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WO2018037505A1 - Système d'endoscope - Google Patents

Système d'endoscope Download PDF

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Publication number
WO2018037505A1
WO2018037505A1 PCT/JP2016/074683 JP2016074683W WO2018037505A1 WO 2018037505 A1 WO2018037505 A1 WO 2018037505A1 JP 2016074683 W JP2016074683 W JP 2016074683W WO 2018037505 A1 WO2018037505 A1 WO 2018037505A1
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WO
WIPO (PCT)
Prior art keywords
light
special
emission
image data
reference light
Prior art date
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Ceased
Application number
PCT/JP2016/074683
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English (en)
Japanese (ja)
Inventor
佳宏 林
友輝 池田
祐哉 増川
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Hoya Corp
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Hoya Corp
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Priority to PCT/JP2016/074683 priority Critical patent/WO2018037505A1/fr
Publication of WO2018037505A1 publication Critical patent/WO2018037505A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0655—Control therefor

Definitions

  • the present invention relates to an endoscope system that calculates and acquires a feature amount in a living tissue based on image data generated by imaging the living tissue.
  • An endoscope system having a function of obtaining, as a feature amount of a biological tissue, information on a biological substance in a biological tissue as a subject, for example, information on the amount of hemoglobin and oxygen saturation of hemoglobin, from image data obtained by the endoscope It has been known.
  • An example of such an endoscope system is described in Patent Document 1.
  • the endoscope system described in Patent Document 1 includes a light source device on which a rotary filter is mounted.
  • the rotary filter includes three optical bandpass filters (two optical bandpass filters that selectively transmit light in the 550 nm band and one optical bandpass filter that selectively transmits light in the 650 nm band) and white Normal observation filters that transmit light are arranged side by side in the circumferential direction.
  • the controller rotationally drives the rotary filter at a constant rotation period, sequentially inserts each filter into the white light optical path, and sequentially performs imaging of the living tissue with the irradiation light transmitted through each filter.
  • the controller generates a distribution image indicating the distribution of biomolecules in the biological tissue, for example, an oxygen saturation distribution image indicating the oxygen saturation distribution of hemoglobin, based on the image data captured using each optical bandpass filter.
  • the generated distribution image is displayed in the display screen side by side with the normal observation image captured using the normal observation filter.
  • the present invention has been made in view of the above circumstances, and is a distribution of feature amounts such as the amount of hemoglobin and oxygen saturation of biological tissue generated from captured image data of biological tissue illuminated with a plurality of lights.
  • feature amounts such as the amount of hemoglobin and oxygen saturation of biological tissue generated from captured image data of biological tissue illuminated with a plurality of lights.
  • the endoscope system of the present invention includes the following forms.
  • a light source device configured to repeat Color image data of the image of the biological tissue illuminated with the illumination light is obtained by imaging the biological tissue in accordance with the timing of emission of the illumination light each time the biological tissue is illuminated with each of the illumination light.
  • An endoscope comprising an imaging device configured to generate;
  • a processor comprising a feature amount acquisition unit configured to calculate the amount of hemoglobin in the living tissue and the oxygen saturation level of hemoglobin in the living tissue as the feature amount of the living tissue using the color image data;
  • An image of the biological tissue illuminated with the reference light and imaged by the imaging device, and a feature amount distribution image showing at least one distribution of the amount of the hemoglobin and the oxygen saturation are displayed.
  • the feature amount acquisition unit includes a component of the first special light color image data obtained by illumination of the first special light and the reference light color image data obtained by illumination of the reference light among the color image data.
  • a hemoglobin amount calculating unit configured to calculate the amount of the hemoglobin using a component, the component of the first special light color image data obtained by the illumination of the first special light, and the illumination of the second special light
  • An oxygen saturation calculator configured to calculate the oxygen saturation of the hemoglobin using the component of the second special light color image data obtained by
  • the light source device emits the reference light at least twice between one emission of the special light and another emission of the special light in the one cycle with respect to the order of the illumination light.
  • An endoscope system configured to perform the emission of reference light without continuing.
  • the light source device comprises a light source configured to emit a single light;
  • the light source device transmits the reference light and the special light by transmitting the light emitted from the light source through a plurality of optical filters having different pass wavelength bands so as to correspond to the order of emission of the reference light and the special light.
  • the endoscope system according to any one of Embodiments 1 to 3, wherein the endoscope system is configured to emit light.
  • the wavelength band of the reference light is wider than the wavelength band of the special light
  • the wavelength band of the reference light includes a wavelength band in which one of the components of the reference light color image data does not have sensitivity to a change in the amount of hemoglobin in the living tissue.
  • one of the components of the first special light color image data is sensitive to changes in the amount of hemoglobin in the living tissue, but sensitive to changes in the oxygen saturation.
  • the wavelength band of the second special light includes any one of modes 1 to 6, wherein one of the components of the second special light color image data includes a wavelength band having sensitivity to the change in oxygen saturation.
  • the endoscope system according to one.
  • the first special light is an optical filter that is filtered light of the reference light that transmits a first wavelength band within a range of 500 nm to 600 nm of the wavelength band of the reference light
  • the second special light is: The optical filter according to any one of Embodiments 1 to 7, wherein the reference light is a filtered light of the reference light that has been transmitted through a second wavelength band narrower than the first wavelength band within the first wavelength band. Endoscopic system.
  • the hemoglobin amount calculating unit is configured to calculate the amount of the hemoglobin based on a first ratio that is a ratio of the component of the reference light color image data and the component of the first special light color image data,
  • the oxygen saturation calculating unit calculates oxygen saturation of the hemoglobin based on a second ratio that is a ratio between the component of the first special light color image data and the component of the second special light color image data.
  • the reference light includes a first reference light and a second reference light having the same wavelength band
  • the light source device may be arranged between the emission of the first special light and the emission of the second special light, or between the emission of the second special light and the emission of the first special light with respect to the order of emission of the illumination light.
  • the first reference light is emitted and the first special light and the second reference light are emitted, or the second reference light and the first special light are emitted.
  • the feature amount acquisition unit calculates first feature color image data of an image of the biological tissue illuminated with the first reference light and the biological tissue illuminated with the second reference light for calculating the feature amount.
  • the endoscope system according to any one of Embodiments 1 to 11, further comprising a data selection unit configured to select and use any one of the second reference light color image data of the image.
  • the feature amount acquisition unit illuminates with the first reference light and illuminates with the second reference light with respect to the image of the biological tissue captured by the imaging element, and a positional deviation amount of the image of the biological tissue captured by the imaging element
  • a misregistration amount calculation unit configured to calculate
  • the data selection unit may use the first reference light color image data for calculating the feature amount instead of the second reference light color image data when the calculated positional deviation amount is out of an allowable range.
