JP2006181061A - Endoscope system - Google Patents

Abstract

【Task】
Even if the same light source device is used by replacing an endoscope with a different diameter of the light guide passed through the endoscope, there is no loss of the amount of light emitted from the tip of the light guide. An endoscope system in which the light emitted from the tip is not uneven is provided.
[Solution]
The fluorescence observation endoscope 10 stores the diameter of the fiber bundle 102 of the light guide 101 a in the memory 116. The system control circuit 215 reads the diameter of the fiber bundle 102 stored in the memory 116, and matches the diameter of the light collected by the condenser lens 209 with the diameter of the fiber bundle 102 on the base end surface of the light guide 101a. The position of the condenser lens 209 is moved so that
[Selection] Figure 2

Description

  The present invention relates to an endoscope system that observes the inside of a body cavity by irradiating illumination light into the body cavity through a light guide provided in the endoscope.

  As is well known, when a biological tissue is irradiated with light of a specific wavelength, it is excited and emits fluorescence. In addition, an abnormal living tissue in which a lesion such as a tumor or cancer has occurred emits weaker fluorescence than a normal living tissue. In recent years, endoscope systems have been developed that detect abnormalities occurring in living tissue in a body cavity by utilizing this phenomenon. Patent Document 1 discloses an endoscope system of this type.

  In such an endoscope system, the light source device and the endoscope are made as separate parts, and light emitted from the light source device by connecting the light source device and the endoscope is transmitted to the distal end of the endoscope. In some cases, a configuration that enables irradiation from the outside is employed. Hereinafter, such an endoscope system will be described.

  This conventional endoscope system includes a light source device that emits illumination light (white light) and excitation light, and an endoscope that is inserted into a body cavity of a subject.

  FIG. 4 is a schematic diagram showing an internal configuration of a light source device in a conventional endoscope system. As shown in FIG. 4, the light source device includes a white light source 301 that emits white light as parallel light, and an excitation light source 306 that emits excitation light. The optical path of the white light and the optical path of the excitation light intersect within the light source device, and a dichroic mirror 308 that transmits the white light and reflects the excitation light is disposed at a position where these optical paths intersect each other. Yes. In addition, a condensing lens 309 for converging these lights is disposed on the optical path of white light transmitted through the dichroic mirror 308 and excitation light reflected by the dichroic mirror 308 inside the light source device.

  Between the white light source 301 and the dichroic mirror 308, an infrared cut filter 302 and a light beam diameter reducing optical system 303 including a pair of convex lenses 303a and 303b are disposed. The convex lens 303a. Between the convex lens 303b and the convex lens 303b, a rotation shielding plate 304 and a light quantity stop 305 for blocking or passing the light beam are arranged. In addition, a collimating lens 307 that converts the excitation light emitted from the excitation light source 306 into parallel light is disposed between the excitation light source 306 and the dichroic mirror 308.

  The endoscope is provided with a light guide 401a in order to irradiate light emitted from the light source device from the distal end of the endoscope. The light guide 401a includes a fiber bundle 411a in which a plurality of optical fibers are bundled and a protective tube 412 (see FIG. 5A) that covers the side surface of the fiber bundle 411a. When the endoscope is connected to the light source device, the base end surface of the light guide 401a and the condensing lens 309 are configured to face each other.

  Therefore, if the light beam can pass through the rotation shielding plate 304 after connecting the endoscope to the light source device, white light from which components in the infrared region have been removed is applied to the proximal end surface of the light guide 401a of the endoscope. It can be converged. Further, when the rotation shielding plate 304 is in a state where the light beam is shielded and the excitation light is emitted from the excitation light source 306, only the excitation light can be converged on the proximal end surface of the light guide 401a of the endoscope. .

  Next, the manner in which light is incident on the light guide 401a will be specifically described with reference to FIG. FIG. 5A is an explanatory diagram showing a state in which the light collected by the condenser lens 309 is converged on the base end face of the light guide 401a.

