JP2012231834A - Light source device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a light source device for condensing diffused light and parallel light into a light incident end surface of a predetermined light guide member, the light source device having a reduced whole size without deteriorating transmission efficiency of special light.SOLUTION: The light source device includes: a diffused light source for emitting diffused light; a parallel light source portion for emitting parallel light; and a condensing lens for condensing the diffused light and the parallel light into the light incident end surface of the predetermined light guide member. The diffused light source and the parallel light source portion are disposed on an axis parallel to the optical axis of the condensing lens.

Description

  The present invention relates to a light source device that collects diffused light and parallel light and enters the light incident end face of a predetermined light guide member.

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

  And as one of such endoscope systems, for example, to observe blood vessels running under fat and blood flow, lymphatic vessels, lymph flow, bile duct running, bile flow, etc. that do not normally appear on the image, An endoscope system has been proposed in which ICG (Indocyanine Green) is previously introduced into an observation part and an ICG fluorescence image is acquired by irradiating the observation part with excitation light of near infrared light. In addition, an endoscope system has been proposed in which autofluorescence emitted from an observed portion is detected by irradiating the observed portion with excitation light to acquire a fluorescent image.

  For example, in Patent Document 1, as described above, an endoscope system that irradiates a portion to be observed with excitation light to capture a fluorescent image and irradiates white light to the portion to be observed to capture a normal image is proposed. Has been.

  Here, in the endoscope system of Patent Document 1, the light source device for irradiating excitation light and white light emits the reference light source 100 that emits white light 102 and the excitation light 103 as shown in FIG. The excitation light source 101 is provided. Further, the white light 102 emitted from the reference light source 100 is provided on the incident end face of the light guide 105 connected to the endoscope main body, and a condensing lens 104 is provided in the optical path of the white light 102 for excitation. And a mirror 106 that reflects the excitation light 103 emitted from the light source 101 toward the condenser lens 104.

JP 2009-72213 A

  However, in the case of the configuration like the light source device described in Patent Document 1, since the excitation light is reflected by the mirror 106 and is incident on the condenser lens 104, the excitation light source 101 is placed outside the optical path of the white light 102. In addition, it is necessary to arrange the excitation light source 101 at a position where the optical axis of the excitation light source 101 is perpendicular to the optical axis of the condenser lens 104.

  In such an arrangement relationship, it is necessary to arrange the reference light source 100 in the optical axis direction of the condensing lens 104 and the excitation light source 101 in a direction perpendicular to the optical axis of the condensing lens 104, that is, mutually Since it is necessary to arrange the reference light source 100 and the excitation light source 101 in the orthogonal direction, the entire light source device has a predetermined width in the orthogonal direction, and there is a problem that the size becomes large.

  Further, since the excitation light 101 is reflected by the mirror 106, there is a problem that the transmission efficiency of the excitation light 101 is lowered by the mirror 106.

  An object of this invention is to provide the light source device which can reduce the whole size, without reducing the transmission efficiency of excitation light in view of said problem.

  The light source device of the present invention includes a diffused light source that emits diffused light, a parallel light source unit that emits parallel light, and a light collecting device that collects the diffused light and the parallel light and makes them incident on a light incident end surface of a predetermined light guide member. The diffusing light source and the parallel light source unit are arranged on a straight line parallel to the optical axis of the condenser lens.

  Further, the parallel light source unit can be disposed on the optical path of the diffused light.

  In addition, the parallel light source unit can be disposed on the optical path of the diffused light and at a position other than the optical axis of the condenser lens.

  Further, the parallel light source unit can be disposed in the vicinity of the diffuse light source outside the optical path of the diffused light and at a position where the parallel light can enter the condenser lens.

  In addition, parallel light emitted from the parallel light source unit can be incident from a position other than the optical axis of the condenser lens.

  Moreover, the heat_generation | fever suppression member for suppressing the heat_generation | fever by irradiation of the diffused light to a parallel light source part can be provided.

  Further, a lens may be provided between the diffusion light source and the parallel light source unit, and the heat generation suppressing member may be a light shielding member that blocks the diffused light that passes through the lens and is irradiated on the parallel light source unit.

  A light shielding member can be provided on the lens.

  Moreover, a light shielding member can be provided in the parallel light source unit.

  In addition, a reflection member that reflects diffused light can be used as the light shielding member.