  • the endoscope system according to form 12, which is configured.
  • the endoscope has any one of forms 1 to 13, wherein the imaging device includes an optical system configured to receive reflected light of the living tissue in a wavelength band of the reference light and the special light. Endoscope system according to one.
  • the light source device includes: a light source configured to emit one light; and a plurality of light beams emitted from the light source having different pass wavelength bands so as to correspond to an order of emission of the reference light and the special light.
  • a rotary filter configured to emit the reference light and the special light by transmitting the optical filter, the optical filter being arranged on the circumference with an interval; and
  • the image sensor is a CMOS image sensor that exposes the light receiving surface with a rolling shutter;
  • the endoscope system according to any one of Embodiments 1 to 15, wherein the rotary filter has a blocking section that blocks light between the optical filters.
  • the light source device is configured to repeat emission of a plurality of cycles, with the emission of the reference light and the special light as one cycle.
  • the number of times that the image pickup device generates the reference light color image data in the one cycle is the number of times the image pickup device generates the first special light color image data and the image pickup device generates the second special light color image data.
  • the endoscope system according to any one of Embodiments 1 to 16, wherein the endoscope system is larger than the number of times of generating.
  • a biological tissue can be observed without stress for an operator who performs a procedure while operating the endoscope, and a focused position in a feature amount distribution image of the biological tissue with high accuracy is normally observed. It can be specified on the image of the living tissue in the image.
  • the endoscope system includes a light source device, an endoscope including an imaging element, a processor, and a display.
  • the light source device emits a plurality of special lights including reference light having different wavelength bands and at least first special light and second special light as one cycle, and uses the reference light and special light as illumination light for living tissue in one cycle. repeat.
  • the reference light and the plurality of special lights having different wavelength bands are different from each other in the wavelength band of the reference light and the plurality of special lights, and the wavelength bands of the plurality of special lights.
  • the imaging device picks up the image of the living tissue illuminated with each illumination light by imaging the living tissue with the timing of emitting the illumination light. Generate image data. Using this color image data, the processor calculates the amount of hemoglobin in the living tissue and the oxygen saturation of the hemoglobin in the living tissue.
  • the display connected to the processor displays an image of the biological tissue illuminated with the reference light, and a feature amount distribution image showing at least one distribution of the amount of hemoglobin and oxygen saturation.
  • the processor includes a component of the first special light color image data obtained by the illumination of the first special light and the reference light color image data obtained by the illumination of the reference light among the color image data. Of the first special light color image data obtained by illumination of the first special light and the second special light color image data obtained by illumination of the second special light.
  • the oxygen saturation of hemoglobin is calculated using the components.
  • the light source device is arranged between one emission of special light and another emission of special light with respect to the order of emission of illumination light in one cycle of emission of reference light and a plurality of special lights.
  • the reference light is emitted at least twice without continuing the emission of the reference light.
  • the emission of the reference light is not continued at least twice in the sequence of the special light emission order determined to emit the special light sequentially. It is the order of arrangement. In this way, normal observation obtained by imaging a biological tissue illuminated with the feature amount distribution image obtained in each cycle and the reference light by repeatedly emitting one cycle with a plurality of special light and reference light being emitted as one cycle.
  • the normal observation image is obtained by illuminating the living tissue with the reference light at least twice in one cycle. Therefore, the conventional observation image obtained only once in one cycle can be obtained. Compared to the endoscope system, the refresh rate of the normal observation image can be improved. In addition, since the refresh rate of the normal observation image is improved, the living tissue can be observed without stress for an operator who performs the procedure while operating the endoscope.
  • the refresh rate of the normal observation image is improved, the positional deviation between the image of the biological tissue in the feature distribution image obtained from the captured image of the biological tissue illuminated with special light and the image of the biological tissue in the normal observation image As a result, the operator who performs the procedure while operating the endoscope can easily specify the position of interest in the feature amount distribution image on the image of the biological tissue in the normal observation image.
  • the endoscope system of the present embodiment will be described in detail with reference to the drawings.
  • FIG. 1 is a block diagram illustrating a configuration of an endoscope system 1 according to the present embodiment.
  • the endoscope system 1 includes an electronic endoscope (endoscope) 100, a processor 200, a display 300, and a light source device 400.
  • the electronic endoscope 100 and the display 300 are detachably connected to the processor 200.
  • the processor 200 includes an image processing unit 500.
  • the light source device 400 is detachably connected to the processor 200. Note that the light source device 400 may be provided in the housing of the processor 200.
  • the electronic endoscope 100 has an insertion tube 110 that is inserted into the body of a subject. Inside the insertion tube 110, a light guide 131 extending over substantially the entire length of the insertion tube 110 is provided.
  • the distal end portion 131 a that is one end portion of the light guide 131 is located in the distal end portion of the insertion tube 110, that is, in the vicinity of the distal end portion 111 of the insertion tube, and the proximal end portion 131 b that is the other end portion of the light guide 131 is connected to the light source device 400.
  • the light guide 131 extends from the connection portion with the light source device 400 to the vicinity of the insertion tube distal end portion 111.
  • the light source device 400 includes a light source lamp 430 that generates a large amount of light, such as a xenon lamp, as a light source.
  • the light emitted from the light source device 400 enters the base end portion 131b of the light guide 131 as illumination light IL.
  • the light incident on the base end portion 131b of the light guide 131 is guided to the tip end portion 131a through the light guide 131, and is emitted from the tip end portion 131a.
  • a light distribution lens 132 disposed opposite to the distal end portion 131 a of the light guide 131 is provided at the insertion tube distal end portion 111 of the electronic endoscope 100.
  • the illumination light IL emitted from the distal end portion 131a of the light guide 131 passes through the light distribution lens 132 and illuminates the living tissue T in the vicinity of the insertion tube distal end portion 111.
  • An objective lens group 121 and an image sensor 141 are provided at the insertion tube tip 111 of the electronic endoscope 100.
  • the objective lens group 121 and the imaging element 141 form an imaging unit.
  • the illumination light IL the light reflected or scattered by the surface of the living tissue T is incident on the objective lens group 121, is condensed, and forms an image on the light receiving surface of the image sensor 141.
  • the image sensor 141 a known image sensor such as a CCD (Charge-Coupled Device) image sensor or a CMOS (Complementary Metal-Oxide Semiconductor) image sensor having a color filter 141 a on the light receiving surface can be used. . Note that it is preferable to use a CMOS image sensor for the image sensor 141 in terms of low power consumption and low cost.