  As shown in FIG. 5A, the condensing lens 309 is configured such that the light incident when the light source device and the endoscope are connected to the diameter of the fiber bundle 411a of the light guide 401a. It arrange | positions in the position converged to the diameter which corresponds.

Therefore, when the light source device and the endoscope are connected, light enters all the optical fibers constituting the fiber bundle 411a.
JP 2000-23903 A

  By the way, when performing a diagnosis using such an endoscope system, an endoscope having a different light guide diameter may be replaced depending on the contents of the diagnosis. The case where the endoscopes having different light guide diameters are used in this manner will be described with reference to FIGS. 5B and 5C.

  FIG. 5B shows a case where an endoscope that employs a light guide 401b having a diameter smaller than that of the light guide 401a instead of the endoscope having the light guide 401a in FIG. 5A is connected to the light source device. FIG. 5C illustrates an endoscope that employs a light guide 401c having a diameter larger than that of the light guide 401a instead of the endoscope having the light guide 401a in FIG. 5A. It is explanatory drawing at the time of connecting to an apparatus. In addition, the same number is used about the structure which is common in FIG. 5A, The description is abbreviate | omitted.

  As shown in FIG. 5B, when an endoscope using the light guide 401b is connected to the light source device, the light converged by the condenser lens 309 on the base end surface of the light guide 401b is This is larger than the diameter of the fiber bundle 411b. Therefore, a part of the light transmitted through the condenser lens 309 cannot enter the fiber bundle 411b on the base end surface of the light guide 401b, so that the amount of light emitted from the distal end of the endoscope is reduced. It will end up (there is a loss). In this way, if the light incident on the light guide 401b is in a loss state, even if excitation light is incident on the light guide 401b, sufficient energy is required to excite the living tissue. Since it cannot be obtained, there is a possibility that observation by fluorescence cannot be performed.

  Further, as shown in FIG. 5C, when an endoscope employing the ride guide 401c is attached to the light source device, the light converged by the condensing lens 309 on the base end surface of the light guide 401c. Is smaller than the diameter of the fiber bundle 411c. Therefore, light does not enter the optical fiber on the outer peripheral side among the optical fibers constituting the fiber bundle 411c.

  Here, a general light guide will be described. In a general light guide, in order to transmit light energy instead of an image, the positional relationship between optical fibers at the distal end side of the light guide is random relative to the positional relationship between optical fibers at the proximal end side of the light guide. It is designed to be.

  Therefore, even if light is converged in a circular shape on a part of the fiber bundle 411c on the base end surface of the light guide 401c, the light emitted from the tip of the light guide 401c may not be circular. For example, unevenness occurs in the light emitted from the tip of the light guide 401c, and mottled light and darkness may occur on the living tissue irradiated with this light. If there is unevenness in the light emitted from the light guide 401c in this way, when the excitation light is incident on the light guide 401c, even if the living tissue is a normal part, the fluorescence emitted from the living tissue is also reduced. It becomes mottled (partly dark). Therefore, in this case, even if the part to be observed is a normal part, there is a possibility that the part is diagnosed as a lesion part.

  Therefore, the problem of the present invention is that the same light source device is incident on the proximal end of the light guide even when an endoscope having a different diameter of the light guide drawn through the endoscope is used. It is an object of the present invention to provide an endoscope system in which there is no loss of light and no unevenness occurs in the light emitted from the tip of the light guide.

  An endoscope system according to the present invention devised to solve the above-described problem is a light source that makes an endoscope provided with a light guide for guiding illumination light into a body cavity and makes the illumination light incident on the light guide. An endoscope system that is replaceably attached to an apparatus, and includes an optical guide having a fiber bundle in which a plurality of optical fibers are bundled, and a storage device that stores the diameter of the fiber bundle A light source unit that emits illumination light as parallel light, a condensing lens that converges the illumination light emitted from the light source unit on the proximal end surface of the light guide of the endoscope, and the condensing lens of the endoscope Read the diameter of the fiber bundle from the lens moving means that moves to and away from the base end face of the light guide and the storage device of the endoscope, and at the base end face of the light guide And a light source device having a control unit for controlling the lens moving means to move the condenser lens to a position where the illumination light is converged to a size that matches the diameter of the fiber bundle. .

