving unit 653 based on the fluorescence intensity of the incident fluorescence.

  The actuator driving unit 653 first obtains the distance from the outer peripheral surface of the balloon 615 to the actuator driving unit 653 based on the input signal related to the fluorescence intensity. Then, the actuator driving unit 653 calculates the distance from the inner wall of the body cavity 3 to the image sensor 43 based on the distance from the outer peripheral surface of the balloon 615 to the actuator driving unit 653, and the calculated distance is a predetermined constant. The actuator 47 is controlled so as to be the distance.

  On the other hand, the imaging method of the fluorescence generated from the body cavity 3 is the same as that of the second modification of the first embodiment, and thus the description thereof is omitted.

  According to the above configuration, the excitation light emitted radially outward of the insertion portion 605 is irradiated to the fluorescent agent disposed on the contact surface with the inner wall of the balloon 615, and the fluorescent agent irradiated with the excitation light is irradiated from the fluorescent agent. Fluorescence is generated. The fluorescence intensity of the generated fluorescence is detected by the fluorescence detection unit 624. Here, since the fluorescence intensity is inversely proportional to the square of the distance from the fluorescent agent, the fluorescence intensity signal output from the fluorescence detection unit 624 can be regarded as a signal related to the distance between the fluorescence agent and the fluorescence detection unit 624. it can. Therefore, based on the fluorescence intensity signal, the measurement control unit 609 can keep the distance from the inner wall to the image sensor 43 of the image sensor 43 at a predetermined constant distance.

[First Modification of Second Embodiment]
Next, a first modification of the second embodiment of the present invention will be described with reference to FIGS.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the second embodiment, but the configuration of the insertion portion is different from that of the second embodiment. Therefore, in this modification, only the periphery of the insertion portion will be described with reference to FIGS. 23 and 24, and description of other components and the like will be omitted.
FIG. 23 is a schematic diagram illustrating the configuration of the fluorescence endoscope according to the present embodiment.
In addition, about the component same as 2nd Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 23, the fluorescence endoscope 701 has a distance between the insertion portion 705 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 705 and the inner wall of the body cavity 3. A measurement control unit 709 that performs measurement and a display unit 11 that displays the captured fluorescent image are provided.

FIG. 24 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 23, the insertion portion 705 is provided with an outer insertion portion (insertion portion) 713A and a rotation insertion portion (light emitting introduction portion, rotation portion) 713B.

  The outer insertion portion 713A is a tube constituting the outer peripheral surface of the insertion portion 705, and the rotation insertion portion 713B is inserted therein. A balloon 15 is disposed on the outer peripheral surface of the insertion side end (the left side end in FIG. 24) of the outer insertion portion 713A. At least the region where the balloon 15 of the outer insertion portion 713A is disposed, and the region facing the excitation light window 225 and the fluorescence window 227, which will be described later, is used for excitation light and fluorescence transmitted through the excitation light window 225. It is desirable to be made of a material that transmits fluorescence that passes through the window 227. Further, it is desirable that the outer insertion portion 713A is made of a hard material with good ultrasonic transmission.

  The rotation insertion portion 713B is inserted into the outer insertion portion 713A. As shown in FIG. 24, the rotation insertion unit 713B includes an excitation light window 225, a fluorescence window 227, an irradiation unit 217, an introduction unit 219, an imaging unit 21, a moving unit 23, and ultrasonic wave generation. And a measurement unit (ultrasonic signal generator, ultrasonic signal detector) 724.

  The ultrasonic generation measurement unit 724 measures the distance from the rotary insertion unit 713 </ b> B to the contact surface of the balloon 15 with the body cavity 3. The ultrasonic wave generation and measurement unit 724 measures ultrasonic waves that have been generated toward the outside of the rotary insertion unit 713B and propagated inside the rotary insertion unit 713B. The ultrasonic generation measurement unit 724 receives a control signal for controlling the phase and the like of ultrasonic waves generated from the control unit 754 described later, and the ultrasonic generation measurement unit 724 controls the measured ultrasonic wave. A measurement signal related to the phase of the sound wave is output. The ultrasonic wave generation measuring unit 724 is arranged on the radially outer side of the distal end side end portion of the rotary insertion unit 713B. At a position adjacent to the ultrasonic wave generation and measurement unit 724, a cover 725 constituting a part of the outer peripheral surface of the rotation insertion unit 713B is disposed. The cover 725 is preferably formed of a hard material having good ultrasonic transmission.