  Further, the reflecting member can reflect diffused light in a direction other than the direction in which the diffused light source is installed.

  An absorbing member that absorbs diffused light can be used as the light shielding member.

  Moreover, the heat insulation member provided with respect to the parallel light source part can be used as a heat_generation | fever suppression member.

  Further, the parallel light source unit may have a laser diode or a light emitting diode.

  The parallel light source unit can emit near infrared light as parallel light.

  Further, the diffused light source can emit white light as diffused light.

  According to the light source device of the present invention, the diffused light source that emits the diffused light, the parallel light source unit that emits the parallel light, and the diffused light and the parallel light are collected and incident on the light incident end face of the predetermined light guide member. Since the diffused light source and the parallel light source unit are arranged on a straight line parallel to the optical axis of the collective lens, they are orthogonal to each other as in the conventional light source device described above. Therefore, it is not necessary to secure a predetermined width in the direction to be performed, and the entire apparatus can be reduced in size. Further, since the mirror is not used unlike the conventional light source device described above, the transmission efficiency of special light can be improved.

  In addition, when the parallel light source unit is arranged on the optical path of the diffused light and at a position other than the optical axis of the condenser lens, the parallel light source unit is arranged to diffuse light due to the arrangement of the parallel light source unit on the optical path. Since the influence can be further reduced, it is possible to irradiate the observed portion with better quality diffused light.

  In addition, when the parallel light source unit is disposed in the vicinity of the diffuse light source outside the optical path of the diffused light and at a position where the parallel light can enter the condenser lens, Since there is no influence, it is possible to irradiate the observed portion with a better quality diffused light.

  Further, when the parallel light emitted from the parallel light source unit is incident from a position other than the optical axis of the condenser lens, the direction is inclined by a predetermined incident angle with respect to the light incident end surface of the light guide member. Special light can be made incident from. In this way, when the special light is incident on the light incident end surface of the light guide member, compared with the case where the special light is incident from the vertical direction on the light incident end surface of the light guide member, the observed portion It is possible to widen the irradiation range of the special light irradiated to. This action will be described in detail later.

  In addition, when a heat generation suppressing member for suppressing heat generation due to the diffusion light irradiation to the parallel light source unit is provided, the parallel light source unit is prevented from being heated and broken due to the diffusion light irradiation. be able to.

Schematic configuration diagram of a rigid endoscope system using an embodiment of a light source device of the present invention Schematic configuration diagram of body cavity insertion part Schematic configuration diagram of the imaging unit The figure which shows schematic structure of an image processing apparatus and a light source device The figure which shows one Embodiment of the light source device which provided the light-shielding member The figure which shows one Embodiment of the light source device which provided the reflection member The figure which shows one Embodiment which has arrange | positioned a near-infrared laser diode other than the optical axis of a condensing lens Illuminance distribution when excitation light is incident from a direction inclined by an incident angle of 20 ° with respect to the vertical direction of the light incident end face of the light guide, and excitation light is incident from the vertical direction on the light incident end face of the light guide. Graph showing experimental data with illuminance distribution in case The figure which shows one Embodiment which has arrange | positioned the near-infrared laser diode in the vicinity of the visible light lamp The figure which shows schematic structure of the conventional light source device

  Hereinafter, a rigid endoscope system using an embodiment of a light source device of the present invention will be described in detail with reference to the drawings. The rigid endoscope system of this embodiment is characterized by the configuration of the light source device. First, the configuration of the entire rigid endoscope 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 according to the present embodiment guides the normal light and excitation light emitted from the light source device 2 and the light source device 2 that emits white normal light and excitation light. A rigid mirror imaging apparatus that irradiates the observation unit and captures a normal image based on reflected light reflected from the observed portion by irradiation of normal light and a fluorescent image based on fluorescence emitted from the observed portion by irradiation of excitation light 10, a processor 3 that performs a predetermined process on the image signal captured by the rigid endoscope imaging device 10, and a monitor 4 that displays a normal image and a fluorescence image of the observed portion based on a display control signal generated by the processor 3. And.

  As shown in FIG. 1, the rigid endoscope imaging apparatus 10 includes a body cavity insertion unit 30 that is inserted into a body cavity, and an imaging unit 20 that captures a normal image and a fluorescence image of the observed portion guided by the body cavity insertion unit 30. And.