  When configured in this manner, when the endoscope is connected to the light source device, based on the diameter of the fiber bundle of the light guide in the endoscope stored in the storage device provided in the endoscope. The position of the condenser lens is adjusted. Therefore, according to the present invention, even if an endoscope having a different light guide diameter is replaced and connected to the same light source device, the light bundle of the endoscope is converged by the condenser lens. Since all the illumination light is incident and the illumination light is incident on all the optical fibers constituting the fiber bundle, there is no loss of light incident on the proximal end of the light guide, and the light is emitted from the distal end of the light guide. An endoscope system in which there is no unevenness in light can be provided.

  The light source device includes a white light source unit that emits white light as parallel light, an excitation light source unit that emits excitation light for exciting biological tissue as parallel light, and parallel light from the white light source unit. And an optical path combining element that combines the optical path of the white light emitted as and the optical path of the excitation light emitted as parallel light from the excitation light source unit so as to be the same optical path.

  Further, the control unit is configured to determine a base end surface of the light guide based on a focal length of the condensing lens, a diameter of excitation light incident on the condensing lens, and a diameter of the fiber bundle read from the storage unit. The lens moving means may be controlled after calculating the position of the lens for converging the illumination light to a size that matches the diameter of the fiber bundle.

  According to the present invention, even if an endoscope having a different light guide diameter drawn through the endoscope is used for the same light source device, the light incident on the proximal end of the light guide is replaced. It is possible to provide an endoscope system that has no loss and does not cause unevenness in light emitted from the tip of the light guide.

  Next, modes for carrying out the present invention will be described based on the attached drawings.

  FIG. 1 is an external view of an endoscope system according to an embodiment of the present invention. As shown in FIG. 1, the endoscope system includes a fluorescence observation endoscope 10, a light source processor device 20, and a monitor 30.

  The fluorescence observation endoscope 10 is obtained by adding a modification for fluorescence observation to a normal electronic endoscope, and is inserted into a body cavity. An operation unit 10b having an angle knob for bending the tip of the unit 10a, a light guide flexible tube 10c for connecting the operation unit 10b and the light source processor device 20, and the light guide flexible tube 10c. The connector 10d provided at the base end of is provided.

  The body cavity insertion portion 10a is a portion that is inserted into the body cavity, and includes a resin-made cladding tube and a tubular skeleton structure covered with the cladding tube. The skeletal structure flexes flexibly in response to an applied external force and possesses rigidity capable of maintaining the flexed state to such an extent that the body cavity wall is not damaged. Although not shown, the body cavity insertion portion 10a includes an objective optical system and an image sensor in the distal end portion. The objective optical system forms an image of a subject facing the distal end of the body cavity insertion portion 10a, and the imaging element captures the image formed by the objective optical system and converts it into an image signal.

  The operation part 10b is a part provided with an angle knob 112, a forceps port 113, and the like, and is connected to the proximal end of the body cavity insertion part 10a. The angle knob 112 changes the bending state of the distal end portion of the body cavity insertion portion 10a through a bending mechanism incorporated in a portion of a predetermined length from the distal end to the proximal end of the body cavity insertion portion 10a. It is a handle. The forceps port 113 is an opening for inserting a treatment tool such as forceps into a narrow tube (forceps channel) drawn through the body cavity insertion portion 10a.