  The measurement control unit 709 measures the distance between the insertion unit 605 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. As shown in FIG. 24, the measurement control unit 709 includes a pump (inflow unit) 749, an actuator driving unit 753, and a control unit 754.

  The pump 749 inflates the balloon 15 by pumping a liquid (for example, water). The liquid pumped from the pump 749 is sent to the balloon 15 through the pumping tube 755. In addition, as a pump 749, a well-known pump can be used and it does not specifically limit.

  The control unit 754 controls the ultrasonic generation measurement unit 724 and measures the distance from the inner wall of the body cavity 3 to the ultrasonic generation measurement unit 724. The control unit 754 outputs a control signal for controlling the generation and stop of the ultrasonic wave, the phase of the generated ultrasonic wave, and the like to the ultrasonic wave generation and measurement unit 724, and for the actuator driving unit 753, A signal related to the obtained distance from the inner wall of the body cavity 3 to the ultrasonic wave generation and measurement unit 724 is output. On the other hand, a measurement signal such as the phase of the measured ultrasonic wave is input from the ultrasonic wave generation measurement unit 724 to the control unit 754.

Next, a method for imaging the inner wall of the body cavity 3 using the fluorescence endoscope 701 having the above configuration will be described.
Note that the method of fixing the outer insertion portion 713A to the body cavity 3 by the balloon 15 and the method of imaging the fluorescence generated from the body cavity 3 are the same as in the first embodiment, and thus the description thereof is omitted.

  Next, a method for measuring the distance from the inner wall of the body cavity 3 to the ultrasonic wave generation measuring unit 724, which is a feature of the present embodiment, will be described.

  In a state where the outer insertion portion 713A is fixed to the body cavity 3 by the balloon 15, the control unit 754 outputs a control signal for generating an ultrasonic wave to the ultrasonic wave generation measuring unit 724. The ultrasonic wave generation control unit 754 to which the control signal is input generates an ultrasonic wave based on the control signal. The ultrasonic wave propagates through the liquid in the cover 725, the outer insertion portion 713 </ b> A, and the balloon 15, and is reflected on the outer peripheral surface that is a contact surface between the balloon 15 and the body cavity 3. The reflected ultrasonic waves propagate through the liquid in the balloon 15, the outer insertion portion 713 </ b> A, and the cover 725, and are detected by the ultrasonic wave generation / measurement unit 724. The ultrasonic generation measurement unit 724 outputs a measurement signal including information such as the phase of the reflected ultrasonic wave to the control unit 754.

  The control unit 754 determines the distance from the inner wall of the body cavity 3 to the ultrasonic generation measurement unit 724 based on the measurement signal input from the ultrasonic generation measurement unit 724 and the control signal output to the ultrasonic generation measurement unit 724. calculate. Specifically, the control unit 754 calculates the distance based on the phase difference between the ultrasonic wave generated from the ultrasonic wave generation and measurement unit 724 and the ultrasonic wave measured by the ultrasonic wave generation and measurement unit 724. A signal related to the calculated distance is output from the control unit 754 to the actuator driving unit 753.

  According to said structure, an ultrasonic wave is generate | occur | produced toward the said contact surface of the balloon 15 from the ultrasonic generation measurement part 724, and propagates the inside of the balloon 15 filled with the liquid. Since the balloon 15 is filled with the liquid, the ultrasonic attenuation rate is lower than that in the case where the balloon 15 is filled with the gas. The ultrasonic wave propagated in the balloon 15 is reflected on the contact surface and is detected by the ultrasonic wave generation measuring unit 724.

The control unit 754 controls the ultrasonic wave generated by controlling the ultrasonic wave generation and measurement unit 724, and the detection signal output from the ultrasonic wave generation and measurement unit 724 is input to the control unit 754. Therefore, the control unit 754 obtains the distance between the contact surface and the insertion unit 705 based on the phase difference between the phase of the ultrasonic wave generated from the ultrasonic wave generation and measurement unit 724 and the phase of the detected ultrasonic wave. be able to.
Therefore, based on the distance obtained by the control unit 754, the moving unit 23 can keep the distance from the inner wall to the image pickup device 43 of the image pickup unit 21 at a predetermined constant distance.

[Second Modification of Second Embodiment]
Next, a second modification of the second embodiment of the present invention will be described with reference to FIG. 25 and FIG.
The basic configuration of the fluorescence endoscope of this modification is the same as that of the second embodiment, but the configuration of the insertion portion is different from that of the second embodiment. Therefore, in this modification, only the periphery of the insertion portion will be described with reference to FIGS. 25 and 26, and description of other components and the like will be omitted.
FIG. 25 is a schematic diagram illustrating the configuration of the fluorescence endoscope in the present embodiment.
In addition, about the component same as 2nd Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.