  • the color filter 141 a includes an R color filter that transmits red light, a G color filter that transmits green light, and a B color filter that transmits blue light, and is arranged on each light receiving element of the image sensor 141. It is a so-called on-chip filter formed directly.
  • FIG. 2 is a diagram illustrating an example of spectral characteristics of each of the red (R), green (G), and blue (B) filters of the image sensor used in the present embodiment.
  • the R color filter of the present embodiment is a filter that passes light having a wavelength longer than about 570 nm (for example, 580 nm to 700 nm)
  • the G color filter is a filter that passes light having a wavelength of about 470 nm to 620 nm.
  • the B color filter is a filter that allows light having a wavelength shorter than about 530 nm (for example, 420 nm to 520 nm) to pass therethrough.
  • the imaging element 141 is an imaging unit that images the living tissue T illuminated with each of a plurality of lights and generates color image data corresponding to each light, and the living tissue T with a plurality of lights having different wavelength ranges. It is an image data generation means for generating color image data corresponding to light reflected or scattered on the living tissue T by illuminating.
  • the image sensor 141 is controlled to be driven in synchronization with an image processing unit 500 described later, and periodically (for example, 1/30 second interval) color image data corresponding to the subject image formed on the light receiving surface. Output).
  • the color image data output from the image sensor 141 is sent to the image processing unit 500 of the processor 200 via the cable 142.
  • the image processing unit 500 mainly includes an A / D conversion circuit 502, a pre-image processing unit 504, a frame memory unit 506, a post image processing unit 508, a feature amount acquisition unit 510, a memory 512, an image display control unit 514, and a controller 516. Prepare for.
  • the A / D conversion circuit 502 performs A / D conversion on the color image data input from the image sensor 141 of the electronic endoscope 100 via the cable 142 and outputs digital image data. Digital data output from the A / D conversion circuit 502 is sent to the pre-image processing unit 504.
  • the pre-image processing unit 504 captures digital data by using the R digital image data captured by the light receiving element in the image sensor 141 with the R color filter and the light receiving element in the image sensor 141 with the G color filter.
  • the R, G, and B component color image data constituting the image by demosaic processing from the G digital image data and the B digital image data picked up by the light receiving element in the image pickup element 141 to which the B color filter is attached.
  • the pre-image processing unit 504 is a part that performs predetermined signal processing such as color correction, matrix calculation, and white balance correction on the generated color image data of R, G, and B components.
  • the frame memory unit 506 temporarily stores color image data for each image captured by the image sensor 141 and subjected to signal processing.
  • the post image processing unit 508 reads the color image data stored in the frame memory unit 506 or performs signal processing ( ⁇ correction or the like) on the image data generated by the image display control unit 514 (to be described later) for display display. Generate screen data.
  • the image data generated by the image display control unit 514 includes data of distribution images of feature amounts such as oxygen saturation of hemoglobin in the living tissue T.
  • the generated screen data (video format signal) is output to the display 300.
  • an image of the living tissue T, a feature amount distribution image indicating the distribution of the feature amount of the living tissue T, and the like are displayed on the display screen of the display 300.
  • the feature amount acquisition unit 510 calculates a feature amount of the imaged living tissue T, for example, the amount of hemoglobin, or the amount of hemoglobin and the oxygen saturation of hemoglobin, as will be described later.
  • the image data of the distribution image on the image of the captured tissue T of these feature amounts is generated. Since the feature quantity acquisition unit 510 calculates the feature quantity by calculating using the color image data of the living tissue T illuminated with a plurality of lights having different wavelength bands, the feature quantity acquisition unit 510 acquires the feature quantity from the frame memory unit 506 or the memory 512. Color image data and various information used in the unit 510 are called up.
  • the image display control unit 514 controls the display of the distribution image on the captured image of the biological tissue T of the feature amount calculated by the feature amount acquisition unit 510 in accordance with an instruction from the controller 516. For example, the image display control unit 514 displays the captured image of the living tissue T and the feature amount distribution image in parallel, or displays the feature amount distribution image so as to overlap the captured image of the living tissue T.
  • the controller 516 is a part that performs operation instruction and operation control of each part of the image processing unit 500, and performs operation instruction and operation control of each part of the electronic endoscope 100 including the light source device 400 and the imaging element 141.
  • the feature amount acquisition unit 510 and the image display control unit 514 may be configured by software modules that perform the above-described functions by starting and executing programs on a computer, or may be configured by hardware. Good.
  • the processor 200 instructs and controls the function of processing the color image data output from the image sensor 141 of the electronic endoscope 100 and the operation of the electronic endoscope 100, the light source device 400, and the display 300. Combines functionality.
  • the light source device 400 is a light emitting unit that emits reference light and special light as illumination light IL, and makes the reference light and special light enter the light guide 131.
  • the wavelength band of the reference light is different from the wavelength band of the plurality of special lights, and the wavelength bands of the plurality of special lights are different from each other.
  • the reference light includes first reference light and second reference light having the same wavelength band as described later, and the special light is different from the wavelength region of the reference light and has different wavelength bands from each other as described later. Includes special light and second special light.
  • the light source device 400 of the present embodiment emits four illumination lights IL, but may emit five or more illumination lights IL. In this case, the fifth light can be third special light different from the wavelength bands of the first special light and the second special light.
  • the light source device 400 includes a condenser lens 440, a rotation filter 410, a filter control unit 420, and a condenser lens 450.
  • the light that is substantially parallel light emitted from the light source lamp 430 is, for example, white light, is collected by the condenser lens 440, passes through the rotary filter 410, and is condensed again by the condenser lens 450.
  • the light enters the base end 131 b of the guide 131.
  • the rotary filter 410 is movable between a position on the optical path of light emitted from the light source 430 and a retracted position outside the optical path by a moving mechanism (not shown) such as a linear guide way.
  • the wavelength band of the illumination light IL emitted from the light source device 400 differs depending on the type of the rotary filter 410 that crosses the optical path of the light emitted from the light source lamp 430.
  • the special light is light that illuminates the biological tissue T in order to obtain color image data necessary for calculating the amount of hemoglobin in the biological tissue and the oxygen saturation of the hemoglobin
  • the wavelength band of the special light is Illumination light IL limited to a wavelength band having light absorption characteristics of hemoglobin.
  • the reference light is illumination light IL having a broad wavelength band, the wavelength band of which is not limited to the wavelength band having the light absorption characteristic of hemoglobin, and is white light in the present embodiment.
  • the configuration of the light source device 400 is not limited to that shown in FIG.
  • the light source lamp 430 may be a lamp that generates convergent light instead of parallel light.
  • a configuration may be adopted in which light emitted from the light source lamp 430 is collected before the condenser lens 440 and is incident on the condenser lens 440 as diffused light.