  The light guide flexible tube 10c is a resin cable through which the light guide 101a and various signal lines are passed, and the tip thereof is connected to the side surface of the operation unit 10b. As shown in the enlarged view of FIG. 3A, the light guide 101a includes a fiber bundle 102 composed of a plurality of bundled optical fibers and a protective tube 103 covering the outer periphery of the fiber bundle 102. The insertion portion 10a, the operation portion 10b, and the cable portion 10c are sequentially passed through. The tip of the light guide 101a is fixed to the tip of the insertion portion 10a. The signal lines in the light guide flexible tube 10c include signal lines that are led through the operation unit 10b and the body cavity insertion unit 10a and connected to the image sensor of the body cavity insertion unit 10a.

  The connector 10d is connected to the proximal end of the light guide flexible tube 10c, and is a connecting portion for detachably mounting on the light source processor device 20. On the end face of the connector 10d, as shown in the schematic view of FIG. 2, there are a terminal 114 to which an end of a signal line led through the light guide flexible tube 10c is connected and a metal tube 115 protruding vertically. , Provided. Further, the connector 10d includes a memory 116 (corresponding to a storage device) connected to the terminal 114 with a signal line. The memory 116 stores the diameter of the fiber bundle 102 of the light guide 101a. Note that the base end of the light guide 101a is inserted and fixed in the metal tube 115 in the connector 10d.

  The light source processor device 20 selectively introduces illumination light (white light) and excitation light into the proximal end surface of the light guide 101a of the fluorescence observation endoscope 10 and through the terminal 114 of the connector 10d of the fluorescence observation endoscope 10. This is a device that generates a video signal by performing image processing on the image signal received from the image sensor and outputs it to the monitor 30.

  On the front panel of the housing of the light source processor device 20, various switches 21 including a switch for designating the normal observation mode and a switch for designating the fluorescence observation mode, and a metal tube 115 in the connector 10d of the fluorescence observation endoscope 10 are provided. A socket 22 which is a cylinder inserted from the outer surface is provided. The through hole formed in the socket 22 communicates with the internal space of the light source processor device 20.

  FIG. 2 is a schematic diagram showing the internal configuration of the light source processor device 20. In the light source processor device 20, white light is sequentially emitted toward the socket 22 on the extension line of the central axis of the socket 22 (that is, the central axis of the light guide 101 a in the metal tube 115 inserted into the socket 22). A light source 201, an infrared ray removal filter 202, a light beam diameter reducing optical system 203, a rotation shielding plate 204, a light amount stop 205, a dichroic mirror 208, and a condenser lens 209 are arranged. Further, in the light source processor device 20, the excitation light source 206 and the excitation light source 206 are arranged in order toward the dichroic mirror 208 on a line perpendicular to the extended line of the central axis of the socket 22 on the surface of the dichroic mirror 208. A collimating lens 207 is arranged.

  The white light source 201 (corresponding to a white light source unit) is an apparatus that emits white light as parallel light, and reflects a light emitted from a focal point as parallel light, and a parabolic mirror. A xenon lamp having a light emitting point arranged at the focal point. The infrared filter 202 is a filter for removing infrared light from incident light and transmitting the remaining light, and is disposed on the optical path of white light emitted from the white light source 201. . The light beam diameter reducing optical system 203 is a Kepler type afocal optical system including a pair of convex lenses 203 a and 203 b, and reduces the light beam diameter of white light transmitted through the infrared removing filter 202.

  The rotation shielding plate 204 is a disc in which only one substantially semicircular opening is formed, and the center of the arc of the through hole coincides with the center of the outer circumferential circle of the rotation shielding plate 204. The center of the rotation shielding plate 204 is fixed to the tip of a drive shaft of a motor (not shown). When driven by a motor (not shown), the rotation shielding plate 204 rotates around the drive shaft. The rotation shielding plate 204 is orthogonal to the optical axis of the light beam diameter reducing optical system 203, and the white light is incident on the eccentric position of the rotation shielding plate 204. For this reason, when the opening of the rotation shielding plate 204 is disposed on the optical axis of the light beam reduction optical system 203, white light passes from the light beam reduction optical system 203, and portions other than the opening of the rotation shielding plate 204 When arranged on the optical axis of the light beam reduction optical system 203, white light is blocked from the light beam reduction optical system 203.

