JP2012183216A - Endoscope apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To irradiate both of a leading end direction and a side direction of an insertion part of an endoscope with illumination light, and to optionally adjust the light amount of the illumination light irradiated to the directions.SOLUTION: An optical fiber wherein a fluorescent substance extended in the insertion part and emitting fluorescence having a wavelength contained in the illumination light by irradiation of excitation light is contained in a clad is extended in the insertion part. On a side surface of the insertion part, a transmitting part 30g transmitting the fluorescence emitted from the clad of the optical fiber is provided, and a light-blocking member 35 for adjusting the light amount of the fluorescence irradiated to the side direction of the insertion part by transmitting the transmitting part 30g.

Description

  The present invention relates to an endoscope apparatus that includes an insertion portion that is inserted into a body, and that irradiates illumination light to a portion to be observed in the body by the insertion portion.

  Conventionally, endoscope systems for observing tissue in a body cavity are widely known. A normal image is obtained by imaging a portion to be observed in a body cavity by irradiation with white illumination light, and this normal image is displayed on a monitor screen. Electronic endoscope systems that are displayed on the screen have been widely put into practical use.

  As such an endoscope system, for example, a system using a rigid endoscope has been put into practical use. In this rigid endoscope, the illumination light emitted from the light source device is transmitted to the observed portion near the distal end of the rigid endoscope. In order to guide the light, a light guide made of an optical fiber is generally employed.

JP 2010-51461 A

  However, since the optical fiber generally propagates light only in front of it (in the direction opposite to the light receiving side), it can irradiate illumination light only to the observed portion in the distal direction of the rigid endoscope.

  On the other hand, in the case of scleroscopic surgery, the presence or absence of bleeding in parts other than the observed part, interference between treatment tools such as forceps, interference between forceps and an organ, etc. are also important concerns for doctors. However, such a matter cannot be observed with a rigid endoscope system using a general optical fiber.

  On the other hand, in Patent Document 1, for example, by providing an organic light emitting layer at the distal end portion of an endoscope as an illumination light source, illumination light can be irradiated not only in the distal end direction of the endoscope but also in the lateral direction. Although proposed, the endoscope of Patent Document 1 enables irradiation of illumination light in the distal direction and the lateral direction by simply forming an organic light emitting layer from the distal end of the endoscope along the side surface. Therefore, it is not possible to adjust the amount of illumination light irradiated in the distal direction and the lateral direction.

  However, if you want to irradiate illumination light only in the distal direction or only to the side of the endoscope, or change the ratio of the amount of illumination light irradiated to the distal direction and side, give priority to illumination in either direction. Sometimes you want to do it.

  The present invention has been made in view of the above problems, and can illuminate illumination light in both the distal direction and the lateral direction of the insertion portion of the endoscope, and illumination illuminated in these directions. An object of the present invention is to provide an endoscope apparatus capable of arbitrarily adjusting the amount of light.

  An endoscope apparatus according to the present invention is inserted into a body, irradiates an observation part in the body with illumination light, and receives an light emitted from the observation part by irradiation of the illumination light, and an insertion part And an optical fiber in which a phosphor that emits fluorescence having a wavelength included in illumination light by irradiation of excitation light is contained in a clad, wherein the optical fiber is disposed on a side surface of the insertion portion. A transmissive portion that transmits fluorescence emitted from the cladding is provided, and includes a light shielding member that adjusts the amount of fluorescent light that is transmitted through the transmissive portion and irradiated toward the side of the insertion portion. .

  In the endoscope apparatus of the present invention, the light shielding member is an oversheath formed in a cylindrical shape so as to cover the transmission part of the insertion part, and the oversheath is movable in the longitudinal direction of the insertion part. Can be configured.

  Further, the oversheath shall be configured such that a portion that transmits fluorescence emitted from the clad of the optical fiber and a portion that shields light are arranged side by side in the circumferential direction and configured to be rotatable in the circumferential direction. it can.