  As shown in FIG. 25, the fluorescence endoscope 801 determines the distance between the insertion portion 805 inserted into the body cavity 3 of the subject, the light source 7 that emits excitation light, and the insertion portion 805 and the inner wall of the body cavity 3. A measurement control unit 809 that performs measurement and a display unit 11 that displays the captured fluorescent image are provided.

FIG. 26 is a schematic diagram illustrating the configuration of the insertion portion in FIG.
As shown in FIG. 25, the insertion portion 805 is provided with an outer insertion portion (insertion portion) 813A and a rotation insertion portion (light emission introduction portion, rotation portion) 813B.

  The outer insertion portion 813A is a tube constituting the outer peripheral surface of the insertion portion 805. A balloon 15 is disposed on the outer peripheral surface of the insertion side end (the left end in FIG. 26) of the outer insertion portion 813A. At least the region where the balloon 15 of the outer insertion portion 813A is disposed and the region facing the excitation light window 225 and the fluorescence window 227, which will be described later, is the excitation light and fluorescence light transmitted through the excitation light window 225. It is desirable to be made of a material that transmits fluorescence that passes through the window 227. Moreover, it is desirable that the outer insertion portion 713A be formed from a material having good microwave transmission.

  The rotary insertion portion 813B is inserted into the outer insertion portion 813A. As shown in FIG. 26, the rotation insertion unit 813B includes an excitation light window 225, a fluorescence window 227, an irradiation unit 217, an introduction unit 219, an imaging unit 21, a moving unit 23, and microwave generation. And a measurement unit (microwave signal generator, microwave signal detector) 824.

  The microwave generation measurement unit 824 measures the distance from the rotary insertion unit 813B to the contact surface of the balloon 15 with the body cavity 3. The microwave generation measurement unit 824 generates microwaves toward the outside of the rotation insertion unit 813B and measures the microwave propagated inside the rotation insertion unit 813B. The microwave generation measurement unit 824 receives a control signal for controlling the phase or the like of the generated microwave from a control unit 854 described later, and is measured from the microwave generation measurement unit 824 to the control unit 854. A measurement signal related to the phase of the microwave is output. The microwave generation measurement unit 824 is disposed on the radially outer side of the distal end side end portion of the rotation insertion unit 813B. At a position adjacent to the microwave generation measurement unit 824, a cover 825 constituting a part of the outer peripheral surface of the rotation insertion unit 813B is disposed. The cover 825 is preferably formed from a material having good microwave transmission.

  The measurement control unit 809 measures the distance between the insertion unit 805 and the inner wall of the body cavity 3 and controls the distance between the image sensor 43 and the inner wall of the body cavity 3 to a predetermined constant distance. As shown in FIG. 26, the measurement control unit 809 includes an air supply pump 49, an actuator drive unit 853, and a control unit 854.

  The control unit 854 controls the microwave generation measurement unit 824 and measures the distance from the inner wall of the body cavity 3 to the microwave generation measurement unit 824. The control unit 854 outputs a control signal for controlling the generation and stop of the microwave and the phase of the generated ultrasonic wave to the microwave generation measurement unit 824, and for the actuator drive unit 853, A signal related to the obtained distance from the inner wall of the body cavity 3 to the microwave generation measurement unit 824 is output. On the other hand, a measurement signal such as a measured microwave phase is input from the microwave generation measurement unit 824 to the control unit 854.

Next, a method for imaging the inner wall of the body cavity 3 using the fluorescence endoscope 801 having the above configuration will be described.
Note that the method for fixing the outer insertion portion 813A to the body cavity 3 by the balloon 15 and the method for imaging the fluorescence generated from the body cavity 3 are the same as those in the first embodiment, and thus the description thereof is omitted.

  Next, a method for measuring the distance from the inner wall of the body cavity 3 to the microwave generation measurement unit 824, which is a feature of the present embodiment, will be described.

  In a state where the outer insertion portion 813A is fixed to the body cavity 3 by the balloon 15, the control unit 854 outputs a control signal for generating a microwave to the microwave generation measuring unit 824. The microwave generation measurement unit 824 to which the control signal is input generates a microwave based on the control signal. The microwave propagates through the cover 825, the outer insertion portion 813 </ b> A, and the balloon 15, and is reflected on the outer peripheral surface that is a contact surface between the balloon 15 and the body cavity 3. The reflected microwave propagates through the balloon 15, the outer insertion portion 813 A, and the cover 825 and is detected by the microwave generation measurement unit 824. The microwave generation measurement unit 824 outputs a measurement signal including information such as the phase of the reflected microwave to the control unit 854.