  The light quantity stop 205 is an instrument for reducing the light quantity by a known structure in which a part of light is shielded by a plurality of diaphragm blades that form a substantially circular opening. Between the rotary shielding plate 204 and the convex lens 203b, a white light quantity stop 205 is provided. It is arranged on the optical path of light. The light quantity diaphragm 205 includes a mechanism for displacing each diaphragm blade. When each diaphragm blade is displaced and the diameter of the opening changes, the amount of light beam passing through the opening increases or decreases.

  The excitation light source 206 is a laser diode that emits excitation light for exciting a living tissue to generate fluorescence. The excitation light source 206 emits light having a wavelength shorter than the wavelength band of white light emitted from the white light source 301 (for example, ultraviolet light). The collimating lens 207 is a collimating lens that converts excitation light emitted as diverging light from the excitation light source 206 into parallel light (the excitation light source 206 and the paralleling lens 207 correspond to the excitation light source unit).

  The dichroic mirror 208 is an optical element that transmits white light and reflects excitation light. The dichroic mirror 208 is disposed at a position where the optical path of the white light and the optical path of the excitation light intersect. The dichroic mirror 208 is inclined by 45 ° with respect to the optical axis direction of the light beam diameter reducing optical system 203 and It is also inclined 45 ° with respect to the optical axis direction. White light emitted as parallel light from the beam diameter reducing optical system 203 is transmitted through the dichroic mirror 208, and excitation light emitted from the collimating lens 207 is reflected at right angles by the dichroic mirror 208, thereby producing white light. On the same optical path in the same direction as the traveling direction of the white light. Therefore, the dichroic mirror 208 functions as an optical path synthesis element. In the present embodiment, the diameter of the white light is adjusted by the light amount diaphragm 205 so that the diameters of the excitation light path and the white light path are substantially the same when they are combined.

  The condenser lens 209 is a lens having a positive power for converging parallel light. The condensing lens 209 is disposed on the optical path of the white light transmitted through the dichroic mirror 208 and the excitation light reflected by the dichroic mirror 208.

  In order to operate the configuration described above, the light source processor device 20 further includes a first power supply circuit 211, a second power supply circuit 212, a driver circuit 213, a condenser lens drive mechanism 214, and a system control circuit 215. I have.

  The first power supply circuit 211 is a circuit for supplying power to the white light source 201, and the second power supply circuit 212 is a circuit for supplying power to the excitation light source 206.

  The condensing lens drive mechanism 214 (corresponding to the lens moving means) is a mechanism for moving the condensing lens 209 in the optical axis direction. That is, the condensing lens drive mechanism 214 moves a lens frame (not shown) that holds the condensing lens 209 via a rack and pinion type gear train driven by a motor, for example, in the optical axis direction of the condensing lens 209. Is configured to move. Therefore, the condensing lens 209 contacts and separates from the base end surface while maintaining a coaxial state with the base end surface of the light guide 101a by the condensing lens drive mechanism 214.

  The driver circuit 213 is a circuit for controlling the motor of the condenser lens drive mechanism 214. When the driver circuit 213 receives the movement direction and movement amount of the condenser lens 209 from the system control circuit 215, the driver circuit 213 collects the movement amount in the movement direction. The motor of the condensing lens drive mechanism 214 is controlled so that the optical lens 209 moves.

  The system control circuit 215 (corresponding to the control unit) is a controller for controlling the entire light source processor device 20, and various switches 21 (shown in FIG. 2) provided on the front panel of the housing of the light source processor device 20. (Not shown), the first power supply circuit 211, the second power supply circuit 212, the driver circuit 213, and the image processing unit (not shown in FIG. 2). When the connector 10d of the fluorescence observation endoscope 10 is attached to the light source processor device 20, the system control circuit 215 receives an image sensor (not shown) in the body cavity insertion portion 10a via the terminal 114 of the connector 10d. And connected to the memory 116. Therefore, an operation signal generated by an operation on the switch 21 is input to the system control circuit 215, and an image signal output when the image sensor performs imaging is also input to the system controller circuit 215.