  Moreover, as shown in FIG. 2, the rigid-scope imaging device 10 has the body cavity insertion part 30 and the imaging unit 20 connected detachably. The body cavity insertion portion 30 includes a connection member 30a, an insertion member 30b, a cable connection portion 30c, an irradiation window 30d, and an imaging window 30e.

  The connection member 30a is provided at one end 30X of the body cavity insertion portion 30 (insertion member 30b) on the imaging unit 20 side. For example, the connection member 30a is fitted into an opening 20a formed in the imaging unit 20, thereby The body cavity insertion part 30 is 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. Inside the body cavity insertion section 30, a normal image and a fluorescence image of the observed part incident from the imaging window 30e are formed, guided to one end 30X on the imaging unit 20 side of the body cavity insertion section 30, and one end thereof A relay lens 30f (see FIG. 4) that emits light from the portion 30X is provided. The normal image and the fluorescence image emitted from the relay lens 30 f are incident on the imaging unit 20.

  As shown in FIG. 2, a cable connection portion 30c is provided on the side surface of the insertion member 30b, and the light guide LG is mechanically connected to the cable connection portion 30c by a connector C. Thereby, the light source device 2 and the insertion member 30b are optically connected via the light guide LG. In the body cavity insertion portion 30, a bundled multimode optical fiber 30g (see FIG. 4) that guides normal light and excitation light emitted from the light guide LG connected to the cable connection portion 30c. The multimode optical fiber 30g is provided to guide incident normal light and excitation light to the distal end portion 30Y of the insertion member 30b and irradiate the observed portion. The multimode optical fiber 30g provided in the insertion member 30b has its tip polished to form an irradiation window 30d.

  FIG. 3 is a diagram illustrating a schematic configuration of the imaging unit 20. The imaging unit 20 includes a first imaging system that captures the fluorescence image L4 of the observed part imaged by the relay lens 30f in the body cavity insertion part 30 and generates a fluorescence image signal of the observed part, and the body cavity insertion part And a second imaging system that generates a normal image signal by capturing a normal image L3 of the observed portion imaged by the relay lens 30f within 30. These imaging systems are divided into two optical axes orthogonal to each other by a dichroic prism 21 having a spectral characteristic that reflects the normal image L3 and transmits the fluorescent image L4.

  The first imaging system cuts light having a wavelength equal to or less than the wavelength of the excitation light reflected by the observed portion and transmitted through the dichroic prism 21 and an excitation light cut filter 22 that transmits fluorescent wavelength region illumination light, which will be described later, and a body cavity A first imaging optical system 23 that forms a fluorescent image L4 emitted from the insertion unit 30 and transmitted through the dichroic prism 21 and the excitation light cut filter 22, and a fluorescent image L4 formed by the first imaging optical system 23 And a high-sensitivity image pickup device 24 for picking up images.

  The high-sensitivity imaging element 24 detects light in the wavelength band of the fluorescent image L4 with high sensitivity, converts it into a fluorescent image signal, and outputs it. As the high sensitivity image sensor 24, for example, a monochrome image sensor can be used.

  The second imaging system includes a second imaging optical system 25 that forms a normal image L3 emitted from the body cavity insertion unit 30 and reflected by the dichroic prism 21, and a normal image formed by the second imaging optical system 25. An image sensor 26 that captures the image L3 is provided.

  The image sensor 26 detects light in the wavelength band of the normal image, converts it into a normal image signal, and outputs it. On the image pickup surface of the image pickup element 26, color filters of three primary colors red (R), green (G) and blue (B), or cyan (C), magenta (M) and yellow (Y) are arranged in a Bayer array or a honeycomb. It is provided in an array.

  In addition, the imaging unit 20 includes an imaging control unit 27. The imaging control unit 27 performs CDS / AGC (correlated double sampling / automatic gain control) processing and A / A processing on the fluorescence image signal output from the high-sensitivity imaging device 24 and the normal image signal output from the imaging device 26. A D-conversion process is performed and output to the processor 3 via the cable 5 (see FIG. 1).

  As shown in FIG. 4, the processor 3 includes a normal image input controller 41, a fluorescence image input controller 42, an image processing unit 43, a memory 44, a video output unit 45, an operation unit 46, a TG (timing generator) 47, and a CPU 48. ing.