  • a configuration in which substantially parallel light generated by the light source lamp 430 is directly incident on the rotary filter 410 without using the condenser lens 440 may be employed.
  • a configuration in which a collimator lens is used instead of the condenser lens 440 and light is incident on the rotary filter 410 in a substantially parallel light state may be employed.
  • a collimator lens is used instead of the condenser lens 440 and light is incident on the rotary filter 410 in a substantially parallel light state.
  • an interference type optical filter such as a dielectric multilayer filter
  • the incident angle of the light to the optical filter is made uniform by causing substantially parallel light to enter the rotary filter 410.
  • a lamp that generates divergent light may be employed as the light source lamp 430.
  • the light source device 400 is configured to emit a plurality of lights having different wavelength bands by transmitting light emitted from one light source lamp 430 through an optical filter.
  • different wavelengths are used instead of the light source lamp 430.
  • a semiconductor light source such as a light emitting diode or a laser element that outputs laser light having different bands can be used as the light source of the light source device 400.
  • the rotation filter 410 may not be used.
  • the rotation filter 410 is a disc-shaped optical unit including a plurality of optical filters, and is configured such that the light passing wavelength region is switched according to the rotation angle.
  • the rotary filter 410 of the present embodiment includes four optical filters having different pass wavelength bands, but may include five, or six or more optical filters.
  • the rotation angle of the rotary filter 410 is controlled by a filter control unit 420 connected to the controller 516. When the controller 516 controls the rotation angle of the rotary filter 410 via the filter control unit 420, the wavelength band of the illumination light IL that passes through the rotary filter 410 and is supplied to the light guide 131 is switched.
  • FIG. 3 is an external view (front view) of the rotary filter 410.
  • the rotary filter 410 includes a total of four optical filters: a substantially disk-shaped frame 411, two optical filters Fn1, Fn2, one optical filter Fs1, and one optical filter Fs2.
  • the four optical filters are provided at intervals on the circumference.
  • the optical filters of the present embodiment are all dielectric multilayer filters, but other types of optical filters (for example, absorption optical filters and etalon filters using dielectric multilayer films as reflective films). May be used.
  • CMOS image sensor for the imaging element 141 of the electronic endoscope 100 from the viewpoint of low power consumption and low cost.
  • the CMOS image sensor is a rolling that repeats exposure and blocking of the light receiving surface. Since the image is taken by the shutter, it is preferable that the rotary filter 410 is rotated in accordance with the timing of the image pickup. However, the timing of exposure and the timing of emission of the illumination light IL may not match due to fluctuations in the rotation of the rotary filter 410, and the type of illumination light IL may change during exposure. For this reason, it is preferable that a blocking section where the illumination light IL is not emitted is provided between the optical filters on the frame 411 of the rotary filter 410.
  • the CMOS image sensor tends to generate a darker image than the CCD image sensor, it is necessary to lengthen the exposure time. It is preferable to increase the emission continuation time.
  • the wavelength bands of the optical filters Fs1 and Fs2 are narrower than the wavelength bands of the optical filters Fn1 and Fn2, as described later, the intensity of light transmitted through the optical filters Fs1 and Fs2 is weak, and the image is picked up by the image sensor 141. Images tend to be dark. For this reason, the accuracy of the feature quantity distribution image obtained using the color image data obtained from the light transmitted through the optical filters Fs1 and Fs2 tends to be low.
  • the ratio of the length along the circumference (circumferential direction) of each region of the cutoff section between the optical filters in the rotary filter 410 to the length along the circumference (circumferential direction) of each region of the optical filter is 0. It is preferably from super to 1, more preferably from 0.1 to 1.
  • a boss hole 412 is formed on the central axis of the frame 411.
  • An output shaft of a servo motor (not shown) provided in the filter control unit 420 is inserted into the boss hole 412 and fixed, and the rotary filter 410 rotates together with the output shaft of the servo motor.
  • the optical filter on which this light is incident is switched in the order of the optical filter Fs2, the optical filter Fn1, the optical filter Fs1, and the optical filter Fn2, thereby rotating the rotary filter.
  • the wavelength band of the illumination light IL passing through 410 is sequentially switched. Specifically, every time the rotary filter 410 makes one rotation, the light emitted from the light source lamp 430 passes through the optical filter Fs2 in turn, so that the second special light is generated, and the light emitted from the light source lamp 430 is optical.
  • the first reference light is generated by passing through the filter Fn1
  • the first special light is generated by passing the light emitted from the light source lamp 430 through the optical filter Fs1
  • the light emitted from the light source lamp 430 is converted into the optical filter Fn2.
  • the cycle in which the second reference light is generated by passing through is repeated.
  • the optical filters Fs1 and Fs2 are optical bandpass filters that selectively pass light in the 550 nm band. As shown in FIG. 4, the optical filter Fs1 allows light in a wavelength band R0 (W band) from equal absorption points E1 to E4, which will be described later, to pass through with low loss, and blocks light in other wavelength regions. It is configured.
  • the optical filter Fs2 is configured to pass light in a wavelength band R2 (N band) from equal absorption points E2 to E3, which will be described later, with low loss, and block light in other wavelength regions.
  • FIG. 4 is a diagram showing an example of an absorption spectrum of hemoglobin near 550 nm.
  • optical filters Fn1 and Fn2 are ultraviolet cut filters having the same transmission characteristics and passing light of the same wavelength band with low loss.
  • the optical filters Fn1 and Fn2 transmit light emitted from the light source lamp 430 in the wavelength region of 400 to 700 nm.
  • the wavelength band R1 shown in FIG. 4 is a band including the peak wavelength of the absorption peak P1 derived from oxygenated hemoglobin as described later, and the wavelength band R2 is the absorption peak P2 derived from reduced hemoglobin as described later.
  • the wavelength band R3 is a band including the peak wavelength of the absorption peak P3 derived from oxygenated hemoglobin, as will be described later.
  • the wavelength range R0 includes the peak wavelengths of the three absorption peaks P1, P2, and P3.
  • FIG. 4 is a diagram showing an example of an absorption spectrum of hemoglobin near 550 nm. A detailed description of the relationship between the amount of hemoglobin, the oxygen saturation of hemoglobin, and the wavelength band will be described later.
  • the light transmitted through the optical filters Fs1 and Fs2 is used as special light for illuminating the biological tissue T in order to obtain color image data for calculating the amount of hemoglobin of the captured biological tissue T and the oxygen saturation of the hemoglobin. .
  • the light transmitted through the optical filters Fn1 and Fn2 is used as reference light for illuminating the living tissue T in order to obtain color image data for generating a normal observation image.