  The system control circuit 215 reads the diameter of the fiber bundle 102 of the fluorescence observation endoscope 10 stored in the memory 116 when the fluorescence observation endoscope 10 is connected to the light source processor device 20. Then, the system control circuit 215 determines the light guide 101a based on the read diameter of the fiber bundle 102, the diameter of the excitation light incident on the condenser lens 209 stored as a constant, and the focal length of the condenser lens 209. The position of the condenser lens 209 where the diameter of the excitation light converged by the condenser lens 209 is equal to the diameter of the fiber bundle 102 is calculated. Based on this calculation result, the system control circuit 215 controls the driver circuit 213 and moves the condenser lens 209 to the calculated position by the condenser lens drive mechanism 214. FIG. 3A shows the positional relationship between the condenser lens 209 thus moved and the base end face of the light guide 101a.

  The system control circuit 215 controls each component of the light source processor device 20 based on operation signals generated by operating the various switches 21 after the condenser lens 209 is moved as described above. . Hereinafter, the operation inside the optical processor device 20 will be described for the case where the switch for designating the normal observation mode and the switch for designating the fluorescence observation mode in the switch 21 are operated.

  When the system control circuit 215 receives an operation signal generated by operating a switch that designates the normal observation mode, the system control circuit 215 starts emitting white light to the white light source 201 by controlling the first power supply circuit 211. The rotation shielding plate 204 is rotated to the rotation position where the white light passes through the opening of the rotation shielding plate 204, and the second power supply circuit 212 is controlled to stop the excitation light source 206 from emitting the excitation light. . As a result, only white light enters the condenser lens 209, so only white light enters the light guide 101 a of the fluorescence observation endoscope 10, and the body cavity insertion portion 10 a of the fluorescence observation endoscope 10. Only white light is emitted from the tip of the.

  On the other hand, when the system control circuit 215 receives an operation signal generated by operating a switch for designating the fluorescence observation mode, the system control circuit 215 continuously rotates the rotation shielding plate 204. At the same time, the second power supply circuit 212 is controlled in synchronization with the rotation of the rotation shielding plate 204, and the excitation light is emitted to the excitation light source 206 only when the rotation shielding plate 204 is in a position to shield white light. Let As a result, the excitation light and the white light are alternately incident on the condenser lens 209. Therefore, the excitation light and the white light are alternately incident on the light guide 101a of the fluorescence observation endoscope 10, and the fluorescence observation is performed. Excitation light and white light are alternately emitted from the distal end of the insertion portion 10a of the endoscope 10.

  The image processing unit converts an image signal sent from the imaging element of the fluorescence observation endoscope 10 via the system control circuit 215 into a video signal, and displays an image based on the video signal on the monitor 30.

  That is, when the switch for designating the normal observation mode is operated, the image processing unit images the subject (that is, the subject illuminated with white light) formed by white light reflected on the surface of the subject. A normal observation image is displayed on the monitor 30.

  The image processing unit displays a fluorescence observation image, which is an image of the subject formed by the fluorescence emitted from the surface of the subject, on the monitor 30 when a switch for designating the fluorescence observation mode is operated. Let Note that the image processing unit captures an image signal (image signal of a normal image) obtained by imaging white light reflected from the surface of the subject and an image signal (fluorescence observation image) obtained by imaging fluorescence emitted from the subject. A portion that is displayed brightly in the normal image but darkly displayed in the fluorescent image is extracted as a lesioned portion and displayed on the monitor 30.

  Since it is configured as described above, the endoscope system according to the present invention operates as described below.

