JP5600568B2 - Endoscope device - Google Patents

Description

  The present invention provides a light source device including a light source device that mixes narrow-band wavelength excitation light emitted from an excitation light source such as a laser light source and fluorescence light excited from the excitation light and emitted from a phosphor to produce white illumination light. The present invention relates to a mirror device.

  As a light source device used for an endoscope device, for example, a white light source device using a light emitting diode or a semiconductor laser diode as a light source has been developed. A white light source device excites a phosphor with excitation light (for example, blue laser light) emitted from a light source to generate fluorescence such as green, yellow, and red, and mixes excitation light and fluorescent light to generate white light. (Pseudo white light) is created.

In an endoscope apparatus, conventionally, a xenon lamp or a metal halide lamp is used as a light source of an illuminating unit that illuminates the inside of a body cavity. In order to promote further downsizing, higher brightness, and cost reduction of an endoscope. In addition, the use of a white light source device using an excitation light source such as a light emitting diode or a semiconductor laser diode as a light source has become active.
In addition, a white light source device using a light emitting diode or a semiconductor laser diode has an advantage that the amount of heat generation is suppressed lower than that of a xenon lamp or a metal halide lamp, and deterioration of the endoscope due to heat generation can be suppressed.

  In Patent Document 1, as described above, in the white light source device using the excitation light source, when the oscillation wavelength of the excitation light in the excitation light source varies between the white light source devices, the light emission amount of the phosphor changes, and as a result, the light is finally output. There is a problem that the amount of light and chromaticity of the white light to be changed. On the other hand, in Patent Document 1, a driving current for driving the excitation light source is input as a pulse, and the amount of emitted light is made constant by changing at least one of the number of pulses, the pulse width, the pulse amplitude, and the duty ratio, The color of white light between the white light source devices is stabilized, and the white balance of the captured image is stabilized. The light quantity is a concept including not only the emission intensity but also the emission spectrum which is the distribution thereof.

JP 2009-56248 A

When the phosphor used in the white light source device changes at least one of the oscillation wavelength and emission intensity from the excitation light source, the fluorescence characteristics change, and as a result, the emission spectrum of the white light finally output changes, and imaging There is a problem that the white balance of the image changes. Here, the fluorescence characteristics refer to the characteristics of the phosphor including the emission intensity of the fluorescent light and the amount of emitted light.
In particular, when the white balance of the captured image is set on the basis of the case where the excitation light amount is maximized, the excitation light amount is reduced to irradiate light with insufficient bluishness and not suitable for diagnosis. End up. The excitation light amount is a concept including the emission intensity of the excitation light, and the excitation light refers to light that causes the phosphor to emit fluorescence.

The method described in Patent Document 1 can always obtain illumination light having an appropriate light amount and chromaticity based on the accumulated light amount and chromaticity of white light, and a white light source having a different oscillation wavelength (center emission wavelength) of excitation light. This is an effective method for correcting variations in the appearance of an image by correcting the accumulated light quantity and chromaticity of white light due to variations in the oscillation wavelength of excitation light between devices and stabilizing the color. However, in the method of Patent Document 1, for example, when the pulse amplitude is greatly changed, the chromaticity changes greatly, and it may be difficult to correct the change in chromaticity by changing the number of pulses and the pulse width. Many (see Patent Document 1, FIG. 12, etc.).
In other words, as soon as the excitation light amount is changed, the emission intensity and the emission light amount of the fluorescent light change, the chromaticity of the white light irradiated to the subject changes, and the white balance of the captured image also changes. It cannot be said that it works well in an endoscope apparatus in which the excitation light amount needs to be changed greatly according to the distance and reflectance of the subject.

