JP6277068B2 - Endoscope light source device and endoscope system - Google Patents

Description

  The present invention relates to an endoscope light source device and an endoscope system having an excitation light source and a phosphor.

  In recent medical treatments, diagnosis and the like using an endoscope system including an endoscope light source device, an electronic endoscope, and a processor device are widely performed. The endoscope light source device generates illumination light and irradiates the sample. The electronic endoscope generates an imaging signal by imaging an inside of a specimen irradiated with illumination light with an imaging element. The processor device performs image processing on the imaging signal generated by the electronic endoscope, and generates an observation image to be displayed on the monitor.

  Conventionally, in an endoscope light source device, a lamp light source such as a xenon lamp or a halogen lamp that emits white light as illumination light has been used, but recently, a light of a specific color is emitted instead of the lamp light source. Semiconductor light sources such as laser diodes (LDs) and light emitting diodes (LEDs) are being used.

  In addition, in order to increase the brightness of illumination light, an excitation light source (blue LD) that emits excitation light (blue light), a phosphor that emits fluorescence (green light) upon incidence of excitation light, and excitation light is reflected. An endoscope light source device is known in which a dichroic mirror is provided as an optical member that transmits fluorescence (see Patent Document 1). In this endoscope light source device, the excitation light emitted from the excitation light source is reflected by the dichroic mirror and applied to the phosphor. The phosphor emits green light toward the dichroic mirror in response to the excitation light irradiation. This fluorescence is emitted through the dichroic mirror.

  In the endoscope light source device described in Patent Document 1, in order to generate blue light, red light, and violet light in addition to green light, a blue light source (blue LED), a red light source (red LED), and a purple light source are generated. (Purple LED) is provided. Further, in order to integrate the optical path of these lights with the optical path of the fluorescence (green light) from the phosphor, one dichroic mirror is provided for each light source.

  Of these lights, violet light is light that is easily absorbed by hemoglobin on the surface layer of the living tissue and is reflected almost without diffusing into the living tissue around the blood vessel. Green light is light that diffuses deeper into the living tissue than violet light, and is more absorbed by hemoglobin. For this reason, in the blood vessel enhancement observation mode for emphasizing the blood vessels on the surface of the living tissue, only purple light and green light are used as illumination light.

  However, the blood vessel-enhanced observation image obtained using only purple light and green light as illumination light is a pseudo-color image that is darker than normal observation images using white light and has low color reproducibility. It is known that white light is used and an image with high blood vessel contrast is obtained by reducing the light intensity in the wavelength band of 460 nm to 500 nm from the white light (see Patent Document 2). This is because light in the wavelength band of 460 nm to 500 nm is hardly absorbed by hemoglobin and is likely to be reflected or scattered.

JP 2013-215435 A Japanese Patent No. 5306447

  In the endoscope light source device described in Patent Document 1, each light source emits light to generate white light, and light intensity in a wavelength band of 460 nm to 500 nm as described in Patent Document 2 is reduced from the white light. It is conceivable to obtain an image with high blood vessel contrast.

  However, in the endoscope light source device described in Patent Document 1, green light is generated by a phosphor and thus has high luminance, whereas blue light is generated by an LED and thus has low luminance. . The wavelength band of 460 nm to 500 nm includes a part of the long wavelength side of the blue light and a part of the low wavelength side of the green light. Therefore, when the light intensity in this wavelength band is reduced, the light intensity of the blue light is further increased. It causes a drop and becomes unbalanced with green light.

  For example, in distant view observation where the imaging distance to the specimen is large, it is preferable to increase the amount of illumination light because the brightness of the observation image is reduced, but the blue light generated by the LED cannot increase the amount of light, Unbalanced with green light.

  The present invention relates to an endoscope light source device and an endoscope system having an excitation light source and a phosphor, and has a light intensity in a wavelength band of 460 nm or more and 500 nm or less while maintaining a balance between the intensity of green light and blue light. An object is to provide an endoscope light source device and an endoscope system that can be reduced.

In order to achieve the above object, an endoscope light source device of the present invention includes an excitation light source that emits excitation light, a first region that emits green first fluorescence when irradiated with excitation light, and a blue color when irradiated with excitation light. A second fluorescent region that emits the second fluorescence, and the first region and the second region pass through the excitation light irradiation position with rotation, a purple light source that emits purple light, and an excitation light source The excitation light incident through the first optical path is reflected on one surface and emitted to the second optical path toward the rotating phosphor, and the first fluorescence and the second fluorescence incident from the rotating phosphor through the second optical path are reflected on one side. A first dichroic mirror that is transmitted from the surface and emitted to the third optical path, and the violet light incident from the violet light source through the fourth optical path is reflected by the other surface and emitted to the third optical path; and the second optical path or the second optical path 460 nm from the first fluorescence and the second fluorescence provided on the three optical paths It comprises a notch filter to reduce the light intensity of a wavelength band above 500 nm, the. The endoscope light source device of the present invention emits an excitation light source that emits excitation light, a first region that emits green first fluorescence when irradiated with excitation light, and a blue second fluorescence when irradiated with excitation light. A rotating phosphor in which the first region and the second region pass through the excitation light irradiation position with rotation, a violet light source that emits violet light, and an incident light from the excitation light source through the first optical path. The excitation light to be transmitted is transmitted from one surface and emitted to the second optical path toward the rotating phosphor, and the first fluorescence and the second fluorescence incident from the rotating phosphor through the second optical path are reflected by the other surface to be The first dichroic mirror that emits violet light that is emitted from the violet light source through the fourth optical path and is transmitted from one surface and is emitted to the third optical path and the second optical path or the third optical path. 460 nm or more and 500 nm or less from the first fluorescence and the second fluorescence It comprises a notch filter to reduce the light intensity of the wavelength band, the.

  The peak wavelength of the excitation light and the second fluorescence is preferably 460 nm or less, and the peak wavelength of the first fluorescence is preferably 500 nm or more.

  It is preferable to include a red light source that emits red light and a second optical member that integrates an optical path of red light emitted from the red light source into the third optical path.

  The violet light source emits violet light during the first period when the first region passes through the excitation light irradiation position, and the red light source emits red light during the second period when the second region passes through the excitation light irradiation position. It is preferable to emit light.

  The first region may include a phosphor material that emits red third fluorescence when irradiated with excitation light, and may emit yellow light in which the first fluorescence and the third fluorescence are mixed.

  The rotating phosphor has a third region that emits red third fluorescence when irradiated with excitation light, and the first region, the second region, and the third region pass through the excitation light irradiation position with rotation. There may be. In this case, it is preferable that the violet light source emits violet light during the second period in which the second region passes through the excitation light irradiation position.

  The excitation light source changes the emission intensity of the excitation light between the first period in which the first region passes the excitation light irradiation position and the second period in which the second region passes the excitation light irradiation position. It is preferable to do.