  Further, the surface of the oversheath on the transmission part side can be formed so that the fluorescence transmitted through the transmission part is reflected toward the distal end of the insertion part.

  In addition, a plurality of reflection surfaces that reflect fluorescence toward the distal end of the insertion portion can be formed on the surface of the oversheath on the transmission portion side.

  Further, the light shielding member may be a shutter provided between the side surface of the optical fiber in the insertion portion and the transmission portion, and the shutter can be configured to be movable in the longitudinal direction of the insertion portion.

  In addition, the shutter is formed in a cylindrical shape, and the part that transmits the fluorescence emitted from the clad of the optical fiber and the part that shields light are arranged side by side in the circumferential direction and can be rotated in the circumferential direction. Can be configured.

  In addition, an image pickup device for receiving and imaging light emitted from the observed portion is provided in the distal end portion of the insertion portion, and the side surface of the optical fiber extending in the vicinity of the image pickup device is covered by a light shielding cover that blocks fluorescence. Can be coated.

  In addition, it is possible to provide a side image sensor that receives and captures light reflected from a peripheral region on the side of the insertion portion by fluorescence irradiation.

  In addition, a wide-angle lens that receives the light in the lateral peripheral region and forms an image on the lateral imaging device can be provided on the side surface of the insertion portion.

  Further, a side image sensor can be provided in the vicinity of the transmission part.

  According to the endoscope apparatus of the present invention, an optical fiber in which a phosphor emitting fluorescence having a wavelength included in illumination light is contained in the cladding extends into the insertion portion, and the side surface of the insertion portion extends from the optical fiber cladding. Since a transmission part that transmits the emitted fluorescence is provided, and a light shielding member is provided for adjusting the amount of fluorescent light that is transmitted through the transmission part and directed toward the side of the insertion part. While it is possible to irradiate illumination light in both the distal direction and the lateral direction, the amount of illumination light irradiated in these directions can be arbitrarily adjusted by the light shielding member.

  Then, as described above, by enabling illumination light to be irradiated to the side, for example, by inserting a small-diameter camera from the body surface, the inside of the body cavity can be observed from above. If the camera provided on the body surface is also provided with an illumination function, the diameter of the hole provided on the body surface increases and the invasiveness increases. If a camera that does not have an illumination function is used, a thin lens camera with a diameter of about 2 mm can be used. If such an incision has a diameter of about 2 mm, natural healing can be expected. As much invasiveness as possible can be achieved.

Schematic configuration diagram of a rigid endoscope system using an embodiment of an endoscope apparatus of the present invention Schematic configuration diagram of body cavity insertion part Schematic configuration diagram of the distal end of the body cavity insertion part 4-4 'sectional view of FIG. Diagram showing the structure of a phosphor-containing optical fiber The figure which shows blue light spectrum S1 and the green-yellow fluorescence spectrum S2 emitted from the fluorescent substance of a fluorescent substance containing optical fiber The figure for demonstrating the structure and effect | action of an oversheath The figure which shows schematic structure of an imaging unit The figure which shows schematic structure of a processor and a light source device The figure for demonstrating the effect | action of the rigid endoscope system using one Embodiment of the endoscope apparatus of this invention. The figure which shows other embodiment of an oversheath The figure which shows one Embodiment of a shutter The figure which shows other embodiment of a shutter The figure which shows embodiment which provided the image pick-up element in the front-end | tip of an insertion member The figure which shows embodiment which provided the camera unit for side imaging | photography

  Hereinafter, a rigid endoscope system using an embodiment of an endoscope apparatus of the present invention will be described in detail with reference to the drawings. The present embodiment is characterized by the configuration for irradiating the observation part with illumination light. First, the configuration of the entire system will be described. FIG. 1 is an external view showing a schematic configuration of a rigid endoscope system 1 of the present embodiment.