  The surgeon performing the operation on the subject using the endoscope system according to the present invention turns on the main power supplies of the display device 30 and the light source processor device 20, and connects the connector 10d of the fluorescence observation endoscope 10 to the light source processor. Connect to device 20. Then, in the light source processor device 20, the movement process of the condenser lens 209 described above is executed, and the diameter of the excitation light converged by the condenser lens 209 and the diameter of the fiber bundle 102 on the proximal end surface of the light guide 101a. Are disposed at the same diameter. As described above, since the diameter of the white light incident on the condenser lens 209 substantially matches the diameter of the excitation light, the white light converged by the condenser lens 209 on the base end surface of the light guide 101a. The diameter also substantially coincides with the diameter of the fiber bundle 102.

  Therefore, according to the present embodiment, since all the light transmitted through the condensing lens 209 is incident on the fiber bundle 102 and light is incident on all the optical fibers constituting the fiber bundle 102, the light is transmitted through the condensing lens 209. The incident light can be incident on the proximal end of the light guide 101a without loss, and unevenness occurs in the light emitted from the distal end of the light guide 101a (the light irradiated on the body cavity wall becomes mottled) Will be able to prevent.

  Next, the operator selects the normal observation mode by operating the switch 21 provided in the housing of the light source processor device 20, and the distal end of the insertion portion 10a of the fluorescence observation endoscope 10 is placed in the body cavity of the subject. insert. Then, white light is emitted from the distal end of the insertion portion 10a of the fluorescence observation endoscope 10, and an image of the body cavity wall formed by the white light reflected by the surface of the body cavity wall is displayed as a normal observation image on the monitor 30. It is projected on. The surgeon can observe the state of the body cavity wall by viewing the normal observation image.

  When a portion suspected of having a lesion is found by looking at the normal observation image, the operator operates the switch 21 provided on the housing of the light source processor device 20 to enter the fluorescence observation mode. Switch. Then, excitation light and white light are alternately emitted from the distal end of the insertion portion 10 a of the fluorescence observation endoscope 10, and a fluorescence observation image is displayed on the monitor 30. As described above, since the excitation light emitted from the tip of the light guide 101a is not uneven, the state of the living tissue on the body cavity wall in the range irradiated with the excitation light is all the same (for example, all normal parts). If so, the intensity of the fluorescence emitted from the range irradiated with the excitation light is constant regardless of the location. Therefore, the surgeon can accurately diagnose the presence or absence of a lesion based on the image displayed on the monitor 30.

  By the way, the surgeon may use an electronic endoscope in which the diameter of the light guide drawn through the inside differs depending on the examination contents for the subject. Such a case will be described below with reference to FIGS.

  FIG. 3B is an explanatory diagram showing a case where the fluorescence observation endoscope 10 into which the light guide 101b having a smaller diameter than the light guide 101a is drawn is connected to the light source processor device 20. 3 (c) is an explanatory view showing a case where the fluorescence observation endoscope 10 into which the light guide 101c having a diameter larger than that of the light guide 101a is passed is connected to the light source processor device 20. FIG.

  After a diagnosis is performed in a state where the fluorescence observation endoscope 10 through which the light guide 101a is passed is connected to the light source processor device 20, the fluorescence observation endoscope 10 is removed from the light source processor device 20, and the light source processor When another fluorescence observation endoscope 10 through which the light guide 101b (or the light guide 101c) is passed is attached to the apparatus 20, it is stored in the memory 116 of the fluorescence observation endoscope 10. The condensing lens 209 is moved based on the diameter of the fiber bundle 102 of the light guide 101b (or the light guide 101c). Therefore, as shown in FIGS. 3B and 3C, the diameter of the light converged by the condenser lens 209 and the diameter of the fiber bundle 102 on the base end face of the light guide 101b (or the light guide 101c) It becomes the same diameter.

  As described above, according to the light source device according to the present embodiment, even if a fluorescence observation endoscope having a different light guide diameter is used for the same light source processor device, the fluorescence observation endoscope 10 can be used. Since the position of the condensing lens 209 is automatically adjusted based on the information regarding the diameter of the fiber bundle 102 stored in the memory 116, there is no loss of light incident on the tip of the light guide, and from the tip of the light guide. An endoscope system in which the emitted light is not uneven can be provided.