An endoscope system according to the present invention includes an excitation light source that emits excitation light, a first region that emits green first fluorescence when irradiated with excitation light, and a second region that emits blue second fluorescence when irradiated with excitation light. A rotating phosphor in which the first region and the second region pass through the excitation light irradiation position with rotation, a violet light source that emits violet light, and excitation light incident from the excitation light source via the first optical path The light is transmitted from one surface and emitted to the second optical path toward the rotating phosphor, and the first fluorescence and the second fluorescence incident from the rotating phosphor through the second optical path are reflected by one surface and emitted to the third optical path. The first dichroic mirror that transmits the violet light incident from the violet light source via the fourth optical path from the other surface and exits to the third optical path and the second fluorescent path or the third optical path is provided. And a wavelength band from 460 nm to 500 nm from the second fluorescence. A light source device comprising: a notch filter that reduces the light intensity of the light source; an endoscope having an imaging element that captures reflected light from an observation site irradiated with at least one of the first fluorescence and the second fluorescence; and the light source device And a control unit that controls the image sensor. The endoscope system of the present invention also includes an excitation light source that emits excitation light, a first region that emits green first fluorescence when irradiated with excitation light, and a second region that emits blue second fluorescence when irradiated with excitation light. A rotating phosphor in which the first region and the second region pass through the excitation light irradiation position with rotation, a purple light source that emits violet light, and excitation that is incident from the excitation light source via the first optical path Light is transmitted from one surface and emitted to the second optical path toward the rotating phosphor, and the first fluorescence and the second fluorescence incident from the rotating phosphor through the second optical path are reflected by the other surface to form the third optical path. injected into the violet light incident from violet light source through the fourth optical path by transmitting from one side, a first dichroic mirror for emitting the third light path, provided in the second optical path or the third optical path, the 460 nm or more and 500 nm or less from 1 fluorescence and 2nd fluorescence A light source device comprising a notch filter for reducing long-band light intensity, and an endoscope having an imaging device for imaging reflected light from an observation site irradiated with at least one of the first fluorescence and the second fluorescence, A control unit that controls the light source device and the image sensor.

  According to the present invention, the rotating phosphor has a first region emitting green first fluorescence and a second region emitting blue second fluorescence, and the first fluorescence and the second fluorescence emitted from the rotating phosphor. Since a notch filter for reducing the light intensity in the wavelength band of 460 nm to 500 nm is provided on the fluorescent light path, the wavelength band of 460 nm to 500 nm is maintained while maintaining the balance of the intensity of green light and blue light. Light intensity can be reduced.

It is an external view of an endoscope system. It is a front view of the front-end | tip part of an endoscope. It is a block diagram which shows the electric constitution of an endoscope system. It is a figure which shows the structure of a color filter array. It is a figure which shows the structure of a light source part. It is a figure which shows the structure of a rotation fluorescent substance. It is a graph which shows the wavelength spectrum of illumination light. It is a graph which shows the optical characteristic of 1st DM. It is a graph which shows the optical characteristic of a notch filter. It is a graph which shows the optical characteristic of 2nd DM. It is a timing diagram explaining the drive timing of a light source part and an image pick-up element. It is a timing diagram explaining the generation timing of image data. It is a graph which shows the optical characteristic of the notch filter provided in the injection | emission side of 2nd DM. It is a graph which shows the optical characteristic of 1st DM which gave the notch characteristic. It is a graph which shows the optical characteristic of 2nd DM which gave the notch characteristic. It is a figure which shows the modification of a light source part. It is a figure which shows the structure of the rotation fluorescent substance of 3rd Embodiment. It is a figure which shows the structure of the rotation fluorescent substance of 4th Embodiment.

[First Embodiment]
In FIG. 1, an endoscope system 10 includes an electronic endoscope (hereinafter simply referred to as an endoscope) 11 that images an observation site in a living body as a specimen, and an observation site based on an imaging signal obtained by imaging. A processor device 12 that generates a display image, an endoscope light source device (hereinafter simply referred to as a light source device) 13 that supplies illumination light for irradiating an observation site to the endoscope 11, and a monitor 14 that displays the display image It has. An operation input unit 15 such as a keyboard or a mouse is connected to the processor device 12.

  The endoscope 11 connects the insertion unit 16 inserted into the digestive tract of a living body, the operation unit 17 provided at the proximal end portion of the insertion unit 16, and the endoscope 11 to the processor device 12 and the light source device 13. And a universal cord 18 for the purpose. The insertion portion 16 includes a distal end portion 19, a bending portion 20, and a flexible tube portion 21, and is connected in this order from the distal end side.

  As shown in FIG. 2, an illumination window 22 that irradiates the observation site with illumination light, an observation window 23 for capturing an image of the observation site, and an observation window 23 are washed on the distal end surface of the distal end portion 19. An air supply / water supply nozzle 24 for supplying air and water and a forceps outlet 25 for performing various treatments by projecting a treatment tool such as a forceps or an electric knife are provided. An imaging element 33 (see FIG. 3) is built in the back of the observation window 23.

  The bending portion 20 is composed of a plurality of connected bending pieces, and bends in the vertical and horizontal directions according to the operation of the angle knob 26 of the operation portion 17. By curving the bending portion 20, the distal end portion 19 is directed in a desired direction. The flexible tube portion 21 has flexibility and can be inserted into a tortuous tube passage such as an esophagus or an intestine. The insertion unit 16 guides the drive signal for driving the image sensor 33, the signal cable for transmitting the image signal output from the image sensor 33, and the illumination light supplied from the light source device 13 to the illumination window 22. A light guide 32 (see FIG. 3) is inserted.

  In addition to the angle knob 26, the operation unit 17 includes a forceps port 27 for inserting a treatment instrument, an air / water supply button 28 that is operated when air / water is supplied from the air / water supply nozzle 24, a still image. A freeze button (not shown) or the like is provided for photographing the image.

  A communication cable and a light guide 32 extending from the insertion portion 16 are inserted into the universal cord 18, and a connector 29 is attached to one end of the processor device 12 and the light source device 13. The connector 29 is a composite type connector composed of a communication connector 29a and a light source connector 29b. The communication connector 29a and the light source connector 29b are detachably connected to the processor device 12 and the light source device 13, respectively. One end of a communication cable is disposed on the communication connector 29a. An incident end 32a (see FIG. 3) of the light guide 32 is disposed on the light source connector 29b.

  In FIG. 3, the light source device 13 includes a light source unit 30 and a light source control unit 31. The light source unit 30 outputs illumination light based on the control of the light source control unit 31. The illumination light output from the light source unit 30 enters the incident end 32 a of the light guide 32 of the endoscope 11.