  As shown in FIG. 1, the rigid endoscope system 1 of the present embodiment includes a light source device 2 that emits blue light that is excitation light, and white light obtained by wavelength-converting blue light emitted from the light source device 2 to be observed. The rigid mirror imaging device 10 that captures a visible image based on the reflected light reflected from the observed portion by the irradiation of the white light, and a predetermined process on the image signal captured by the rigid mirror imaging device 10 And a processor 3 that outputs a control signal to the light source device 2 and a monitor 4 that displays a visible image of the observed portion based on the display control signal generated by the processor 3.

  As shown in FIG. 1, the rigid endoscope imaging apparatus 10 is an imaging unit that captures a visible image of a body cavity insertion unit 30 that is inserted into a body such as an abdominal cavity or a chest cavity, and a portion to be observed guided by the body cavity insertion unit 30. 20.

  As shown in FIG. 2, the rigid endoscope imaging apparatus 10 has a body cavity insertion unit 30 and an imaging unit 20 that are detachably connected. The body cavity insertion portion 30 includes a connection member 30a, an insertion member 30b, and a cable connection port 30c.

  The connection member 30a is provided on one end side 30X of the body cavity insertion part 30 (insertion member 30b). For example, the connection member 30a is fitted into an opening 20a formed on the imaging unit 20 side, whereby the imaging unit 20 and the body cavity insertion part 30 are connected. Are detachably connected.

  The insertion member 30b is inserted into the body cavity when photographing inside the body cavity, and is formed of a hard material and has, for example, a cylindrical shape with a diameter of about 5 mm. A relay lens (to be described later) for forming an image of the observed portion is accommodated inside the insertion member 30b, and the visible image of the observed portion incident from the distal end side 30Y passes through the relay lens. The light is emitted to the imaging unit 20 side of the one end side 30X.

  A cable connection port 30c is provided on the side surface of the insertion member 30b, and the optical cable LC is mechanically connected to the cable connection port 30c. Thereby, the light source device 2 and the insertion member 30b are optically connected via the optical cable LC.

  Further, as shown in FIG. 1, an oversheath 35 formed in a cylindrical shape is provided in the vicinity of the distal end portion of the insertion member 30b. The oversheath 35 is formed of, for example, a light-shielding resin. The action of the oversheath 35 will be described in detail later.

  Further, as shown in FIGS. 2 and 3, an imaging lens 30d that forms a visible image reflecting the observed portion is provided at the distal end surface of the distal end portion 30Y of the insertion member 30b. Irradiation windows 30e and 30f that irradiate white light substantially symmetrically with the lens 30d interposed therebetween are provided. The irradiation windows 30e and 30f are formed by polishing the tip of a bundled phosphor-containing optical fiber, which will be described later.

  Further, as shown in FIG. 2, a plurality of rectangular transmissive portions 30g extending in the longitudinal direction of the insertion member 30b are formed on the side surface of the distal end portion 30Y of the insertion member 30b in the circumferential direction at predetermined intervals. Yes. This transmission part 30g is comprised from the member which permeate | transmits the illumination light emitted from the clad of the fluorescent substance containing optical fiber mentioned later extended in the insertion member 30b, for example, is comprised from transparent resin or glass. Is. The transmission part 30g may be a simple space.

  FIG. 4 is a sectional view taken along line 4-4 ′ of the distal end portion 30Y of the insertion member 30b shown in FIG. As shown in FIG. 4, a relay lens 32 for guiding a visible image incident on the imaging lens 30 d to the imaging unit 20 is provided at the center of the body cavity insertion portion 30, and the relay lens 32. Are bundled with a large number of phosphor-containing optical fibers 31 in a substantially symmetrical position. This bundle fiber is bundled so that the tip surface thereof forms crescent-shaped irradiation windows 30e and 30f as shown in FIGS.

  The phosphor-containing optical fiber 31 extended in the insertion member 30b is a multimode optical fiber composed of a core 31a and a clad 31b, as shown in FIG. Specifically, for example, a core having a core diameter of 105 [mu] m, a cladding diameter of 125 [mu] m, and a diameter including a protective layer (not shown) as an outer skin of 0.3 mm to 0.5 mm can be used.