  • the optical filters Fn1 and Fn2 may not be used, and the window on the frame 411 in which the optical filters Fn1 and Fn2 are arranged may be opened.
  • the first special light transmitted from the light source lamp 430 through the optical filter Fs1 is hereinafter referred to as Wide light
  • the second special light transmitted through the optical filter Fs2 from the light emitted from the light source lamp 430 Is referred to as “Narrow light” hereinafter
  • the reference light transmitted through the optical filters Fn1 and Fn2 among the light emitted from the light source lamp 430 is hereinafter referred to as “white light WL”.
  • the reference light generated when the light emitted from the light source lamp 430 passes through the optical filters Fn1 and Fn2 is transmitted from the light source device 400 to the first reference light and the second reference light.
  • the first reference light is hereinafter referred to as white light WL1
  • the second reference light is hereinafter referred to as white light WL.
  • the wavelength band R0 of the optical filter Fs1 and the wavelength band R2 of the optical filter Fs2 are included in the pass wavelength band (FIG. 2) of the G color filter of the color filter 141a. Therefore, the image of the living tissue T formed by the light that has passed through the optical filter Fs1 or Fs2 is obtained as an image of the G component of the color image data captured by the image sensor 141.
  • the optical filter Fs1 or the optical filter Fs1 or the optical filter Fs2 so that the light intensity of the special light generated by the optical filter Fs1 and the optical filter Fs2 is approximately the same so that an image with the same brightness can be obtained under the same exposure condition of the image sensor 414.
  • the transmittance of the optical filter Fs2 is adjusted.
  • a through hole 413 is formed in the peripheral edge of the frame 411.
  • the through-hole 413 is formed at the same position (phase) as the boundary between the optical filter Fn2 and the window where the optical filter Fs1 is arranged in the rotation direction of the frame 411.
  • a photo interrupter 422 for detecting the through hole 413 is arranged so as to surround a part of the peripheral edge of the frame 411.
  • the photo interrupter 422 is connected to the filter control unit 420.
  • the light source device 400 switches the four optical filters Fs2, Fn1, Fs1, and Fn2 in order in the optical path of the light emitted from the light source lamp 430, that is, light having different wavelength bands, that is, narrow light.
  • (Second special light), white light WL1 (first reference light), wide light (first special light), and white light WL2 (second reference light) are emitted as illumination light IL.
  • the light source device 400 of the present embodiment in one cycle in which the four illumination lights IL are sequentially emitted, is related to the order of emission of the illumination light IL between one emission of special light and another emission of special light.
  • the emission of the white light WL (reference light) is performed at least twice without continuing the emission of the white light WL (reference light).
  • the order of emission of the reference light and the special light is the sequence of the special light emission order determined for sequentially emitting the special light, specifically, the narrow light (second special light), the wide light ( This is the order in which the emission of the white light WL (reference light) is interrupted (disposed) twice in succession in the sequence of the emission of the first special light). As shown in FIG.
  • the light source device 400 includes narrow light (second special light), white light WL1 (first reference light), wide light (first special light), and white light WL2 (second reference light). Are sequentially emitted as the illumination light IL of the living tissue T, and the emission of the illumination light IL for one cycle is repeated.
  • FIG. 5 is a diagram illustrating an example of the order of emission of the reference light and the special light in the light source device 200 of the present embodiment.
  • the processor 200 acquires a normal observation image and a feature amount distribution image of the living tissue T and displays them on the display 300. Therefore, in this embodiment, since the white light WL is emitted twice in one cycle, the normal observation image is generated and displayed twice in one cycle.
  • the light source device 400 of the present embodiment emits two special lights, but may emit three or more special lights having different wavelength bands.
  • the white light WL reference light
  • the white light WL is not continuously emitted in two or more places, more than three places in the sequence of the emission order of three or more special lights. It is good to arrange (interrupt).
  • the emission of the Wide light (first special light) and the single emission of the white light WL (reference light) are performed.
  • the amount of hemoglobin is obtained as will be described later, that one emission of white light WL (reference light) and one emission of wide light (first special light) are continuous with each other. Therefore, when calculating the first ratio, it is preferable from the viewpoint that the positional deviation in the image of the image of the living tissue T can be suppressed.
  • the emission of narrow light (second special light) and one emission of white light WL (reference light), or white light WL (reference light) It is preferable that one emission of light) and the emission of narrow light (second special light) are continuous without interfering with other emission. Thereby, the white light WL (reference light) twice can be used as the illumination light IL of the living tissue T in one cycle, and the refresh rate of the normal observation image is improved.
  • the light source device 400 includes the light source lamp 430 that emits one light as a light source, and the light source device 400 includes white light WL (reference light), wide light, and narrow light ( The white light WL (reference light), the wide light, and the narrow light are transmitted by transmitting light in one wavelength band through a plurality of optical filters having different pass wavelength bands so as to correspond to the order of emission of the special light). It is preferable to be configured to emit (special light).
  • the wavelength band of the white light WL (reference light) of the present embodiment includes a wavelength band in which one of the components of the reference color image data does not have sensitivity to changes in the amount of hemoglobin in the living tissue T. It is preferable that it is set from the point that the influence of the scattering characteristics in the living tissue T can be appropriately removed in the first ratio.
  • the feature amount of the living tissue T is calculated by the feature amount acquisition unit 510 of the processor 500. Processing for calculating the amount of hemoglobin in the biological tissue T and the oxygen saturation Sat of hemoglobin as the feature amount from the captured image of the biological tissue T will be described below.
  • hemoglobin has a strong absorption band called a Q band derived from porphyrin near 550 nm.
  • the absorption spectrum of hemoglobin changes according to the oxygen saturation Sat representing the proportion of oxygenated hemoglobin HbO in the total hemoglobin.
  • the solid line waveform in FIG. 4 is an absorption spectrum of oxygen saturation Sat of 100%, that is, oxygenated hemoglobin HbO
  • the long broken line waveform is an absorption spectrum of oxygen saturation Sat of 0%, that is, reduced hemoglobin Hb. It is.
  • oxygenated hemoglobin HbO and reduced hemoglobin Hb have different peak wavelengths. Specifically, oxygenated hemoglobin HbO has an absorption peak P1 near a wavelength of 542 nm and an absorption peak P3 near a wavelength of 576 nm. On the other hand, reduced hemoglobin Hb has an absorption peak P2 near 556 nm.
  • FIG. 4 is an absorption spectrum when the sum of the concentrations of oxygenated hemoglobin HbO and reduced hemoglobin Hb is constant. Therefore, the ratio of oxygenated hemoglobin HbO and reduced hemoglobin Hb, that is, the absorbance is constant regardless of the oxygen saturation.