  The normal image input controller 41 and the fluorescence image input controller 42 include a line buffer having a predetermined capacity, and the normal image input controller 41 receives a normal image signal for each frame output from the imaging control unit 27 of the imaging unit 20. The fluorescent image input controller 42 temporarily stores a fluorescent image signal. The normal image signal stored in the normal image input controller 41 and the fluorescent image signal stored in the fluorescent image input controller 42 are stored in the memory 44 via the bus.

  The image processing unit 43 receives the normal image signal and the fluorescence image signal for each frame read from the memory 44, performs predetermined image processing on these image signals, and outputs them to the bus.

  The video output unit 45 receives the normal image signal and the fluorescence 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. Output.

  The operation unit 46 receives input by the operator such as various operation instructions and control parameters. The TG 47 outputs a driving pulse signal for driving the high-sensitivity imaging device 24, the imaging device 26 of the imaging unit 20, and the LD driver 53 of the light source device 2 described later. The CPU 48 controls the entire apparatus.

  The processor 3 and the imaging unit 20 are connected via a cable 5 as shown in FIGS. 1 and 4. The cable 5 includes a signal wiring that propagates a normal image signal and a fluorescent image signal captured by the imaging unit 20, a control wiring that transmits a control signal output from the processor 3, and the like. A connector 5a and a connector 5b are provided at the tip of the cable 5. The cable 5 is detachably connected to the processor 3 via the connector 5a, and is detachably connected to the imaging unit 20 via the connector 5b. Is.

  As shown in FIG. 4, the light source device 2 includes a visible light lamp 50 that emits normal light (white light) L <b> 1 having a broadband wavelength of about 400 to 700 nm as diffused light, and a normal light emitted from the visible light lamp 50. An aspheric lens 51 that emits light L1 as substantially parallel light, a near-infrared laser diode 52 that emits excitation light L2, which is near-infrared light of 750 to 790 nm, and an LD that drives the near-infrared laser diode 52 The driver 53, the collimating lens 54 that is irradiated with the excitation light L <b> 2 emitted from the near infrared laser diode 52 and emitted as parallel light, and the normal light L <b> 1 emitted from the aspherical lens 51 and the collimating lens 54 are emitted. A condensing lens 55 that condenses the excitation light L2 and makes it incident on the light incident end surface 60 of the light guide LG described above is provided.

  As the visible light lamp 50, for example, a xenon lamp is used. Further, a near infrared light emitting diode may be used instead of the near infrared laser diode.

  In the present embodiment, as shown in FIG. 4, a parallel light source unit 70 including a visible light lamp 50 that emits normal light L1, a near-infrared laser diode 52, and a collimator lens 54 is used as a condensing lens. The parallel light source unit 70 is disposed on the optical path of the normal light L <b> 1 emitted from the visible light lamp 50.

  In the present embodiment, by arranging the parallel light source unit 70 as described above, the size can be reduced as compared with the conventional light source device.

  Specifically, in the light source device 2 of the present embodiment, the size in the direction orthogonal to the optical axis of the condenser lens 55 is about the lens diameter of the condenser lens 55. For example, when a precision aspheric lens manufactured by Edmund is used. Can be about 50 mm. On the other hand, in the case of the light source device using the conventional mirror as shown in FIG. 10, the size in the same direction is the lens diameter of the condensing lens, the length of the near infrared laser diode, and the collimating lens. The size is the sum of the focal lengths. For example, when a can-type laser diode manufactured by Edmund is used as a near-infrared laser diode, the length is 5 mm or more, and when a LIGHTPATH GRADIUM (registered trademark) lens manufactured by Edmund is used as a collimating lens. Since the focal length is 12.5 mm, the conventional light source device is 17.5 mm or larger.

  A connector 61 is provided at the tip of the light guide LG on which the normal light L1 and the excitation light L2 collected by the condenser lens 55 are incident. The light guide LG is connected to the light source device 2 via the connector 61. Is detachably connected. The light guide LG is composed of, for example, a bundled multimode optical fiber.

  By configuring as described above, as shown in FIG. 4, the normal light L1 and the excitation light L2 emitted from the condensing lens 55 of the light source device 2 are inserted into the light guide LG connected to the light source device 2 and the body cavity. The portion to be observed is irradiated via a multimode optical fiber 30 g provided in the portion 30.

  As described above, even if the parallel light source unit 70 is provided on the optical path of the normal light L1, the amount of the normal light L1 can be sufficiently large, and there is a diffraction effect, a diffusion effect, and the like. There will be no shadows that cause problems in the observed part.