In the clad 31b of the phosphor-containing optical fiber 31, a part of the blue light L1 emitted from the light source device 2 is absorbed and excited, and a phosphor 31c that emits green to yellow fluorescence L2 is dispersed. Contained. As the phosphor 31c, for example, a phosphor formed of a plurality of types of phosphors can be used, such as a YAG phosphor or a phosphor containing a phosphor such as BAM (BaMgAl ₁₀ O ₁₇ ). it can.

  FIG. 6 shows the blue light spectrum S1 of the blue light L1 emitted from the light source device 2, and the green to yellow fluorescence spectrum S2 emitted from the phosphor 31c of the phosphor-containing optical fiber 31.

  Blue light L1 is incident on one end of the phosphor-containing optical fiber 31, and the blue light L1 propagates while being totally reflected in the core 31a, and part of the propagated blue light L1 leaks to the clad 31b side. . The leaked blue light L1 excites the phosphor 31c in the clad 31b to emit green to yellow fluorescence L2, and this fluorescence L2 propagates toward the tip while totally reflecting the blue light L1 in the core 31a. At the same time, the blue light L1 leaks out of the cladding 31b. By such an action, the light of the two spectra shown in FIG. 6 is emitted from the tip of the phosphor-containing optical fiber 31, and the same two spectra of light are emitted from the side surface of the phosphor-containing optical fiber 31. Become.

  Then, the blue light L1 and the green to yellow fluorescence L2 are mixed to become white light, which is emitted from the tip and side surfaces of the phosphor-containing optical fiber 31 as illumination light.

  Illumination light emitted from the clad 31b of the phosphor-containing optical fiber 31 in the insertion member 30b is transmitted through the transmission part 30g provided on the side surface of the insertion member 30b and emitted to the outside. Thereby, irradiation of illumination light from the side surface direction of the insertion member 30b becomes possible.

  As shown in FIGS. 1 and 7, a cylindrical oversheath 35 capable of covering part or all of the outer surface of the transmission part 30g is provided in the vicinity of the distal end part 30Y of the insertion member 30b. ing. The oversheath 35 is formed of a member that blocks the illumination light emitted from the transmission part 30g as described above, and is configured to be movable in the longitudinal direction of the insertion member 30b, that is, in the direction of arrow A shown in FIG. Has been. Thus, by moving the oversheath 35 in the direction of arrow A, it is possible to adjust the range covering the transmission part 30g, and thereby to adjust the amount of illumination light emitted from the transmission part 30g.

  As a method of configuring the oversheath 35 to be movable in the direction of arrow A, for example, the oversheath 35 can be moved between the oversheath 35 and the insertion member 30b, and the oversheath 35 is supported at a predetermined position. The oversheath 35 may be formed using a material that generates a certain amount of frictional force, or the outer peripheral surface of the oversheath 35 on the insertion member 36b side and the outer periphery of the insertion member 30b on the oversheath 35 side. On the surface, the oversheath 35 can be moved, and irregularities having a shape that allows the oversheath 35 to be supported at a predetermined position may be formed. As such an uneven structure, for example, a screw structure may be used. Alternatively, a wire or the like may be provided on the oversheath 35, and the oversheath 35 may be configured to be movable by pushing and pulling the wire.

  FIG. 8 is a diagram illustrating a schematic configuration of the imaging unit 20. The image pickup unit 20 includes an image pickup system that picks up a visible image of the observed portion formed by the relay lens 32 in the body cavity insertion portion 30 and generates an image signal.

  This imaging system includes an imaging optical system 21 that forms a visible image L3 emitted from the body cavity insertion unit 30, and an imaging element 22 that images the visible image L3 imaged by the imaging optical system 21. I have.