  • the isosbestic points E1, E2, E3, E4 appear.
  • the wavelength band sandwiched between the equal absorption points E1 and E2 is the wavelength band R1 described above, and the wavelength region sandwiched between the equal absorption points E2 and E3 is the wavelength band R2.
  • the wavelength band sandwiched between the equal absorption points E3 and E4 is the wavelength band R3, and the wavelength band sandwiched between the equal absorption points E1 and E4, that is, the combined band of the wavelength bands R1, R2, and R3 is the wavelength band. R0. Therefore, the wavelength band of the Wide light, which is the transmitted light that has passed through the optical filter Fs1 out of the light emitted from the light source lamp 430, is the wavelength band R0, and the light emitted from the light source lamp 430 is transmitted through the optical filter Fs2.
  • the wavelength band of the narrow light that is the transmitted light is the wavelength band R2.
  • the absorption of hemoglobin increases or decreases linearly with respect to the oxygen saturation.
  • the absorptions AR1 and AR3 of hemoglobin in the wavelength bands R1 and R3 increase linearly with respect to the oxygenated hemoglobin concentration, that is, the oxygen saturation.
  • the absorption AR2 of hemoglobin in the wavelength band R2 increases linearly with respect to the concentration of reduced hemoglobin.
  • the oxygen saturation is defined by the following equation (1).
  • formulas (2) and (3) representing the concentrations of oxygenated hemoglobin HbO and reduced hemoglobin Hb are obtained.
  • the absorption AR1, AR2, and AR3 of hemoglobin are characteristic amounts that depend on both the oxygen saturation and the amount of hemoglobin.
  • the total value of absorbance in the wavelength band R0 does not depend on the oxygen saturation Sat, but is a value determined by the amount of hemoglobin. Therefore, the amount of hemoglobin can be quantified based on the total absorbance in the wavelength band R0.
  • the oxygen saturation Sat can be quantified based on the total absorbance in the wavelength band R1, the wavelength band R2, or the wavelength band R3 and the amount of hemoglobin quantified based on the total value in the wavelength band R0. .
  • the feature amount acquisition unit 510 of the present embodiment calculates a hemoglobin amount of the biological tissue T based on a later-described first ratio having sensitivity to the amount of hemoglobin of the biological tissue T, and acquires a hemoglobin calculation unit 510a.
  • An oxygen saturation calculation unit 510b that calculates and acquires the oxygen saturation of hemoglobin in the living tissue T based on the calculated amount of hemoglobin and the second ratio described later having sensitivity to the oxygen saturation of hemoglobin, and a data selection unit 510c and a positional deviation amount calculation unit 510d.
  • the hemoglobin amount calculation unit 510a of the feature amount acquisition unit 510 of the form calculates the amount of hemoglobin based on the luminance component of the color image data in the wavelength band R0.
  • the luminance component is obtained by multiplying the R component of the color image data by a predetermined coefficient, multiplying the G component of the color image data by a predetermined coefficient, and multiplying the value of the B component of the color image data by a predetermined coefficient.
  • the result of multiplication can be calculated by adding them up.
  • the hemoglobin amount calculation unit 510a of the feature amount acquisition unit 510 includes color image data (first special light color image data) of the living tissue T using Wide light (first special light) as the illumination light IL.
  • the ratio Wide (Yh) / WL (R) or Wide (Yh) / ⁇ WL (R) + WL (G) ⁇ divided by the total component WL (R) + WL (G) of the G component WL (G) first The amount of hemoglobin is calculated based on the ratio.
  • WL (R) + WL (G) ⁇ is used to eliminate the change in the spectral characteristics of the living tissue T depending on the degree to which the illumination light IL is scattered on the surface of the living tissue T.
  • the reflection spectrum of the living tissue T such as the inner wall of the digestive tract has a wavelength characteristic of absorption by the components constituting the living tissue T (specifically, absorption spectrum characteristics of oxygenated hemoglobin and reduced hemoglobin), It is easily affected by the wavelength characteristic of scattering of illumination light by T.
  • R component WL (R) of color image data (reference light color image data) of living tissue T using white light WL (reference light) as illumination light IL, or total component WL (R) + WL of R component and G component (G) represents the degree of scattering of the illumination light IL in the living tissue T without being affected by the amount of hemoglobin or the oxygen saturation Sat.
  • the wavelength band of the white light WL is one of the components of the reference light color image data, It is preferable that the wavelength band is set so as not to be sensitive to changes in the amount of hemoglobin in the living tissue T. In addition, the wavelength band of the white light WL (reference light) is set so that one of the components of the reference light color image data includes a wavelength band that is not sensitive to changes in oxygen saturation. It is preferable.
  • a reference table representing the correspondence relationship between the information on the first ratio and the amount of hemoglobin in the living tissue T in which the amount of hemoglobin is known is stored in advance in the memory 512, and this reference table is used.
  • the amount of hemoglobin is calculated based on the value of the first ratio in the color image data captured by the living tissue T.
  • FIG. 6 is a diagram illustrating an example of a correspondence relationship between the first ratio and the amount of hemoglobin. In the figure, the amount of hemoglobin is normalized to be in the range of 0 to 1024, and the first ratio is normalized to be in the range of 0 to 1.
  • the luminance component of the color image data (first special light color image data) of the living tissue T using Wide light (first special light) as the illumination light IL as the first ratio.
  • G component Wide (G) instead of the luminance component Wide (Yh) of the color image data (first special light color image data) of the living tissue T using the illumination light IL.
  • the oxygen saturation calculation unit 510b of the feature amount acquisition unit 510 calculates the oxygen saturation Sat based on the second ratio defined below.
  • the oxygen saturation calculation unit 510b performs color image data (second special light color image data) of the living tissue T illuminated with the narrow light (second special light) that is the light in the wavelength band R2 that has passed through the optical filter Fs2.
  • the ratio Narrow (Yh) / Wide (Yh) is calculated as the second ratio.
  • the correspondence relationship obtained is obtained from a known sample and stored in the memory 512 in advance.
  • the oxygen saturation calculation unit 510b of the feature amount acquisition unit 510 uses the calculation result of the amount of hemoglobin obtained from the color image data generated by imaging the living tissue T and the above correspondence, and the lower limit value and the upper limit of the second ratio. A value is obtained, and the oxygen saturation Sat linearly changes according to the second ratio between the obtained lower limit value and upper limit value.
  • the second ratio Narrow (Yh) / Wide (Yh) of the imaged living tissue T Is calculated at which oxygen saturation Sat. In this way, the oxygen saturation calculation unit 510b of the feature amount acquisition unit 510 calculates the oxygen saturation Sat.