  For the vignetting of the normal light L1 by the near infrared laser diode 52, for example, an Edmund precision aspheric lens having a lens diameter of 50 mm is used as the aspheric lens 51, and an Edmund having a diameter of 5.6 mm is used as the near infrared laser diode. When a laser diode manufactured is used, the transmission efficiency is 1- (5.6 / 50) = 99%, so there is no particular problem.

  In the present embodiment, near-infrared light is used as the excitation light L2. However, the present invention is not limited to this, and a narrower wavelength than normal light having a wideband wavelength is used. And the excitation light L2 is not limited to the light of the said wavelength range, It determines suitably with the kind of fluorescent pigment | dye, or the kind of biological tissue made to autofluoresce.

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

  First, the connector C of the light guide LG connected to the light source device 2 is connected to the cable connection portion 30c of the insertion member 30b of the body cavity insertion portion 30, and the connector 5b of the cable 5 connected to the processor 3 is connected to the imaging unit 20. Connected to.

  Next, after the light source device 2 is turned on, the user inserts the body cavity insertion part 30 into the body cavity, and the tip of the body cavity insertion part 30 is installed in the vicinity of the observed part.

Then, the normal light L 1 is emitted from the visible light lamp 50 of the light source device 2, and the normal light L 1 is made substantially parallel light by the aspherical lens 51 and then incident on the condensing lens 55. The light is incident on the light incident end surface 60 of LG. On the other hand, the excitation light L2 is emitted from the near-infrared laser diode 52 of the light source device 2, and the excitation light L2 passes through the collimator lens 54 and then enters the condensing lens 55. By the condensing lens 55, the light of the ride guide LG The light enters the incident end face 60.

  The normal light L1 and the excitation light L2 are guided by the light guide LG, are incident from the light incident end face of the multimode optical fiber 30g in the body cavity insertion portion 30, and are guided by the multimode optical fiber 30g. L1 and excitation light L2 are emitted from the distal end of the body cavity insertion portion 30 toward the observed portion.

  And the normal image based on the reflected light reflected from the observed part by the irradiation of the normal light L1 as described above is picked up, and the fluorescent image based on the fluorescence emitted from the observed part by the irradiation of the excitation light L2 is obtained. Imaged. It should be noted that ICG is administered to the observed part in advance, and fluorescence emitted from the ICG is imaged.

  Specifically, when the normal image is captured, the normal image L4 based on the reflected light reflected from the observed portion by the irradiation of the normal light L1 is incident from the distal end portion 30Y of the insertion member 30b, and the inside of the insertion member 30b. Are guided by the relay lens 30 f and emitted toward the imaging unit 20.

  The normal image L4 incident on the imaging unit 20 is reflected by the dichroic prism 21 in a direction perpendicular to the imaging device 26, and is imaged on the imaging surface of the imaging device 26 by the second imaging optical system 25. 26 sequentially captures images at a predetermined frame rate.

  The normal image signals sequentially output from the image sensor 26 are subjected to CDS / AGC (correlated double sampling / automatic gain control) processing and A / D conversion processing in the imaging control unit 27, and then the processor via the cable 5. 3 are sequentially output.

  The normal image signal input to the processor 3 is temporarily stored in the normal image input controller 41 and then stored in the memory 44. Then, the normal image signal for each frame read from the memory 44 is subjected to gradation correction processing and sharpness correction processing in the image processing unit 43 and then sequentially output to the video output unit 45.

  Then, the video output unit 45 performs a predetermined process on the input normal image signal to generate a display control signal, and sequentially outputs the display control signal for each frame to the monitor 4. The monitor 4 displays a normal image based on the input display control signal.

  On the other hand, at the time of capturing a fluorescent image, a fluorescent image L5 based on the fluorescence emitted from the observed portion by irradiation with the excitation light L2 is incident from the distal end portion 30Y of the insertion member 30b, and the relay lens 30f in the insertion member 30b. Is guided toward the image pickup unit 20.

  The fluorescence image L5 incident on the imaging unit 20 passes through the dichroic prism 21 and the excitation light cut filter 22, and is then imaged on the imaging surface of the high-sensitivity imaging device 24 by the first imaging optical system 23, and has high sensitivity. Images are taken at a predetermined frame rate by the image sensor 24.