  Since the change in white light relative to the change in the amount of excitation light described above differs depending on the central emission wavelength of the excitation light, the effect is particularly noticeable when the combination of the white light source device and the endoscope is changed in the market. Appear in

  Therefore, the present invention mixes the first narrow-band light emitted from the first light source and the first fluorescent light emitted from the phosphor excited by the first narrow-band light to obtain illumination light. An endoscope apparatus including a light source device, and even if the emission wavelength of the first narrowband light is changed by changing the combination of the light source device and the endoscope, the first narrowband is also used. An object of the present invention is to provide an endoscope apparatus in which the white balance of a captured image does not change even when the amount of emitted light is changed.

  In order to solve the above-described problem, the present invention is a first light source that emits first narrowband light having a first narrowband wavelength, which is different from the first light source. A second light source that emits second narrowband light having a second wavelength, and a light source information storage unit that stores the first wavelength of the first narrowband light from the first light source. And the first wavelength is within a predetermined fluctuation range with respect to the first central emission wavelength of the first light source, and at least a part of the first narrowband light. And is excited by the first narrowband light functioning as excitation light, emits first fluorescent light having a wavelength band different from the first wavelength which is an excitation wavelength, and the first narrowband light is emitted. Fluorescence characteristics change according to fluctuations in the excitation wavelength with respect to the emission amount of the band light and the first central emission wavelength. A fluorescent property storage unit that stores a first fluorescent property of the phosphor that changes in response to fluctuations in the amount of emitted light and the excitation wavelength, the excitation light transmitted through the phosphor, and the phosphor From a subject irradiated with illumination light, light mixed with the first fluorescent light emitted from the phosphor, or light mixed with the excitation light, the first fluorescent light, and the second narrowband light An endoscope having an imaging unit that captures an image with the return light of the illumination light and outputs the captured image signal; and reads the excitation wavelength from the light source information storage unit of the light source device, and The first fluorescence characteristic of the phosphor read out from the fluorescence characteristic storage unit of the mirror is read out and the first fluorescence characteristic of the phosphor with respect to the fluctuation of the excitation wavelength and the excitation light having the readout excitation wavelength is read out. From the fluorescence characteristics of Emission of the second narrowband light from the second light source added to the emission light quantity of the excitation light from the first light source so that the white balance of the captured image signal falls within a predetermined range. An endoscope apparatus comprising: a processor device that calculates a light amount and has a control unit that controls the second light source so that the calculated emission light amount of the second narrowband light is obtained. provide.

  The second wavelength of the second narrowband light from the second light source of the light source device falls within a predetermined variation range with respect to a second central emission wavelength of the second light source. The light source information storage unit further stores the second wavelength of the second narrowband light from the second light source, and the phosphor further includes the second light source. And transmitting at least a part of the narrow-band light and being excited by the second narrow-band light to emit second fluorescent light having a wavelength band different from the second wavelength, and the second central light emission. The fluorescence characteristic changes according to the change of the second wavelength with respect to the wavelength, and the fluorescence characteristic storage unit further changes with respect to the change of the second wavelength of the second narrowband light. The second fluorescent characteristic of the phosphor is stored, and the endoscope includes the As the bright light, the excitation light and the first fluorescent light, and the light obtained by mixing the second narrow-band light and the second fluorescent light are used. The second wavelength is further read from the light source information storage unit of the light source device, and further from the fluorescence characteristic storage unit of the endoscope, the second of the phosphor with respect to the read variation of the second wavelength. Read out the fluorescence characteristics of the two, and from the first and second fluorescence characteristics of the read phosphor, the white balance of the captured image signal falls within a predetermined range so that the white light from the first light source The amount of emitted light of the second narrowband light from the second light source added to the amount of emitted light of the first narrowband light is calculated, and the calculated amount of emitted light of the second narrowband light is calculated. It controls the second light source. It is preferred.

  Moreover, it is preferable that the said fluorescence characteristic contains the emitted light quantity of the said fluorescence light.