  The endoscope 11 includes a light guide 32, an imaging device 33, an imaging drive unit 34, an analog processing circuit (AFE: Analog Front End) 35, an irradiation lens 36, and an objective optical system 37. . The light guide 32 is a fiber bundle obtained by bundling a plurality of optical fibers. When the light source connector 29 b is connected to the light source device 13, the incident end 32 a of the light guide 32 disposed on the light source connector 29 b faces the emission end of the light source unit 30. The exit end of the light guide 32 located at the distal end portion 19 branches into two at the front stage of the illumination window 22 so that light is guided to the two illumination windows 22 respectively.

  An irradiation lens 36 is disposed in the back of the illumination window 22. The illumination light supplied from the light source device 13 is guided to the irradiation lens 36 by the light guide 32 and irradiated from the illumination window 22 toward the observation site. The irradiation lens 36 is a concave lens, and irradiates the illumination light emitted from the light guide 32 to a wide range of the observation site.

  An imaging element 33 is disposed behind the observation window 23 via an objective optical system 37. The image (reflected light) of the observation site is incident on the objective optical system 37 through the observation window 23, and is formed on the imaging surface 33 a of the image sensor 33 by the objective optical system 37.

  The imaging device 33 is a single-plate color CCD (Charge Coupled Device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor) image sensor, and a plurality of pixels that generate pixel signals by photoelectric conversion are formed on the imaging surface 33a. Yes. A color filter array 38 shown in FIG. 4 is provided on the imaging surface 33a. The color filter array 38 includes a red (R) filter 38a, a green (G) filter 38b, and a blue (B) filter 38c. Each filter 38a, 38b, 38c is disposed on the light incident side corresponding to one pixel. The color array of the color filter array 38 is called a Bayer array. Further, microlenses (not shown) are provided on the color filter array 38 corresponding to the respective pixels.

  The pixel in which the R filter 38a is disposed receives red light LR described later. The pixel in which the G filter 38b is disposed receives green light LG described later. The pixel in which the B filter 38c is disposed receives blue light LB and violet light LV, which will be described later.

  The image pickup device 33 is driven by the image pickup drive unit 34, picks up an image formed on the image pickup surface 33a with a plurality of pixels via the color filter array 38, and outputs an image pickup signal. The imaging signal includes one of R, G, and B color signals (R signal, G signal, and B signal) for each pixel.

  The AFE 35 includes a correlated double sampling (CDS) circuit, an automatic gain control (AGC) circuit, an analog / digital (A / D) converter, and the like. The CDS circuit performs correlated double sampling processing on the imaging signal input from the imaging element 33 to remove noise. The AGC circuit amplifies the imaging signal from which noise has been removed by the CDS circuit. The A / D converter converts the imaging signal amplified by the AGC circuit into a digital signal having a predetermined number of bits and inputs the digital signal to the processor device 12.

  The processor device 12 includes a controller 40 as a control unit, a DSP (Digital Signal Processor) 41, a frame memory 42, an image processing unit 43, and a display control unit 44. The controller 40 has a CPU (Central Processing Unit), a ROM (Read Only Memory) that stores control programs and setting data necessary for control, a RAM (Random Access Memory) as a working memory for loading the control programs, and the like. The CPU executes the control program to control each unit of the processor device 12, the light source control unit 31, and the imaging drive unit 34.

  The DSP 41 performs signal processing such as pixel interpolation processing, gamma correction, and white balance correction on the imaging signal input from the AFE 35 via the communication connector 29a. In the pixel interpolation processing, pixel interpolation processing is performed for each of the R signal, the G signal, and the B signal. The DSP 41 causes the frame memory 42 to store the imaged signal subjected to signal processing as image data for each frame period.

  The image processing unit 43 reads the image data from the frame memory 42 and performs predetermined image processing to generate an observation image. The display control unit 44 converts the image generated by the image processing unit 43 into a video signal such as a composite signal or a component signal and outputs the video signal to the monitor 14.

  In FIG. 5, the light source unit 30 includes a rotating phosphor 50, a rotating motor 51, a motor driving unit 52, a violet laser diode (V-LD) 53, an LD driving unit 54, and first and second dichroic mirrors. (DM) 55a, 55b, first to fifth lenses 56a to 56e, a purple LED (V-LED) 57a, a red LED (R-LED) 57b, an LED driving unit 58, and a notch filter 59. Have. The V-LD 53, the V-LED 57a, and the R-LED 57b correspond to an excitation light source, a violet light source, and a red light source described in the claims, respectively.

  The rotating phosphor 50 includes a disk-shaped wheel plate 60 and a phosphor layer 61 provided on one surface of the wheel plate 60. The wheel plate 60 is made of a metal such as copper, aluminum, or stainless steel.

  As shown in FIG. 6, the phosphor layer 61 is embedded in a recess 62 formed on one surface of the wheel plate 60. The recess 62 is formed in a circumferential shape centering on the rotation shaft 63 of the wheel plate 60. The phosphor layer 61 is divided into a first region 61a that emits green light LG (first fluorescence) and a second region 61b that emits blue light LB (second fluorescence). The first region 61 a and the second region 61 b are regions that divide the circumferential phosphor layer 61 around the rotation axis 63 in half.

The first region 61a is a binder (not shown), as a fluorescent material, for example, _{β-SiAlON (β-Si 6} -x Al x O x N 8-x) is an area in which are dispersed, as an excitation light source In response to the excitation light LE emitted from the V-LD 53, green light LG is emitted. The second region 61b is a region in which, for example, BAM (BaMgAl ₁₀ O ₁₇ : Eu ²⁺ ) is dispersed as a phosphor material in a binder (not shown), and emits blue light LB upon receiving excitation light LE. As shown in FIG. 7, the green light LG has a wavelength band of about 480 nm to 600 nm and a peak wavelength of about 540 nm. The blue light LB has a wavelength band of about 410 nm to 510 nm and a peak wavelength of about 460 nm.

  The blue light LB is light that is largely absorbed by hemoglobin on the surface of the living tissue and is reflected without being diffused into the living tissue around the blood vessel. The green light LG is light that diffuses deeper into the living tissue than the blue light LB, and is much absorbed by hemoglobin.

  The LD drive unit 54 generates an LD drive signal (drive current or drive voltage) for driving the V-LD 53 based on the control of the light source control unit 31 and supplies the LD drive signal to the V-LD 53. The V-LD 53 has a plurality of LD elements (not shown) arranged in a two-dimensional array. As shown in FIG. 7, the V-LD 53 emits violet laser light having a peak wavelength of about 405 nm as excitation light LE.