  The control unit 854 determines the distance from the inner wall of the body cavity 3 to the microwave generation measurement unit 824 based on the measurement signal input from the microwave generation measurement unit 824 and the control signal output to the microwave generation measurement unit 824. calculate. Specifically, the control unit 854 calculates the distance based on the phase difference between the microwave generated from the microwave generation measurement unit 824 and the microwave measured by the microwave generation measurement unit 824. A signal related to the calculated distance is output from the control unit 854 to the actuator driving unit 853.

  According to the above configuration, the microwave is generated from the microwave generation measurement unit 824 toward the contact surface of the balloon 15 and propagates in the balloon 15. Here, the microwave propagates in the balloon 15 with a lower attenuation rate than the ultrasonic wave. The microwave propagated in the balloon 15 is reflected on the contact surface and detected by the microwave generation measurement unit 824.

The control unit 854 controls the microwave generated by controlling the microwave generation measurement unit 824, and the detection signal output from the microwave generation measurement unit 824 is input to the control unit 854. Therefore, the control unit 854 obtains the distance between the contact surface and the insertion unit 805 based on the phase difference between the phase of the microwave generated from the microwave generation measurement unit 824 and the detected phase of the microwave. be able to.
Therefore, based on the distance obtained by the control unit 854, the moving unit 23 can keep the distance from the inner wall to the imaging element 43 of the imaging unit 21 at a predetermined constant distance.

The technical scope of the present invention is not limited to the above embodiment, and various modifications can be made without departing from the spirit of the present invention.
For example, in the first modification of the first embodiment, instead of measuring the flow rate of the balloon in order to obtain the distance between the inner wall of the body cavity and the insertion portion, ultrasonic waves are generated at the distal end portion of the measurement insertion portion. A measuring part can be provided.

It is a schematic diagram explaining the structure of the fluorescence endoscope of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a perspective view explaining the structure of the lens for irradiation of FIG. It is a perspective view explaining the structure of the reflective mirror of FIG. It is AA sectional drawing explaining the structure of the holding | maintenance part of FIG. It is a flowchart explaining the control method of the actuator of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 1st modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the conical mirror of FIG. It is a figure which shows the fluorescence image imaged by the image pick-up element of FIG. It is a figure which shows the image after the conversion process by the fluorescence signal process part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 2nd modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 3rd modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 4th modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a front view explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 5th modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 6th modification of the 1st Embodiment of this invention. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 2nd Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 1st modification of the 2nd Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG. It is a schematic diagram explaining the structure of the fluorescence endoscope in the 2nd modification of the 2nd Embodiment of this invention. It is a schematic diagram explaining the structure of the insertion part of FIG.

Explanation of symbols

1, 101, 201, 301, 401, 501, 601, 701, 801, 901 Fluorescence endoscope 3 body cavity 5, 105, 205, 305, 4005, 505, 605, 705, 805, 905 Insertion unit 15 Balloon 17, 217, 417, 517 Irradiation part (light emission introduction part)
19,119,219 Introduction part (light emission introduction part)
21, 421, 521 Imaging unit 23, 423, 523 Moving unit 35 Dichroic mirror (reflecting unit)
37 Drive motor (rotary drive)
49 Air supply pump (inflow part)
51 Flowmeter (Flow measurement unit)
53 Actuator drive unit (calculation unit)
135 Conical mirror (reflection part)
157 Fluorescence signal processing unit (image processing unit)
161 Image sensor (insertion length measurement unit)
213A, 413A, 613A, 713A, 813A Outside insertion part (insertion part)
213B, 313B, 413B, 613B, 713B, 813B, 913B Rotation insertion part (light emission introduction part, rotation part)
609 Measurement control unit (moving unit)
653 Actuator drive unit (calculation unit)
624 Fluorescence detection unit 724 Ultrasonic wave generation measurement unit (ultrasonic signal generator, ultrasonic signal detector)
749 Pump (inflow part)
754,854 Control unit 824 Microwave generation measurement unit (microwave signal generator, microwave signal detector)

Claims (11)