  • FIG. 7 is a diagram illustrating an example of the relationship between the upper limit value (Sat 100%) and the lower limit value (Sat 0%) of the second ratio that changes in accordance with the amount of hemoglobin.
  • the amount of hemoglobin is normalized to be in the range of 0 to 1024
  • the second ratio is normalized to be in the range of 0 to 1.
  • a reference table representing the correspondence relationship between the amount of hemoglobin and the value of the second ratio and the oxygen saturation Sat of hemoglobin is obtained from a known sample and stored in the memory 512 in advance, and this reference table is referred to.
  • the oxygen saturation Sat of hemoglobin can also be calculated from the calculated second ratio.
  • the second ratio is the luminance component Narrow (Yh) of the color image data (second special light color image data) of the living tissue T illuminated with the narrow light and the color of the living tissue T illuminated with the wide light.
  • G component Narrow of color image data (second special light color image data) of living tissue T illuminated with Narrow light which is used as a ratio with the luminance component Wide (Yh) of image data (first special light color image data).
  • the ratio between (G) and the G component Wide (G) of the color image data (first special light color image data) of the living tissue T illuminated with Wide light can also be used.
  • the narrow light in the wavelength band R2 is used for illumination of the living tissue T for the calculation of the second ratio, but is not limited to the narrow light.
  • special light having the wavelength band R1 or the wavelength band R2 as the wavelength band is used with the intention of using the wavelength band R1 or the wavelength band R2 in which the total absorbance changes with respect to the change in the oxygen saturation Sat.
  • the filter characteristic of the optical filter Fs2 may be set to the wavelength band R1 or the wavelength band R2.
  • the wavelength band of the narrow light may be included in the wavelength band of the wide light (first special light).
  • the wavelength band of Wide light is one of the components of the first special light color image data, for example, the luminance component and the G component are sensitive to changes in the amount of hemoglobin. It is preferable that the setting is made so as to include the wavelength band R0 that does not have sensitivity to the change in the saturation, because the oxygen saturation Sat can be accurately calculated.
  • the wavelength band of the narrow light (second special light) one of the components of the second special light color image data, for example, the luminance component and the G component is sensitive to a change in the oxygen saturation Sat of the living tissue T. It is preferable that the wavelength band R2 is set so as to include the oxygen saturation Sat accurately.
  • the above-mentioned Wide light is one of optical filters, and a wavelength band (first wavelength band) within a range of 500 nm to 600 nm in a wavelength band of white light WL (reference light),
  • the narrow light (second special light) is one of the optical filters.
  • a wavelength band (second wavelength band) narrower than the first wavelength band within the first wavelength band for example, a wavelength band between the equal absorption point E2 and the equal absorption point E3. It is preferably filtered light of the transmitted white light WL (reference light).
  • a feature amount distribution image such as an oxygen saturation distribution image showing the distribution of oxygen saturation Sat is required to have high image quality.
  • the feature amount distribution image is preferably 1 million pixels or more, more preferably 2 million pixels or more, and further preferably 8 million pixels or more.
  • the arithmetic circuit of the processor 200 increases and the processing load tends to increase. In particular, the above tendency is remarkable at a high pixel (high image quality) of 1 million pixels or more.
  • a reference table is provided in advance, and the amount of hemoglobin and the oxygen saturation Sat are calculated using this reference table.
  • the amount of hemoglobin and the oxygen saturation are obtained each time color image data is acquired.
  • the amount of hemoglobin and the oxygen saturation Sat can be calculated more efficiently than when Sat is calculated without using a reference table. For this reason, the arithmetic circuit of the processor 200 can be reduced. Accordingly, even when a high-quality image is generated, the low-cost, low heat generation, and low power-saving processor 200 can be provided.
  • the light source device 400 is configured to repeat the emission of a plurality of cycles, with the emission of white light WL (reference light), wide light, and narrow light (special light) as one cycle, and the image sensor 141 in one cycle includes
  • the number of times that the reference light color image data is generated is preferably larger than the number of times that the image sensor 141 generates the first special light color image data and the number of times that the image sensor 141 generates the second special light color image data. .
  • the ratio of the number of times of generating the reference light color image data to the number of times of generating the first special light color image data and the second special light color image data of the number of times of generating the reference light color image data are generated.
  • the ratio to the number of times is preferably 1.5 or more, and more preferably 2 or more.
  • the upper limit of this ratio is not particularly limited, but is preferably 4 or less from the viewpoint of securing a refresh rate of a feature amount distribution image obtained using the first and second special light color image data to a predetermined value or more. More preferably, it is 3 or less.
  • the refresh rate of the normal observation image is improved, the refresh rate of the feature amount distribution image is lowered relative to the refresh rate of the normal observation image. Since this is an auxiliary image for specifying the position of the lesion part in the inside, even if the refresh rate is relatively lowered, the stress applied to the operator who observes the living tissue T is small.
  • the electronic endoscope 100 is configured such that the imaging element 141 receives reflected light of the living tissue T in the wavelength bands of white light WL (reference light), wide light, and narrow light (special light).
  • the optical system includes the objective lens group 121 as described above, but does not include a cut filter that cuts at least part of the wavelength band of white light WL (reference light), wide light, and narrow light (special light). Accordingly, in the present embodiment, it is possible to obtain a highly accurate distribution image of the amount of hemoglobin and the oxygen saturation of hemoglobin by illuminating the living tissue T with the illumination light IL in the wavelength band described above. Therefore, it is preferable that the optical system is configured to transmit light in the wavelength bands of white light WL (reference light), wide light, and narrow light (special light).
  • the feature amount acquisition unit 510 of the present embodiment includes a data selection unit 510c and a positional deviation amount calculation unit 510d, so that the amount of highly reliable hemoglobin and oxygen saturation of hemoglobin are distributed. Is preferable in that it can be obtained.
  • the white light WL (reference light) and the wide light (first special light) emitted with a time interval are used for generating color image data used for calculating the first ratio.
  • white light WL (reference light) and Wide light (first special light) are used as other illumination light IL. It is preferable that the light is continuously emitted without interposing it.
  • the Wide light (first special light) and the narrow light (second special light) are used for generating color image data used for calculating the second ratio. It is preferable that (second special light) and Wide light (first special light) are continuously emitted without other emission.
  • the white light WL reference light
  • the white light WL1 is emitted from the light source device 200 between the narrow light emission and the wide light (first special light), and the wide light (first special light) is emitted and the white light.
  • the illumination light IL is emitted in the order in which the emission of WL2 (second reference light) is continued without interfering with other emission.
  • Narrow light second special light
  • white light WL1 first reference light
  • Wide light first special light
  • white light WL2 second special light
  • the light is emitted in the order of reference light.