  The first lens 56a is disposed on the optical path of the excitation light LE emitted from the V-LD 53, collects the excitation light LE, and makes it incident on the first DM 55a. Hereinafter, the optical path from the V-LD 53 to the first DM 55a is referred to as a first optical path R1. The first DM 55a is arranged such that the first optical path R1 forms an angle of 45 ° with respect to one surface. As shown in FIG. 8, the first DM 55a has a threshold λ1 at about 425 nm, transmits light having a wavelength equal to or greater than the threshold λ1, and reflects light having a wavelength smaller than the threshold λ1. That is, the first DM 55a reflects the excitation light LE incident from the first lens 56a.

  The second lens 56 b is disposed on the optical path of the excitation light LE reflected by the first DM 55 a, collects the excitation light LE, and makes it incident on the rotating phosphor 50. Specifically, the excitation light LE is collected by the second lens 56 b and is applied to the phosphor layer 61 of the rotating phosphor 50. Hereinafter, the optical path from the first DM 55a to the rotating phosphor 50 is referred to as a second optical path R2. The second optical path R2 forms an angle of 90 ° with the first optical path R1.

  The rotation motor 51 rotates the wheel plate 60 around the rotation shaft 63. The motor drive unit 52 generates a rotation drive signal based on the control of the light source control unit 31 and supplies the rotation drive signal to the rotation motor 51. The rotation motor 51 rotates the wheel plate 60 according to the rotation drive signal. The excitation light LE is continuously applied to a part of the phosphor layer 61 in a state where the wheel plate 60 is rotationally driven. Therefore, with the rotation of the wheel plate 60, the first region 61a and the second region 61b pass through the irradiation position 64 (see FIG. 6) of the excitation light LE, and the green light LG and the blue light LB are alternately emitted. .

  The green light LG and the blue light LB emitted from the rotating phosphor 50 are collected by the second lens 56b and emitted toward the first DM 55a. The green light LG and the blue light LB enter the first DM 55a through the second optical path R2. Since the first DM 55a has the optical characteristics described above, almost all components of the green light LG and the blue light LB are transmitted through the first DM 55a and emitted from the first DM 55a. Hereinafter, the optical paths of the green light LG and the blue light LB emitted from the first DM 55a are referred to as a third optical path R3. The third optical path R3 forms an angle of 90 ° with the first optical path R1.

  As shown in FIG. 7, the V-LED 57a emits purple light LV having a wavelength band of about 395 nm to 415 nm and a peak wavelength of about 405 nm. The purple light LV is light that is more easily absorbed by hemoglobin on the surface of the living tissue than the blue light LB, and is reflected without being diffused into the living tissue around the blood vessel. The R-LED 57b emits red light LR having a wavelength band of about 580 nm to 640 nm and a peak wavelength of about 620 nm.

  The LED drive unit 58 generates an LED drive signal (drive current or drive voltage) for driving each of the V-LED 57a and the R-LED 57b based on the control of the light source control unit 31, and the V-LED 57a and R- It supplies to LED57b.

  The third lens 56c is disposed on the optical path of the purple light LV emitted from the V-LED 57a, and collects the purple light LV. The first DM 55a described above is arranged in the optical path of the purple light LV emitted from the third lens 56c.

  Specifically, in the first DM 55a, the purple light LV emitted from the third lens 56c is incident at an angle of 45 ° with respect to the other surface (the surface opposite to the surface on which the excitation light LE is incident). Are arranged as follows. Since the first DM 55a has the optical characteristics described above, the first DM 55a reflects the violet light LV incident from the third lens 56c. Thereby, the optical path of the purple light LV is integrated into the third optical path R3 through which the green light LG and the blue light LB propagate.

  A notch filter 59 is disposed on the third optical path R3. As shown in FIG. 9, the optical characteristic of the notch filter 59 is that the light transmittance with respect to the wavelength band of 460 nm to 500 nm (460 nm to 500 nm) is α (for example, α = 30%), and the other transmittance is Nearly 100%. That is, the notch filter 59 reduces the light intensity in the wavelength band of 460 nm to 500 nm from the blue light LB and the green light LG. The light transmittance α is preferably a value that makes the light intensity in the wavelength band of 460 nm to 500 nm within the range of 20% to 70% with respect to the light intensity at the peak wavelength of the blue light LB. However, the light transmittance α is not limited to a value satisfying this, and may be, for example, 0%.

  The fourth lens 56d is disposed on the optical path of the red light LR emitted from the R-LED 57b, and condenses the red light LR. A second DM 55b is disposed in the optical path of the red light LR emitted from the fourth lens 56d. As shown in FIG. 10, the second DM 55b has a threshold λ2 at about 580 nm, reflects light having a wavelength equal to or greater than the threshold λ2, and transmits light having a wavelength smaller than the threshold λ2.

  In the second DM 55b, the optical path of the red light LR emitted from the fourth lens 56d forms an angle of 45 ° with respect to one surface, and the third optical path R3 forms an angle of 45 ° with respect to the other surface. Are arranged as follows. Almost all components of the light transmitted through the notch filter 59 are transmitted through the second DM 55b, and the red light LR is reflected by the second DM 55b. Thereby, the optical path of the red light LR is integrated with the third optical path R3 through which the light transmitted through the notch filter 59 propagates.

  The fifth lens 56e is disposed on the third optical path R3 through which the violet light LV, the blue light LB, the green light LG, and the red light LR emitted from the second DM 55b propagate, and collects these lights. The fifth lens 56e is disposed in the vicinity of the light source connector 29b, and causes the collected light to enter the incident end 32a of the light guide 32.

  Next, the drive timing of the light source unit 30 and the image sensor 33 will be described. The controller 40 controls the light source control unit 31 and the imaging drive unit 34 so that the rotation of the rotating phosphor 50, the light emission of the V-LED 57a and the R-LED 57b, and the imaging of the imaging device 33 are controlled in synchronization with each other. Is done.

  The controller 40 controls the light emission timing of the V-LED 57 a and the R-LED 57 b and the imaging timing of the image sensor 33 based on the detection value of a rotational position detection sensor (not shown) that detects the rotational position of the wheel plate 60. To do.

  Specifically, the controller 40 rotates the wheel plate 60 of the rotating phosphor 50 with a constant period T, and drives the V-LD 53 to emit the excitation light LE. The emission intensity of the excitation light LE is constant. As shown in FIG. 11, the first half of the rotation period T is a period during which the first region 61a passes through the irradiation position 64 of the excitation light LE (hereinafter referred to as a first period P1), and the green light LG is Be emitted. The second half of the rotation period T is a period during which the second region 61b passes through the irradiation position 64 (hereinafter referred to as a second period P2), and blue light LB is emitted.

  The controller 40 drives the V-LED 57a only during the first period P1 to generate purple light LV, and drives the R-LED 57b only during the second period P2 to generate red light LR. Thereby, in the first period P1, light (hereinafter referred to as first illumination light) obtained by combining the green light LG and the purple light LV is supplied from the light source unit 30 to the light guide 32 of the endoscope 11. The In the second period P2, light (hereinafter referred to as second illumination light) obtained by combining the blue light LB and the red light LR is supplied from the light source unit 30 to the light guide 32 of the endoscope 11.