  The image sensor 22 detects light in the wavelength band of the visible image, converts it into an image signal, and outputs it. On the imaging surface of the imaging element 22, three primary color red (R), green (G) and blue (B) color filters are provided in a Bayer arrangement or a honeycomb arrangement.

  The imaging unit 20 includes an imaging control unit 23. The imaging control unit 23 drives and controls the imaging device 22 based on the CCD driving signal output from the processor 3, and performs CDS / AGC (correlated double sampling / automatic gain) on the image signal output from the imaging device 22. Control) processing and A / D conversion processing are performed and output to the processor 3 via a cable.

  FIG. 9 is a diagram showing a schematic configuration of the light source device 2 and the processor 3. As shown in FIG. 9, the processor 3 includes an image input controller 41, an image processing unit 42, a memory 43, a video output unit 44, an operation unit 45, a TG (timing generator) 46, and a control unit 47.

  The image input controller 41 includes a line buffer having a predetermined capacity, and temporarily stores an image signal for each frame output from the imaging control unit 23 of the imaging unit 20. The image signal stored in the image input controller 41 is stored in the memory 43 via the bus.

  The image processing unit 42 receives image signals for each frame read from the memory 43, performs predetermined image processing on these image signals, and outputs them to the bus.

  The video output unit 44 receives the image signal output from the image processing unit 43 via the bus, performs predetermined processing to generate a display control signal, and outputs the display control signal to the monitor 4. .

  The operation unit 45 receives input by an operator such as predetermined operation instructions and control parameters.

  The TG 46 outputs a driving pulse signal for driving the imaging element 22 of the imaging unit 20 and an LD driver 53 of the light source device 2 described later, and the control unit 47 controls the entire system.

  As shown in FIG. 9, the light source device 2 includes a blue LD light source 50 that emits 445 nm blue light, and a condensing lens that collects the blue light emitted from the blue LD light source 50 and enters the optical fiber splitter 52. 51, an optical fiber splitter 52 that simultaneously enters blue light incident by the condenser lens 51 into both the optical cable LC1 and the optical cable LC2, and an LD driver 53 that drives the blue LD light source 50.

  The optical cables LC1 and LC2 are each optically connected to the bundled phosphor-containing optical fiber 31 in the insertion member 30b via the cable connection port 30c.

  Next, the operation of the rigid endoscope system of this embodiment will be described.

  First, as shown in FIG. 10, the body cavity insertion part 30 is inserted into the body cavity of the subject, and the tip of the body cavity insertion part 30 is installed in the vicinity of the observation part (lesioned part). Further, a small hole is made in the body surface, and a small CCD camera 60 for overlooking the whole body cavity is installed in that portion. As this small CCD camera 60, a camera having no illumination function can be used, and an image pickup lens having a small diameter of 2 mm or less can be used. At this time, treatment tools 61 and 62 for performing a predetermined treatment are also inserted into the body cavity.

  Then, in the state as shown in FIG. 10, imaging of the entire lesioned part and the body cavity is performed.

  Specifically, the blue light emitted from the blue LD light source 50 of the light source device 2 is simultaneously incident on both the optical cables LC1 and LC2 via the condenser lens 51 and the optical fiber splitter 52. Further, the blue light is guided by the optical cables LC <b> 1 and LC <b> 2 and enters the body cavity insertion unit 30, and enters from one end of the bundled phosphor-containing optical fiber 31 in the body cavity insertion unit 30.

  When the blue light L1 is incident on one end of the phosphor-containing optical fiber 31, the blue light L1 propagates while being totally reflected in the core 31a, and part of the propagated blue light L1 leaks to the clad 31b side. It's out. The leaked blue light L1 excites the phosphor 31c in the clad 31b to emit green to yellow fluorescence L2, and this fluorescence L2 propagates toward the tip while totally reflecting the blue light L1 in the core 31a. At the same time, the blue light L1 leaks out of the cladding 31b.