  In the above-described embodiment, the position of the condenser lens 209 is calculated based on the diameter of the excitation light incident on the condenser lens 209. However, the light source processor device 20 is configured to emit only white light. In this case (in the case of an endoscope system that performs only normal observation, not a fluorescence observation endoscope system), the position of the condenser lens 209 is calculated based on the diameter of the white light incident on the condenser lens 209. You may make it do.

  The system control circuit 215 includes a table that associates the diameter of the fiber bundle 102 with the position of the condenser lens 209 and reads the diameter of the fiber bundle 102 stored in the memory 116 of the fluorescence observation endoscope 10. Thereafter, based on this table, the condensing lens is positioned at a position corresponding to the diameter of the fiber bundle 102 (that is, the position where the diameter of the excitation light converged by the condensing lens 209 is equal to the diameter of the fiber bundle 102). It may be designed to move the position of 209.

  In the above-described embodiment, the configuration in which the diameter of the white light incident on the condenser lens 209 is matched with the diameter of the excitation light by the light amount diaphragm 205 is used. Alternatively, a configuration in which the diameter of the white light incident on the condenser lens 209 is made larger than the diameter of the excitation light may be adopted. In this case, the white light converged by the condensing lens 209 is larger than the diameter of the fiber bundle 102 on the base end face of the light guide 101a. Nevertheless, in general, since the output of white light emitted from the white light source is stronger than the output of excitation light output from the excitation light source, the white light incident on the fiber bundle 102 is somewhat lost. In addition, it is possible to obtain a normal observation image capable of observing the inside of the body cavity.

1 is an external view showing an external appearance of an endoscope system according to an embodiment of the present invention. Schematic which shows the internal structure of the light source processor apparatus in an endoscope system Explanatory drawing of the diameter of the light condensed on the base end face of the light guide by the condenser lens Schematic which shows the internal structure of the light source device in the conventional endoscope system Explanatory drawing of the diameter of the light condensed on the base end surface of a light guide by the condensing lens in the conventional endoscope system

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Fluorescence observation endoscope 20 Light source processor apparatus 30 Monitor 101 Light guide 102 Fiber bundle 116 Memory 201 White light source 206 Excitation light source 208 Dichroic mirror 209 Condensing lens 214 Condensing lens drive mechanism 215 System control circuit

Claims (3)

An endoscope system in which an endoscope having a light guide for guiding illumination light into a body cavity is replaceably attached to a light source device that makes the illumination light incident on the light guide,
A light guide having a fiber bundle in which a plurality of optical fibers are bundled, and an endoscope including a storage device storing the diameter of the fiber bundle;
A light source unit that emits illumination light as parallel light, a condensing lens that converges the illumination light emitted from the light source unit on the base end surface of the light guide of the endoscope, and the condensing lens as a light guide of the endoscope A lens moving unit that moves the base end surface of the light guide in a freely movable manner, and a diameter of the fiber bundle from the endoscope storage device, and a size that matches the diameter of the fiber bundle at the base end surface of the light guide And a light source device having a control unit for controlling the lens moving means to move the condenser lens to a position where the illumination light is converged. The light source device is
A white light source that emits white light as parallel light;
An excitation light source unit that emits excitation light for exciting biological tissue as parallel light;
An optical path combining element that combines the optical path of the white light emitted as parallel light from the white light source unit and the optical path of the excitation light emitted as parallel light from the excitation light source unit so as to be the same optical path; The endoscope system according to claim 1, further comprising: The control unit, based on the focal length of the condensing lens, the diameter of the excitation light incident on the condensing lens, and the diameter of the fiber bundle read from the storage unit, on the base end surface of the light guide The endoscope system according to claim 2, wherein the lens moving unit is controlled after calculating a position of the lens for converging the illumination light to a size that matches a diameter of a fiber bundle.