  The controller 40 causes the image sensor 33 to perform an imaging operation in each of the first period P1 and the second period P2. That is, the imaging device 33 captures an image of the specimen illuminated with the first illumination light in the first period P1 to generate an imaging signal (hereinafter referred to as the first imaging signal S1), and the second period P2 The specimen illuminated with the illumination light is imaged to generate an imaging signal (hereinafter referred to as a second imaging signal S2).

  Here, since the wavelength bands of the green light LG and the violet light LV included in the first illumination light are separated from each other, the imaging element 33 performs imaging with good color separation. Similarly, the blue light LB and the red light LR included in the second illumination light are separated from each other in wavelength, so that the imaging element 33 captures an image with good color separation.

  The DSP 41 generates image data based on the G signal and B signal included in the first imaging signal S1 and the B signal and R signal included in the second imaging signal S2. The B signal included in the first imaging signal S1 is based on the purple light LV, and the B signal included in the second imaging signal S2 is based on the blue light LB. When generating image data, the B signal is obtained by adding the B signal included in the first imaging signal S1 and the B signal included in the second imaging signal S2 for each identical pixel. Then, image data is generated by performing the above-described signal processing using the B signal, the G signal, and the R signal.

  As shown in FIG. 12, the DSP 41 uses the obtained imaging signal and the imaging signal obtained immediately before the first imaging signal S1 or the second imaging signal S2 from the imaging device 33, respectively. Image data for one frame is generated. That is, the image data is updated every half time (T / 2) of the rotation period T. This updated period (T / 2) is the above-described one frame period.

  Thus, the observation image based on the image data obtained from the first and second imaging signals S1 and S2 is a full-color image. In addition to this observation image, an observation image may be generated only from the first imaging signal S1. Since the first imaging signal S1 is a signal based on the green light LG and the purple light LV, the observation image based on the first imaging signal S1 is a pseudo color image in which the surface blood vessels and the like are emphasized.

  Next, the operation of the endoscope system 10 will be described. When performing an endoscopic diagnosis, the endoscope 11 is connected to the processor device 12 and the light source device 13, and the processor device 12 and the light source device 13 are powered on. Then, the insertion portion 16 of the endoscope 11 is inserted into the subject's digestive tract, and observation in the digestive tract is started. An instruction to start observation is given by the operation input unit 15.

  When the observation is started, the wheel plate 60 of the rotating phosphor 50 is rotated at the rotation period T, and the V-LD 53 is driven to emit the excitation light LE. The excitation light LE enters the first DM 55a through the first optical path R1, and is reflected by the first DM 55a. The excitation light LE reflected by the first DM 55a is irradiated to the phosphor layer 61 of the wheel plate 60 through a second optical path R2 different from the first optical path R1. As the wheel plate 60 rotates, the first region 61a and the second region 61b alternately pass through the irradiation position 64 of the excitation light LE. Green light LG is emitted during the first period P1 when the first region 61a passes the irradiation position 64, and blue light LB is emitted during the second period P2 when the second region 61b passes the irradiation position 64.

  In the first period P1, green light LG is emitted from the rotating phosphor 50 toward the first DM 55a. The green light LG enters the first DM 55a through the second optical path R2, passes through the first DM 55a, and passes through the first DM 55a. The light is emitted to a third optical path R3 different from the first optical path R1. In the first period P1, the V-LED 57a is driven to emit purple light LV and reflected by the first DM 55a. Thereby, the green light LG and the purple light LV are combined and enter the notch filter 59, and the notch filter 59 reduces the light intensity in the wavelength band of 460 nm to 500 nm from the green light LG. The green light LG and violet light LV that have passed through the notch filter 59 pass through the second DM 55b and are supplied to the light guide 32 as first illumination light.

  In the second period P2, blue light LB is emitted from the rotating phosphor 50 toward the first DM 55a. The blue light LB enters the first DM 55a through the second optical path R2, passes through the first DM 55a, and passes through the third DM 55a. It is emitted to the optical path R3. The blue light LB emitted to the third optical path R3 enters the notch filter 59, and the notch filter 59 reduces the light intensity in the wavelength band of 460 nm to 500 nm. The blue light LB that has passed through the notch filter 59 passes through the second DM 55b. In the second period P2, the R-LED 57b is driven to emit red light LR and reflected by the second DM 55b. Thereby, the blue light LB and the red light LR are combined and supplied to the light guide 32 as the second illumination light.

  In the endoscope 11, the first illumination light and the second illumination light are alternately guided to the illumination window 22 through the light guide 32, and irradiated from the illumination window 22 to the observation site. The reflected light from the observation site enters the image sensor 33 from the observation window 23 via the objective optical system 37. The image sensor 33 captures (photoelectrically converts) incident light every frame period (half of the rotation period T) to generate an image signal. Specifically, the first imaging signal S1 is generated by imaging in the first period P1, and the second imaging signal S2 is generated by imaging in the second period P2. The first and second imaging signals S1 and S2 are each subjected to processing such as CDS, AGC, and A / D conversion by the AFE 35, and are input to the DSP 41 of the processor device 12 as digital signals.

  In the DSP 41, signal processing such as pixel interpolation processing, gamma correction, and white balance correction is performed on the first and second imaging signals S1 and S2 input from the endoscope 11, and is stored in the frame memory 42 as image data. Remembered. At this time, the image data is generated based on the G and B signals included in the first imaging signal S1 and the B and R signals included in the second imaging signal S2. As shown in FIG. 12, the generation of the image data is performed every time one of the first and second imaging signals S1 and S2 is input.

  The image data stored in the frame memory 42 is subjected to predetermined image processing by the image processing unit 43 to become an observation image, and is displayed on the monitor 14 via the display control unit 44. The observation image displayed on the monitor 14 is updated every frame period.

  This observation image is a wavelength band of 460 nm to 500 nm that is reflected or scattered from white illumination light consisting of violet light LV, blue light LB, green light LG, and red light LR with almost no absorption by blood hemoglobin. Since this corresponds to an image obtained by imaging a specimen using illumination light with reduced light intensity, the image has high color reproducibility, is bright, and has high blood vessel contrast.

  Further, since the green light LG and the blue light LB are generated by the phosphor and both have high luminance, the light intensity of the blue light is reduced by reducing the light intensity in the wavelength band of 460 nm to 500 nm. The influence is small, and the balance of the intensity of the green light LG and the blue light LB is maintained.