  As a result, white light in which the blue light L1 and green to yellow fluorescence L2 are mixed is emitted from the tip and side surfaces of the phosphor-containing optical fiber 31 as illumination light.

  And the illumination light inject | emitted from the front end surface (irradiation window 30e, 30f) of the fluorescent substance containing optical fiber 31 in the insertion member 30b is irradiated to the to-be-observed part of the front end direction of the insertion member 30b, and fluorescent substance containing Illumination light emitted from the side surface of the optical fiber 31 passes through a transmission portion 30g provided on the side surface of the insertion member 30b, is emitted to the outside, and is irradiated to a range around the distal end portion of the insertion member 30b. At this time, the oversheath 35 provided at the distal end of the insertion member 30b is assumed to be installed by the user at a position where a desired amount of side irradiation is obtained.

  Then, a visible image reflected from the observed portion by irradiation of illumination light emitted from the distal end surface of the insertion member 30b is incident from the imaging lens 30d of the distal end portion 30Y of the insertion member 30b, and the relay lens in the insertion member 30b. The light is guided by 32 and emitted toward the imaging unit 20.

  The visible image incident on the imaging unit 20 is imaged on the imaging surface of the imaging element 22 by the imaging optical system 21 and is imaged by the imaging element 22.

  The R, G, and B image signals respectively output from the image sensor 22 are subjected to CDS / AGC (correlated double sampling / automatic gain control) processing and A / D conversion processing in the imaging control unit 23. , And output to the processor 3 via the cable 5.

  On the other hand, a visible image reflected from the peripheral area by irradiation of illumination light emitted from the side surface of the insertion member 30b is picked up by the small CCD camera 60 and subjected to A / D conversion processing or the like. An image signal is output from the small CCD camera 60 to the processor 3. The output of the image signal from the small CCD camera 60 to the processor 3 may be performed by wireless communication or via a cable.

  The image signal output from the imaging unit 20 and input to the processor 3 is temporarily stored in the image input controller 41 and then stored in the memory 43. The image signal for each frame read from the memory 43 is subjected to gradation correction processing and sharpness correction processing in the image processing unit 42 and then sequentially output to the video output unit 44.

  Then, the video output unit 44 performs a predetermined process on the input image signal to generate a display control signal, and sequentially outputs the display control signal for each frame to the monitor 4. And the monitor 4 displays the visible image of the to-be-observed part near the front-end | tip of the insertion member 30b based on the input display control signal.

  On the other hand, the image signal output from the small CCD camera 60 and input to the processor 3 is also subjected to predetermined image processing in the processor 3 and then sequentially output to the video output unit 44. The image signal is subjected to predetermined processing to generate a display control signal, and the display control signal for each frame is sequentially output to the monitor 4. And the monitor 4 displays the visible image of the peripheral region of the insertion member 30b based on the input display control signal.

  The visible image near the tip of the insertion member 30b imaged by the imaging unit 20 and the visible image of the peripheral area of the insertion member 30b imaged by the small CCD camera 60 are different window screens on one monitor 4. Or may be displayed on the screens of two monitors, respectively.

  According to the rigid endoscope system of the above-described embodiment, the phosphor-containing optical fiber 31 in which the phosphor 31c emitting fluorescence having the wavelength included in the illumination light is contained in the clad 31b extends into the insertion member 30b, and the insertion member A transmission portion 30g that transmits fluorescence emitted from the clad 31b of the phosphor-containing optical fiber 31 is provided on the side surface of the fluorescent material-containing optical fiber 31, and further, the amount of fluorescence that is transmitted toward the side of the insertion member 30b through the transmission portion 30g. Since the light shielding member 35 for adjusting the light intensity is provided, it is possible to irradiate both the distal direction and the lateral direction of the insertion member 30b with the illumination light, and the amount of illumination light irradiated in these directions. The light shielding member 35 can be arbitrarily adjusted.