  The fluorescent image signals sequentially output from the high-sensitivity image sensor 24 are subjected to CDS / AGC (correlated double sampling / automatic gain control) processing and A / D conversion processing in the imaging control unit 27, and then passed through the cable 5. Are sequentially output to the processor 3.

  The fluorescence image signal input to the processor 3 is temporarily stored in the fluorescence image input controller 42 and then stored in the memory 44. Then, the fluorescence image signal for each frame read from the memory 44 is subjected to predetermined image processing in the image processing unit 43 and then sequentially output to the video output unit 45.

  Then, the video output unit 45 performs a predetermined process on the input fluorescent image signal to generate a display control signal, and sequentially outputs the display control signal for each frame to the monitor 4. The monitor 4 displays a fluorescent image based on the input display control signal.

  In the rigid endoscope system of the above embodiment, since the near-infrared laser diode 52 is provided on the optical path of the normal light L1 as described above, the normal light L1 is applied to the near-infrared laser diode 52. As a result, the near-infrared laser diode may generate heat and break down.

  Therefore, as shown in FIG. 5, a light blocking member 56 (heat generation suppressing member) that prevents the near-infrared laser diode 52 from being irradiated with the normal light L1 on a part of the surface of the aspheric lens 51 on the visible light lamp 50 side. May be provided. As the light shielding member 56, a member that reflects the normal light L1 may be used, or a member that absorbs the normal light L1 may be used. When a member that reflects the normal light L1 is used as the light shielding member 56, it is desirable that the direction in which the normal light L1 is reflected be a direction other than the direction of the visible light lamp 50.

  In FIG. 5, the light shielding member 56 is provided on the visible light lamp 50 side of the aspheric lens 51. However, the present invention is not limited to this, and is provided on the near infrared laser diode 52 side of the aspheric lens 51. Alternatively, it may be provided separately from the aspheric lens 51.

  In addition, as shown in FIG. 6, a reflection member 57 that reflects the normal light L <b> 1 may be provided on the visible light lamp 50 side of the near-infrared laser diode 52. The reflecting member 57 is also preferably configured such that the direction in which the normal light L1 is reflected is a direction other than the visible light lamp 50 direction. Alternatively, a heat insulating member may be provided for the near infrared laser diode 52 instead of the reflecting member 57. A known material can be used as the material of the heat insulating member. Further, both the heat insulating member and the reflecting member may be provided for the near infrared laser diode 52.

  In the rigid endoscope system of the above embodiment, the near-infrared laser diode 52 and the collimator lens 54 are arranged on the optical axis of the condensing lens 55. You may make it provide the near-infrared laser diode 52 and the collimating lens 54 on the straight line parallel to an optical axis.

  Specifically, for example, as in the light source device 6 illustrated in FIG. 7, the parallel light source unit 70 may be provided so that the excitation light L <b> 2 passes through the vicinity of the end in the radial direction of the condenser lens 55. .

  Here, when the parallel light source unit 70 is arranged as shown in FIG. 7, the excitation light L2 collected by the condenser lens 55 is perpendicular to the light incident end surface 60 of the light guide LG (optical axis direction). ) From a direction inclined by a predetermined incident angle. Thus, when the excitation light L2 is incident from the direction inclined by a predetermined incident angle with respect to the light incident end surface 60 of the light guide LG, the excitation light L2 is incident from the vertical direction with respect to the light incident end surface 60 of the light guide LG. Compared with the case where it did, the irradiation range of the excitation light L2 irradiated to a to-be-observed part can be expanded. Therefore, when it is desired to secure a relatively wide irradiation range of the excitation light L2, it is desirable to adopt a configuration as shown in FIG.

  FIG. 8 shows the illuminance distribution when the excitation light L2 is incident from a direction inclined by an incident angle of 20 ° with respect to the vertical direction of the light incident end face 60 of the light guide LG, and the light incident end face 60 of the light guide LG. The experimental data with the illuminance distribution when the excitation light L2 is incident from the vertical direction are shown. As shown in FIG. 8, when the excitation light L2 is incident from a direction inclined by an incident angle of 20 ° with respect to the vertical direction of the light incident end face 60 of the light guide LG, it propagates in the multimode optical fiber of the light guide LG. The excitation light L2 emitted in this way forms two illuminance distributions having a peak, and these two illuminance distributions are partially overlapped to produce a relatively wide illuminance distribution. Can be formed. The incident angle of the excitation light L2 is not limited to 20 °, but may be other incident angles. That is, the parallel light source unit 70 may be arranged so that the incident angle of the excitation light L2 becomes another incident angle. However, if the incident angle is increased too much, the distance between the two illuminance distributions increases and the illuminance also decreases, and it becomes impossible to irradiate the excitation light L2 with sufficient illuminance. It is desirable to set