  In the above-described embodiment, the notch filter 59 is disposed on the third optical path R3 between the first DM 55a and the second DM 55b, but at any position as long as it is on the optical path of the green light LG and the blue light LB. It may be arranged. For example, the second DM 55b may be disposed on the third optical path R3 on the emission side (opposite to the first DM 55a), and the notch filter 59 may be disposed on the second optical path R2 between the rotating phosphor 50 and the first DM 55a. You may arrange in.

  When the notch filter 59 is provided on the emission side of the second DM 55b, as shown in FIG. 13, in addition to the first notch characteristic for reducing the light intensity in the wavelength band of 460 nm to 500 nm, 560 nm to 590 nm (560 nm to 590 nm). The following notch filter 59 is preferably provided with a second notch characteristic that reduces the light intensity in the wavelength band (below). Due to the second notch characteristic, the green light LG and the red light LR are partially attenuated, and the wavelength bands of the green light LG and the red light LR are obtained by the conventional xenon light source and the wavelength selection filter. It is preferable in terms of affinity with conventional equipment. The light attenuation rate of the second notch characteristic may be different from the light attenuation rate (light transmittance α) of the first notch characteristic. Further, the wavelength band of the second notch characteristic is not limited to 560 nm to 590 nm, and may be wider than 550 nm to 600 nm.

  Further, the first DM 55a or the second DM 55b may have the notch characteristic shown in FIG. 9, and the notch filter 59 may be omitted. Thereby, there exists an advantage that the light source part 30 reduces in size. FIG. 14 shows optical characteristics when the first DM 55a is provided with notch characteristics for reducing the light intensity in the wavelength band of 460 nm to 500 nm. FIG. 15 shows optical characteristics when the second DM 55b is provided with notch characteristics for reducing the light intensity in the wavelength band of 460 nm to 500 nm.

  In the above embodiment, the first DM 55a transmits light having a wavelength of the threshold value λ1 or more and reflects light having a wavelength smaller than the threshold value λ1, but conversely, reflects light having a wavelength of the threshold value λ1 or more. Alternatively, light having a wavelength smaller than the threshold λ1 may be transmitted. In this case, the rotating phosphor 50, the V-LD 53, and the V-LED 57a are arranged as shown in FIG. 16 with respect to the first DM 55a, and the optical path of the purple light LV that transmits the first DM 55a is changed by the first DM 55a. It is integrated into the optical path (third optical path R3) of the green light LG and blue light LB reflected by the 1DM 55a.

  In the above embodiment, the second DM 55b reflects light having a wavelength greater than or equal to the threshold λ2 and transmits light having a wavelength smaller than the threshold λ2, but conversely transmits light having a wavelength greater than or equal to the threshold λ2. Alternatively, light having a wavelength smaller than the threshold λ2 may be reflected. In this case, the optical path of the red light LR transmitted through the second DM 55b is integrated with the optical path of the green light LG, blue light LB, and violet light LV (third optical path R3) reflected by the second DM 55b by the second DM 55b.

  Therefore, each of the first DM 55a and the second DM 55b can generate one of reflection and transmission for light having a wavelength equal to or greater than the threshold, and can generate the other of reflection and transmission for light having a wavelength shorter than the threshold. Therefore, as shown in Table 1, the combination of the optical characteristics (reflection or transmission) of the first DM 55a and the second DM 55b can be four patterns including the above embodiment. The configuration shown in FIG. 5 corresponds to the first pattern, and the configuration shown in FIG. 16 corresponds to the second pattern.

  In the above embodiment, as shown in FIG. 11, the imaging cycle of the imaging device 33 is half of the rotation cycle T, and the imaging operation is performed individually in the first period P1 and the second period P2. The imaging cycle of 33 may coincide with the rotation cycle T, and one imaging operation may be performed at one rotation cycle T. In this case, since the sample image illuminated with the first illumination light and the sample image illuminated with the second illumination light are mixed and imaged, the color separation of imaging is reduced as compared with the above embodiment. However, signal processing for generating image data by the DSP 41 is simplified.

  In this case, the V-LED 57a and the R-LED 57b may be constantly driven so that the purple light LV and the red light LR are always lit. Further, the imaging cycle of the image sensor 33 may be made to be an integral multiple of the rotation cycle T. Furthermore, when the rotation period T is sufficiently small with respect to the imaging period, the imaging period may not coincide with an integer multiple of the rotation period T, and the imaging of the imaging element 33 and the rotation of the rotating phosphor 50 may be asynchronous. .

  In the above embodiment, the emission intensity of the excitation light LE by the V-LD 53 is constant, but it is also preferable to change the emission intensity of the excitation light LE between the first period P1 and the second period P2. Since the emission intensity of the green light LG and the blue light LB changes according to the emission intensity of the excitation light LE, by changing the emission intensity of the excitation light LE between the first period P1 and the second period P2, The light quantity ratio between the green light LG and the blue light LB can be changed.

  The light quantity ratio between the green light LG and the blue light LB is preferably changed between the distant view observation and the near view observation. The distant view observation is to observe the distal end portion 19 of the endoscope 11 at a position away from the specimen, and mainly to observe the entire state of the observed site including the positional relationship between the surface blood vessels and the middle-deep blood vessels. It is the purpose. On the other hand, near-field observation is observation at a position where the distal end portion 19 of the endoscope 11 is close to the specimen, and intensive observation of superficial blood vessels where lesions due to early cancer or the like are likely to appear. This is the main purpose.

At the time of distant view observation, since the brightness of the observation image is lower than that at the time of close view observation, it is preferable to increase the light amount ratio _{RG / B} of the green light LG to the light amount of the blue light LB. This is because green light LG has a lower hemoglobin absorption coefficient and scattering coefficient in living tissue than blue light LB, so that it diffuses deeper and wider in living tissue and efficiently illuminates mucous membranes and the like. by.

The change of the light amount ratio _{RG / B} may be performed based on an input signal from the operation input unit 15, for example. Specifically, the distant view observation mode and the foreground observation mode can be set by the operation input unit 15, and when the distant view observation mode is set, the light amount ratio _{RG / B} is made larger than that in the foreground observation mode. . Instead, the exposure amount may be obtained based on the imaging signal acquired by the imaging element 33, and the light amount ratio _{RG / B} may be controlled based on the exposure amount. Specifically, when the exposure amount is equal to or less than a certain value, it is determined that the subject is in a distant view observation state, and when the exposure amount is greater than a certain value, it is determined that the subject is in a near view observation state.

  In the above embodiment, an observation image (hereinafter referred to as a normal observation image) is generated using white illumination light composed of purple light LV, blue light LB, green light LG, and red light LR. An observation image (hereinafter, referred to as a special observation image) may be generated using illumination light (special light) composed of purple light LV, blue light LB, and green light LG excluding the light LR.