  Moreover, you may make it form the reflective coat which consists of a reflective material which reflects the illumination light which permeate | transmitted the transmission part 30g of the insertion member 30b in the internal peripheral surface at the side of the insertion member 30b of the oversheath 35 in the said embodiment. Alternatively, the oversheath 35 itself may be formed of a reflective material. By configuring the oversheath 35 in this way, the illumination light applied to the inner peripheral surface of the oversheath 35 can be guided toward the distal end of the insertion member 30b, and the amount of illumination light directed toward the distal end is increased. Can do. That is, by moving the oversheath 35, the ratio of the amount of illumination light irradiated in the distal direction (forward) of the insertion member 30b and the amount of illumination light irradiated laterally is adjusted to a desired ratio. Can do.

  Furthermore, as shown in FIG. 11, a plurality of inclined surfaces are formed on the inner peripheral surface of the oversheath 36 on the insertion member 30b side so as to reflect the illumination light transmitted through the transmission portion 30g toward the distal end of the insertion member 30b. You may make it do. Thereby, illumination light can be more efficiently guided to the front end direction.

  In the above embodiment, the amount of illumination light that is transmitted through the transmission part 30g and irradiated toward the side of the insertion member 30b is adjusted by providing the oversheath 35 outside the insertion member 30b. However, not limited to this, as shown in FIG. 12, illumination light emitted from the side surface of the phosphor-containing optical fiber 31 between the side surface of the phosphor-containing optical fiber 31 in the insertion member 30b and the transmission part 30g. A shutter 37 that shields the light may be provided, and the shutter 37 may be configured to be movable in the longitudinal direction of the insertion member 30b.

  Further, the shutter 37 is not limited to the configuration in which the shutter 37 can be moved in the longitudinal direction of the insertion member 30b. For example, as shown in FIG. 13, the illumination light emitted from the side surface of the phosphor-containing optical fiber 31 is transmitted. The shutter 38 is formed by alternately arranging the portions 38a to be shielded and the portions 38b to be shielded in the circumferential direction, and the shutter 38 is configured to be rotatable in the circumferential direction (arrow C direction in FIG. 13). Also good.

  Similarly, the oversheath 35 described in the above embodiment may be configured such that portions that transmit illumination light and portions that shield light are alternately arranged in the circumferential direction so as to be rotatable in the circumferential direction. Good.

  Moreover, in the said embodiment, although the image pick-up element 22 which image | photographs the visible image of a to-be-observed part was installed in the image pick-up unit 20, not only this but arrange | positioning at the front-end | tip part 30Y of the insertion member 30b. It may be. Specifically, as shown in FIG. 14, the imaging element 22 is provided inside the distal end portion 30Y of the insertion member 30b, an objective optical system 34 that forms a visible image received by the imaging lens 30d, and an objective A prism 39 that reflects the visible image formed by the optical system 34 at a right angle and forms an image on the imaging surface of the imaging device 22 may be provided. At this time, the illumination light emitted from the side surface of the phosphor-containing optical fiber 31 is extended in the vicinity of the camera unit including the objective optical system 34, the prism 39, and the image sensor 22 so that the illumination light does not enter the image sensor 22. It is desirable to provide a coating 33 made of a material that blocks illumination light on the surface of the phosphor-containing optical fiber 31.

  Furthermore, in the above-described embodiment, the visible image on the side of the insertion member 30b is picked up by the small CCD camera 60 provided on the body surface. However, the present invention is not limited to this. For example, as shown in FIG. A wide-angle lens 70 is provided in the vicinity of the transmission part 30g of the insertion member 30b, and a side visible image received by the wide-angle lens 70 is imaged by a camera unit 71 including an imaging element provided in the insertion member 30b. You may do it.

  As described above, by providing the imaging element in the insertion member 30b, only the rigid endoscope imaging device 10 can display visible images in the distal direction and the side of the insertion member 30b without providing the imaging unit 20 as in the above embodiment. You can take an image.