  In the rigid endoscope system of the above embodiment, the normal light L1 emitted from the visible light lamp 50 is made substantially parallel by the aspherical lens 51 and then incident on the condenser lens 55. However, the present invention is not limited to this. For example, the normal light L1 emitted from the visible light lamp 50 may be directly incident on the condenser lens 55 without providing the aspherical lens 51 as in the light source device 7 shown in FIG. In such a configuration, the parallel light source unit 70 including the near-infrared laser diode 52 and the collimating lens 54 is in the vicinity of the visible light lamp 50 outside the optical path of the normal light L1, as shown in FIG. In addition, the excitation light L <b> 2 may be disposed at a position where it can enter the condenser lens 55. Even when the parallel light source unit 70 is arranged in this manner, the excitation light L2 is incident from a direction inclined by a predetermined incident angle with respect to the light incident end surface 60 of the light guide LG, similarly to the light source device 6 shown in FIG. Therefore, the irradiation range of the excitation light L2 in the observed portion can be expanded.

  In the above embodiment, the fluorescent image is captured by the first imaging system. However, the present invention is not limited to this, and an image based on the light absorption characteristics of the observed part by irradiating special light to the observed part is captured. You may make it do.

  Moreover, although the said embodiment applies the light source device of this invention to a rigid endoscope system, you may apply not only to this but a flexible endoscope system, for example.

DESCRIPTION OF SYMBOLS 1 Rigid endoscope system 2, 6, 7 Light source device 3 Processor 4 Monitor 10 Rigid endoscope imaging device 20 Imaging unit 24 High sensitivity imaging device 26 Imaging device 30 Body cavity insertion part 30f Relay lens 30g Multimode optical fiber 50 Visible light lamp 51 Aspherical surface Lens 52 Near-infrared laser diode 54 Collimating lens 55 Condensing lens 56 Light shielding member 57 Reflecting member 60 Light incident end face 70 Parallel light source section

Claims (16)

A diffuse light source that emits diffuse light;
A parallel light source that emits parallel light;
A condensing lens that condenses the diffused light and the parallel light and enters the light incident end face of a predetermined light guide member;
The light source device, wherein the diffused light source and the parallel light source unit are arranged on a straight line parallel to the optical axis of the condenser lens.   The light source device according to claim 1, wherein the parallel light source unit is disposed on an optical path of the diffused light.   The light source device according to claim 1, wherein the parallel light source unit is disposed on a position other than the optical axis of the condenser lens on the optical path of the diffused light.   2. The parallel light source unit is disposed in the vicinity of the diffused light source outside the optical path of the diffused light and at a position where the parallel light can enter the condenser lens. Light source device.   The light source device according to claim 4, wherein the parallel light emitted from the parallel light source unit is incident from a position other than the optical axis of the condenser lens.   The light source device according to claim 2, wherein a heat generation suppressing member for suppressing heat generation due to the diffusion light irradiation to the parallel light source unit is provided. A lens provided between the diffuse light source and the parallel light source unit;
The light source device according to claim 6, wherein the heat generation suppressing member is a light blocking member that blocks the diffused light that passes through the lens and is applied to the parallel light source unit.   The light source device according to claim 7, wherein the light shielding member is provided on the lens.   The light source device according to claim 7, wherein the light shielding member is provided in the parallel light source unit.   The light source device according to claim 7, wherein the light shielding member is a reflecting member that reflects the diffused light.   The light source device according to claim 10, wherein the reflecting member reflects the diffused light in a direction other than a direction in which the diffused light source is installed.   The light source device according to claim 7, wherein the light shielding member is an absorbing member that absorbs the diffused light.   The light source device according to claim 6, wherein the heat generation suppressing member is a heat insulating member provided for the parallel light source unit.   The light source device according to claim 1, wherein the parallel light source unit includes a laser diode or a light emitting diode.   The light source device according to claim 1, wherein the parallel light source unit emits near infrared light as the parallel light.   The light source device according to claim 1, wherein the diffused light source emits white light as the diffused light.

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