  A normal observation mode and a special observation mode are provided, and in the special observation mode, the R-LED 57b may not be driven, and the red light LR may not be emitted. In the special observation mode, a special observation image is generated using only the B signal and the G signal. The special observation image is displayed on the monitor 14 by, for example, assigning the B signal to the B channel and the G channel of the monitor 14 and assigning the G signal to the R channel of the monitor 14.

  In the above embodiment, a single-plate color image sensor (hereinafter referred to as a color sensor) is used as the image sensor 33, but a monochrome image sensor (hereinafter referred to as a monochrome sensor) having no color filter array is used. It is also possible to use it.

  In the normal observation mode, the emission timing of the purple light LV and the red light LR with respect to the first period P1 and the second period P2 can have three patterns shown in Table 2. The first pattern is a driving method in which the purple light LV is emitted in the first period P1 and the red light LR is emitted in the second period P2, and is the same as in the above embodiment. In contrast to the first pattern, the second pattern is a driving method in which red light LR is emitted in the first period P1, and purple light LV is emitted in the second period P2. The third pattern is a driving method in which violet light LV and red light LR are emitted during both the first period P1 and the second period P2.

  In this normal observation mode, the color sensor can be used in the first to third patterns. However, in any of the first to third patterns, a monochrome sensor cannot be used because light of different wavelength bands is mixed in each period.

  In the special observation mode, three patterns shown in Table 3 can be considered as the emission timings of the purple light LV and the red light LR for the first period P1 and the second period P2. The first pattern is a driving method in which purple light LV is emitted in the first period P1. In contrast to the first pattern, the second pattern is a driving method in which purple light LV is emitted in the second period P2. The third pattern is a driving method in which purple light LV is emitted during both the first period P1 and the second period P2.

  In this special observation mode, the color sensor can be used in the first to third patterns. Among the first to third patterns, in the second pattern, green light LG is emitted in the first period P1, and blue light LB and violet light LV are emitted in the second period P2. Since both the blue light LB and the purple light LV are light related to the B signal in the observation image, there is no problem even if an image is taken without color separation by the monochrome sensor. For this reason, the monochrome sensor can be used only in the second pattern.

  Moreover, in the said embodiment, although red light LR is produced | generated by R-LED57b, another structure can be considered for production | generation of red light LR. In the following, other embodiments relating to the generation of the red light LR are shown.

[Second Embodiment]
In the second embodiment, excitation light LE is added to the first region 61a in the phosphor layer 61 in addition to a phosphor material (β-SiAlON or the like) that emits green light LG (first fluorescence) upon receiving excitation light LE. In response, a phosphor material (for example, CASN (CaAlSiN ₃ : Eu ²⁺ )) that emits red light LR (third fluorescence) is contained, and from the configuration of the light source unit 30 shown in FIG. 56d and the second DM 55b are deleted.

  In the present embodiment, yellow light in which green light LG and red light LR are mixed is emitted from the first region 61a. Other configurations are the same as those in the above embodiment, but in this embodiment, since the green light LG and the red light LR are mixed, a monochrome sensor cannot be used as the image sensor 33.

[Third Embodiment]
In the third embodiment, as shown in FIG. 17, a phosphor layer 70 is provided in the recess 62 of the wheel plate 60 in place of the phosphor layer 61 of the first embodiment. The phosphor layer 70 includes a first region 70a that emits green light LG (first fluorescence), a second region 70b that emits blue light LB (second fluorescence), and a first region that emits red light LR (third fluorescence). 3 regions 70c. The third region 70c is a region in which, for example, CASN (CaAlSiN ₃ : Eu ²⁺ ) is dispersed as a phosphor material in a binder (not shown). In the present embodiment, the R-LED 57b, the fourth lens 56d, and the second DM 55b are deleted from the configuration of the light source unit 30 shown in FIG.

  In the present embodiment, as the wheel plate 60 rotates, the first region 70a, the second region 70b, and the third region 70c sequentially pass through the irradiation position 64 of the excitation light LE, and the green light LG, blue light LB, red Light LR is emitted in order.

  In the present embodiment, either a color sensor or a monochrome sensor can be used as the image sensor 33. When a monochrome sensor is used as the imaging element 33, imaging may be performed in accordance with each light emission period of the green light LG, the blue light LB, and the red light LR. In this case, it is preferable to drive the V-LED 57a to emit the purple light LV during the light emission period of the blue light LB (second period P2). Other configurations are the same as those in the above embodiment.

[Fourth Embodiment]
In the fourth embodiment, as shown in FIG. 18, a phosphor layer 80 is provided in the recess 62 of the wheel plate 60 in place of the phosphor layer 61 of the first embodiment. The phosphor layer 80 includes a first phosphor material 80a that emits green light LG (first fluorescence), a second phosphor material 80b that emits blue light LB (second fluorescence), and a red light LR (third fluorescence). ) And a binder 80d in which the first to third phosphor materials 80a to 80c are dispersed. In the present embodiment, the R-LED 57b, the fourth lens 56d, and the second DM 55b are deleted from the configuration of the light source unit 30 shown in FIG.

  In the present embodiment, the phosphor layer 80 emits light (white light) in which the green light LG, the blue light LB, and the red light LR are mixed by irradiating the phosphor layer 80 with the excitation light LE. For this reason, a color sensor is used as the image sensor 33, and a monochrome sensor cannot be used. In the present embodiment, while the wheel plate 60 is rotating, the V-LED 57a is driven to emit the purple light LV constantly. Other configurations are the same as those in the above embodiment.

  In each of the above embodiments, the V-LED 57a is provided to generate the purple light LV. However, the purple light LV is not essential for the present invention, and the V-LED 57a and the light source unit 30 shown in FIG. The third lens 56c may be deleted.

  In each of the above embodiments, the peak wavelength of the blue light LB is about 460 nm and the peak wavelength of the green light LG is about 540 nm. However, the peak wavelength of the blue light LB may be 460 nm or less, and the peak wavelength of the green light LG is What is necessary is just 500 nm or more.

  In each of the embodiments described above, the color sensor is provided with the primary color filter array 38, but a complementary color filter array may be provided instead.

  In each of the above-described embodiments, the light source device and the processor device are configured separately, but may be configured by one device including the light source device and the processor device.

  The first optical member and the second optical member described in the claims correspond to the first DM 55a and the second DM 55b in the above embodiments, respectively.

  In the configuration according to claim 1, the first optical member (first DM 55a) reflects the excitation light and transmits the first fluorescence and the second fluorescence (green light and blue light). And the second configuration (see FIG. 16) that transmits the excitation light and reflects the first fluorescence and the second fluorescence. Hereinafter, the first and second configurations will be described as additional items 1 and 2, respectively.