  Moreover, in the said embodiment, it was set as the structure which images the visible image of a to-be-observed part by irradiating a to-be-observed part with white light, Furthermore, near-infrared light LD which emits a near-infrared light to a light source device. In addition to providing a light source, an optical fiber that guides near-infrared light emitted from a near-infrared light LD light source is provided in the insertion member 30b, and near-infrared light is applied to a portion to be observed in which ICG (Indocyanine Green) is previously introduced You may make it image | photograph the fluorescence image of ICG by irradiating the excitation light of light.

  Moreover, although the said embodiment applies the endoscope apparatus of this invention to a rigid endoscope system, you may apply to an endoscope system which has not only this but a flexible endoscope, for example.

DESCRIPTION OF SYMBOLS 1 Rigid endoscope system 2 Light source device 3 Processor 4 Monitor 5 Cable 10 Rigid endoscope imaging device 20 Imaging unit 22 Imaging element 30 Body cavity insertion part 30b Inserting member 30d Imaging lens 30g Transmission part 31 Phosphor-containing optical fiber 31a Core 31b Clad 31c 32 Relay lens 34 Objective optical system 35 Oversheath 50 Blue LD light source 60 Small CCD camera 61, 62 Treatment tool 70 Wide angle lens 71 Camera unit

Claims (11)

Inserted into the body, irradiates the observation part in the body with illumination light, receives the light emitted from the observation part by irradiation of the illumination light, and extends into the insertion part to be excited An endoscope apparatus comprising: an optical fiber in which a phosphor that emits fluorescence having a wavelength included in the illumination light by light irradiation is contained in a cladding;
A transmission part that transmits fluorescence emitted from the clad of the optical fiber is provided on a side surface of the insertion part,
An endoscope apparatus comprising: a light shielding member for adjusting a light amount of the fluorescence that is transmitted through the transmission portion and irradiated toward a side of the insertion portion. The light shielding member is an oversheath formed in a cylindrical shape so as to cover the transmission part of the insertion part,
The endoscope apparatus according to claim 1, wherein the oversheath is configured to be movable in a longitudinal direction of the insertion portion.   The oversheath is configured such that a portion that transmits fluorescence emitted from the clad of the optical fiber and a portion that blocks light are arranged side by side in the circumferential direction, and is configured to be rotatable in the circumferential direction. The endoscope apparatus according to claim 2, wherein:   The surface on the transmission part side of the oversheath is formed so as to reflect the fluorescence transmitted through the transmission part in the distal direction of the insertion part. Endoscope device.   The endoscope apparatus according to claim 4, wherein a plurality of reflection surfaces that reflect the fluorescence toward the distal end of the insertion portion are formed on a surface of the oversheath on the transmission portion side. The light shielding member is a shutter provided between a side surface of the optical fiber in the insertion portion and the transmission portion;
The endoscope apparatus according to claim 1, wherein the shutter is configured to be movable in a longitudinal direction of the insertion portion. The shutter is formed in a cylindrical shape, and a part that transmits fluorescence emitted from the clad of the optical fiber and a part that shields light are arranged in a circumferential direction, and
The endoscope apparatus according to claim 6, wherein the endoscope apparatus is configured to be rotatable in the circumferential direction. An imaging element that receives and images light emitted from the observed portion is provided in the distal end portion of the insertion portion,
The endoscope apparatus according to any one of claims 1 to 7, wherein a side surface of the optical fiber extending in the vicinity of the imaging element is covered with a light shielding cover that shields the fluorescence.   9. The image sensor according to claim 1, further comprising: a side image sensor that receives and captures light reflected from a peripheral region of the side by irradiation of the fluorescence to a side of the insertion portion. The endoscope apparatus according to claim 1.   The endoscope apparatus according to claim 9, wherein a wide-angle lens that receives light from the lateral peripheral region and forms an image on the lateral imaging element is provided on a side surface of the insertion portion. .   The endoscope apparatus according to claim 9 or 10, wherein the lateral imaging element is provided in the vicinity of the transmission portion.

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