An insertion part to be inserted into the body cavity;
A balloon for positioning the insertion portion relative to the body cavity in the radial direction of the insertion portion by contacting an inner wall of the body cavity located in a radial direction of the insertion portion;
Excitation light emitted to the inner wall is emitted radially outward of the insertion portion, and fluorescence generated from the inner wall and transmitted through the balloon is transmitted from a plurality of different radial directions of the insertion portion. A light emission introduction part to be introduced into the interior of
An imaging unit for imaging fluorescence introduced from the light emission introducing unit;
A moving unit that moves the imaging unit along an optical axis of fluorescence incident on the imaging unit based on a distance between a contact surface of the balloon with the inner wall and the insertion unit;
Fluorescent endoscope provided with The light emitting introduction part emits the excitation light radially outward of the insertion part; and
Reflecting the fluorescence generated from the inner wall toward the central axis direction of the insertion portion, and a reflection portion arranged to be rotatable around the central axis,
With
The fluorescence endoscope according to claim 1, wherein the imaging unit images fluorescence reflected from the reflection unit.   The fluorescent endoscope according to claim 2, further comprising a rotation driving unit that rotates the reflection unit. The light emission introduction portion is disposed at least inside the distal end portion of the insertion portion, and a rotation portion that is disposed so as to be rotatable around a central axis of the insertion portion;
An irradiating unit that is provided in the rotating unit and emits the excitation light radially outward of the insertion unit;
A reflecting portion provided in the rotating portion and reflecting the fluorescence generated from the inner wall toward the central axis direction;
With
The fluorescence endoscope according to claim 1, wherein the imaging unit is provided in the rotating unit and images fluorescence reflected from the reflecting unit. The light emission introduction portion is disposed at least inside the distal end portion of the insertion portion, and a rotation portion that is disposed so as to be rotatable around a central axis of the insertion portion;
An irradiating unit that is provided in the rotating unit and emits the excitation light radially outward of the insertion unit;
With
The fluorescence endoscope according to claim 1, wherein the imaging unit images fluorescence introduced into the rotating unit. The light emitting introduction part emits the excitation light radially outward of the insertion part; and
A conical mirror that reflects the fluorescence generated from the inner wall in the direction of the central axis of the insertion portion;
With
The fluorescence endoscope according to claim 1, wherein the imaging unit images fluorescence reflected from the conical mirror. An insertion length measurement unit for measuring the insertion length of the insertion unit with respect to the body cavity;
An image processing unit that performs an expansion process of the imaging signal based on an imaging signal output from the imaging unit and a signal related to an insertion length output from the insertion length measurement unit;
The fluorescence endoscope according to any one of claims 1 to 6, further comprising: An inflow portion for allowing fluid to flow into the balloon;
A flow rate measuring unit for measuring the flow rate of the fluid flowing into the balloon;
Based on the flow rate signal output from the flow rate measurement unit, a calculation unit for obtaining a distance between the contact surface of the balloon with the inner wall and the insertion unit is provided,
The fluorescence endoscope according to any one of claims 1 to 7, wherein the moving unit moves the imaging unit along the central axis direction based on a distance obtained by the calculation unit. A fluorescent agent is disposed on a contact surface of the balloon with the inner wall,
A fluorescence detector for detecting the intensity of fluorescence generated from the fluorescent agent is provided;
The fluorescence endoscope according to any one of claims 1 to 7, wherein the moving unit moves the imaging unit based on a fluorescence intensity signal output from the fluorescence detection unit. The fluid flowing into the balloon is a liquid,
An ultrasonic signal generator for generating ultrasonic waves toward a contact surface of the balloon with the inner wall;
An ultrasonic signal detector for detecting ultrasonic waves reflected from the contact surface;
A control unit that controls the ultrasonic signal generator and obtains a distance between a contact surface of the balloon with the inner wall and the insertion unit based on a detection signal output from the ultrasonic signal detector; Is provided,
The fluorescence endoscope according to any one of claims 1 to 7, wherein the moving unit moves the imaging unit along the central axis direction based on a distance obtained by the control unit. A microwave signal generator for generating a microwave toward a contact surface of the balloon with the inner wall;
A microwave signal detector for detecting the microwave reflected from the contact surface;
A control unit for controlling the microwave signal generator and for obtaining a distance between a contact surface of the balloon with the inner wall and the insertion unit based on a detection signal output from the microwave signal detector; Is provided,
The fluorescence endoscope according to any one of claims 1 to 7, wherein the moving unit moves the imaging unit along the central axis direction based on a distance obtained by the control unit.

Images