[Additional Item 1]
An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A first dichroic mirror that reflects the excitation light emitted from the excitation light source, irradiates the rotating phosphor, and transmits the first fluorescence and the second fluorescence emitted from the rotating phosphor and emits them; ,
A notch filter that is provided on the optical path of the first fluorescence and the second fluorescence, and reduces the light intensity in the wavelength band of 460 nm or more and 500 nm or less from the first fluorescence and the second fluorescence;
An endoscope light source device comprising:

[Additional Item 2]
An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A first dichroic mirror that transmits the excitation light emitted from the excitation light source, irradiates the rotating phosphor, and reflects and emits the first fluorescence and the second fluorescence emitted from the rotating phosphor; ,
A notch filter that is provided on the optical path of the first fluorescence and the second fluorescence, and reduces the light intensity in the wavelength band of 460 nm or more and 500 nm or less from the first fluorescence and the second fluorescence;
An endoscope light source device comprising:

  Furthermore, the structure of the said 4th Embodiment is described as additional item 3 below.

[Additional Item 3]
An excitation light source that emits excitation light;
A first phosphor material that emits green first fluorescence upon irradiation with the excitation light, a second phosphor material that emits blue second fluorescence upon irradiation with the excitation light, and a red third material upon irradiation with the excitation light. A rotating phosphor having a phosphor layer in which a third phosphor material emitting fluorescence is dispersed;
The excitation light incident from the excitation light source via the first optical path is emitted toward the rotating phosphor toward a second optical path different from the first optical path, and is incident from the rotating phosphor via the second optical path. A first optical member that emits the first to third fluorescence into a third optical path different from the first optical path;
A notch filter provided on the second optical path or the third optical path, for reducing light intensity in a wavelength band of 460 nm or more and 500 nm or less from the first to third fluorescence;
An endoscope light source device comprising:

DESCRIPTION OF SYMBOLS 10 Endoscope system 11 Endoscope 12 Processor apparatus 13 Light source apparatus 30 Light source part 31 Light source control part 32 Light guide 32a Incident end 33 Image sensor 38 Color filter array 50 Rotating fluorescent substance 55a 1st DM
55b 2nd DM
59 notch filter 60 wheel plate 61 phosphor layer 61a, 61b first and second region 64 irradiation position 70 phosphor layer 70a-70c first to third region 80 phosphor layer 80a-80c first to third phosphor material 80d binder

Claims (11)

An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A purple light source that emits purple light;
The excitation light incident from the excitation light source via the first optical path is reflected on one surface and emitted to the second optical path toward the rotating phosphor, and is incident from the rotating phosphor via the second optical path. 1 fluorescence and the 2nd fluorescence are permeate | transmitted from said one surface, and inject | emitted on the 3rd optical path, The said violet light which injects via the 4th optical path from the said violet light source is reflected by the other surface, and said 3rd optical path A first dichroic mirror ejected on
A notch filter provided on the second optical path or the third optical path, for reducing light intensity in a wavelength band from 460 nm to 500 nm from the first fluorescence and the second fluorescence;
An endoscope light source device comprising: An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A purple light source that emits purple light;
The excitation light incident from the excitation light source via the first optical path is transmitted from one surface, is emitted to the second optical path toward the rotating phosphor, and is incident from the rotating phosphor via the second optical path. The first fluorescent light and the second fluorescent light are reflected by the other surface and emitted to the third optical path, and the violet light incident through the fourth optical path from the violet light source is transmitted from the one surface, and the third optical path is transmitted. A first dichroic mirror ejected on
A notch filter provided on the second optical path or the third optical path, for reducing light intensity in a wavelength band from 460 nm to 500 nm from the first fluorescence and the second fluorescence;
An endoscope light source device comprising: The excitation light and the peak wavelength of the second fluorescent is at 460nm or less, an endoscope light source device according to claim 1 or 2 peak wavelength of the first fluorescent is characterized in that at 500nm or more. A red light source that emits red light;
The light source for endoscopes according to any one of claims 1 to 3 , further comprising: a second dichroic mirror that integrates an optical path of red light emitted from the red light source into the third optical path. apparatus.   The violet light source emits the violet light during a first period in which the first region passes through the excitation light irradiation position, and the red light source transmits the red light source through the excitation light irradiation position. The endoscope light source device according to claim 4, wherein the red light is emitted during the second period. The first region includes a phosphor material that emits red third fluorescence when irradiated with the excitation light, and emits yellow light in which the first fluorescence and the third fluorescence are mixed. The light source device for endoscopes according to 1 or 2 . The rotating phosphor has a third region that emits red third fluorescence when irradiated with the excitation light,
Wherein with the rotation first region, the second region, an endoscope light source device according to claim 1 or 2, wherein the third region is characterized by passing the irradiation position of the excitation light.   8. The endoscope light source device according to claim 7, wherein the violet light source emits the violet light in a second period in which the second region passes through the excitation light irradiation position.   The excitation light source includes a first period in which the first region passes through the excitation light irradiation position and a second period in which the second region passes through the excitation light irradiation position. The light source device for an endoscope according to any one of claims 1 to 8, wherein the light emission intensity is changed. An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A purple light source that emits purple light;
The excitation light incident from the excitation light source via the first optical path is reflected on one surface and emitted to the second optical path toward the rotating phosphor, and is incident from the rotating phosphor via the second optical path. 1 fluorescence and the 2nd fluorescence are permeate | transmitted from the said one surface, and inject | emitted to the 3rd optical path, The said violet light incident through the 4th optical path from the said violet light source is reflected by the other surface, and the said 3rd optical path A first dichroic mirror ejected on
A light source device comprising: a notch filter provided on the second optical path or the third optical path for reducing light intensity in a wavelength band of 460 nm to 500 nm from the first fluorescence and the second fluorescence;
An endoscope having an image sensor that images reflected light from an observation site irradiated with at least one of the first fluorescence and the second fluorescence;
A control unit for controlling the light source device and the imaging element;
An endoscope system comprising: An excitation light source that emits excitation light;
A first region that emits green first fluorescence when irradiated with the excitation light; and a second region that emits blue second fluorescence when irradiated with the excitation light. A rotating phosphor in which two regions pass through the irradiation position of the excitation light;
A purple light source that emits purple light;
The excitation light incident from the excitation light source via the first optical path is transmitted from one surface, is emitted to the second optical path toward the rotating phosphor, and is incident from the rotating phosphor via the second optical path. The first fluorescent light and the second fluorescent light are reflected by the other surface and emitted to the third optical path, and the violet light incident through the fourth optical path from the violet light source is transmitted from the one surface, and the third optical path is transmitted. A first dichroic mirror ejected on
A light source device comprising: a notch filter provided on the second optical path or the third optical path for reducing light intensity in a wavelength band of 460 nm to 500 nm from the first fluorescence and the second fluorescence;
An endoscope having an image sensor that images reflected light from an observation site irradiated with at least one of the first fluorescence and the second fluorescence;
A control unit for controlling the light source device and the imaging element;
An endoscope system comprising:

Images