  • the processor 200 obtains first reference light color image data by imaging the living tissue T illuminated with the white light WL1 (first reference light), and illuminates with the white light WL2 (second reference light).
  • the second reference light color image data is obtained by imaging the biological tissue T thus obtained. Therefore, the data selection unit 510c selects which of the first reference light color image data and the second reference light color image data is used for calculating the first ratio.
  • the selection by the data selection unit 510c is performed based on the amount of positional deviation between the image of the living tissue T in the first reference light color image data and the image of the living tissue T in the second reference light color image data in each cycle. Is called. For example, an image position shift may occur between the normal observation image and the oxygen saturation distribution image due to a rapid movement of the living tissue T or a hand shake during a procedure using the endoscope 100.
  • the feature amount calculation unit 510 uses the Wide light (first special light) without interposing other emission in order to suppress a decrease in reliability of the feature amount due to the displacement of the image of the living tissue T.
  • the first ratio is calculated using the second reference color image data and the first special light color image data obtained by continuously emitting the white light WL2 (second reference light).
  • the reliability of the first ratio due to the positional deviation of the image of the living tissue T may be reduced.
  • the emission of the white light WL2 (second reference light) is narrower than the emission of the white light WL1 (first reference light) (second special light). It is far from the emission of light.
  • the living tissue T represented by the first reference light color image data in each cycle. It is preferable to calculate the amount of positional deviation between the image of and the image of the living tissue T represented by the second reference light color image data. At this time, if the amount of positional deviation is outside the allowable range, the data selection unit 510c calculates the first ratio using the first reference color image data instead of the second reference color image data. Make a selection.
  • the image of the living tissue T illuminated with the white light WL1 (first reference light) and the image of the living tissue T illuminated with the narrow light (second special light) and the wide light (first special light) are used.
  • the possibility that the positional deviation amount is outside the allowable range with respect to the image of the illuminated living tissue T is quite low.
  • the feature amount acquisition unit 510 illuminates the image of the living tissue T illuminated with the white light WL1 (first reference light) and captured with the white light WL2 (second reference light) for the image of the living tissue T captured. It is preferable to include a positional deviation amount calculation unit 510d that calculates the positional deviation amount of the image. At this time, if the calculated displacement amount is outside the allowable range, the data selection unit 510c selects the first reference light color image data to be used for calculating the first ratio instead of the second reference light color image data. .
  • the amount of positional deviation of the image of the biological tissue T is, for example, two directions in the image based on the calculation result of the cross-correlation function between components at the same pixel position of the first reference light color image data and the second reference light image data Can be calculated.
  • the white light WL1 (first reference light) is emitted between the emission of the narrow light (second special light) and the emission of the wide light (first special light).
  • the white light WL1 (first special light) is emitted between the emission of the Wide light (first special light) and the second special light. It is preferable to emit reference light).
  • the white light WL2 (second reference light) is emitted before the Wide light (first special light)
  • the white light WL2 (second reference light)
  • the emission and the emission of the Wide light (first special light) be performed in the order in which the other emission is continued without being separated.
  • FIG. 8 is a diagram illustrating an example of a normal observation image displayed as a moving image on the display 300 of the endoscope system of the present embodiment and an oxygen saturation distribution image of hemoglobin.
  • the left image in the figure is a normal observation image
  • the right image is a distribution image of the oxygen saturation of hemoglobin.
  • the refresh rate of the normal observation image shown in FIG. 8 is such that no stress is given to the observation of the operator. For this reason, the operator who performs the procedure while operating the endoscope 100 can observe the living tissue T without stress, and the position of interest in the oxygen saturation distribution image of the hemoglobin of the living tissue T with high accuracy, for example, oxygen saturation.
  • a low-degree position can be identified on the image of the living tissue T in the normal observation image.
  • the endoscope system of the present invention has been described in detail above, the endoscope system of the present invention is not limited to the above-described embodiment, and various improvements and modifications can be made without departing from the gist of the present invention. Of course it is also good.

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Abstract

Ce système d'endoscope comprend : un dispositif source de lumière qui émet une lumière de référence et de multiples lumières spéciales à différentes régions de longueur d'onde de manière répétée dans un ordre prescrit et en tant que lumière d'éclairage pour illuminer un tissu biologique; un élément d'imagerie qui génère des données d'image couleur d'une image du tissu biologique illuminé avec la lumière d'éclairage susmentionnée; un processeur qui est pourvu d'une unité d'acquisition de valeur caractéristique qui utilise les données d'image couleur susmentionnées pour calculer la saturation en oxygène de l'hémoglobine dans le tissu biologique; et un dispositif d'affichage qui affiche une image du tissu biologique et une image de distribution de la saturation en oxygène. Concernant l'ordre de la lumière d'éclairage dans un cycle, une émission de la lumière de référence entre une émission de la lumière spéciale mentionnée ci-dessus et une autre émission de la lumière spéciale est effectuée par le dispositif source de lumière au moins deux fois, sans émission continue de la lumière de référence.
PCT/JP2016/074683 2016-08-24 2016-08-24 Système d'endoscope Ceased WO2018037505A1 (fr)

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011188929A (ja) * 2010-03-12 2011-09-29 Olympus Corp 蛍光内視鏡装置
WO2014192781A1 (fr) * 2013-05-30 2014-12-04 Hoya株式会社 Procédé et dispositif pour générer une image représentant la distribution de concentration de substances biologiques dans un tissu biologique
JP2016019569A (ja) * 2014-07-11 2016-02-04 オリンパス株式会社 画像処理装置、画像処理方法、画像処理プログラム、及び内視鏡システム
JP2016022043A (ja) * 2014-07-17 2016-02-08 Hoya株式会社 生体組織中の生体物質の濃度分布を示す画像を生成する方法
WO2016132940A1 (fr) * 2015-02-20 2016-08-25 Hoya株式会社 Dispositif source de lumière

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011188929A (ja) * 2010-03-12 2011-09-29 Olympus Corp 蛍光内視鏡装置
WO2014192781A1 (fr) * 2013-05-30 2014-12-04 Hoya株式会社 Procédé et dispositif pour générer une image représentant la distribution de concentration de substances biologiques dans un tissu biologique
JP2016019569A (ja) * 2014-07-11 2016-02-04 オリンパス株式会社 画像処理装置、画像処理方法、画像処理プログラム、及び内視鏡システム
JP2016022043A (ja) * 2014-07-17 2016-02-08 Hoya株式会社 生体組織中の生体物質の濃度分布を示す画像を生成する方法
WO2016132940A1 (fr) * 2015-02-20 2016-08-25 Hoya株式会社 Dispositif source de lumière

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