  Furthermore, the processor device corrects the correspondence between the amount of light emitted from the first light source and the amount of light emitted from the second light source necessary for the captured image signal to maintain a reference white balance. A correction information storage unit that stores a table, and when the endoscope device is configured by connecting the light source device, the endoscope, and the processor device to each other in the market, the control unit includes: The first wavelength and the second wavelength stored in the light source information storage unit, the first fluorescence characteristic and the second wavelength of the phosphor stored in the fluorescence characteristic storage unit of the endoscope And the correction table is created and stored in the correction information storage unit, and the required amount of emitted light of the second light source is calculated from the correction table and the amount of emitted light of the first light source. The required Based on the Do amount of emitted light, it is preferable to control the amount of emitted light of said second light source

  Further, it is preferable that the reference white balance is a white balance of the captured image signal when the emission from the second light source is stopped and the amount of light emitted from the first light source is maximized.

  The wavelength band of the second narrowband light is preferably on the shorter wavelength side than the wavelength band of the first narrowband light, and the first light source has a first wavelength of 445 ± 10 nm. It is preferable that the second light source is a blue-violet laser light source having a second wavelength in the range of 405 ± 10 nm.

  Further, it is preferable that the wavelength band of the second narrowband light is on the longer wavelength side than the wavelength band of the first narrowband light.

  Further, as the white balance, it is preferable to use a G / B ratio that is a ratio of a green light component and a blue light component of the captured image signal.

  It is preferable that the illumination light is pseudo white light including a red light component, a green light component, and a blue light component in a predetermined wavelength band.

  The present invention also provides a first light source that emits a first narrowband light having a first wavelength that has been narrowed, and the first narrowband light from the first light source. A light source information storage unit for storing a wavelength, wherein the first wavelength is within a predetermined variation range with respect to a first central emission wavelength of the first light source; First fluorescent light having a wavelength band different from the first wavelength, which is an excitation wavelength, is transmitted by at least a part of one narrow band light and is excited by the first narrow band light functioning as excitation light. Of the first narrow-band light and a phosphor whose fluorescence characteristics change in accordance with the fluctuation of the excitation wavelength with respect to the first central emission wavelength, the emission light amount of the excitation light, and the excitation wavelength. Fluorescence characteristics for storing the first fluorescence characteristics of the phosphor that change with respect to fluctuations A storage unit, and a subject in which the excitation light transmitted through the phosphor and the first fluorescence light emitted from the phosphor are mixed, or an object irradiated with the excitation light and the first fluorescence light as illumination light An imaging unit that captures an image with the return light of the illumination light and outputs the captured image signal, and reads the excitation wavelength from the light source information storage unit of the light source device, The first fluorescence characteristic of the phosphor is read out from the fluorescence characteristic storage unit of the endoscope and the first fluorescence characteristic of the phosphor with respect to the fluctuation of the excitation wavelength and the excitation light having the readout excitation wavelength is read out. The imaging gain of the imaging unit multiplied by the captured image signal with respect to the amount of emission light of the excitation light from the first light source so that the captured image signal maintains a reference white balance from the fluorescence characteristic of 1. The To provide an endoscope apparatus, characterized in that it comprises a processor device having a Gosuru control unit.

  Moreover, it is preferable that the said 1st fluorescence characteristic contains the emitted light quantity of the said fluorescence light.

  Furthermore, the processor device stores a correction table in which a correspondence relationship between the amount of light emitted from the first light source and the imaging gain of the imaging unit necessary for maintaining the white balance of the captured image signal is recorded. A correction information storage unit that stores the light source device, the endoscope, and the processor device connected to each other in the market to configure the endoscope device, the control unit is configured to control the light source of the light source device. Obtaining the first wavelength stored in the information storage unit and the first fluorescence characteristic of the phosphor stored in the fluorescence characteristic storage unit of the endoscope, and creating the correction table Storing the correction information in the correction information storage unit, obtaining a required imaging gain from the correction table and the amount of light emitted from the first light source, and controlling the imaging gain of the imaging unit based on the required imaging gain. It is preferable.

  The reference white balance is preferably the white balance of the captured image signal when the amount of light emitted from the first light source is maximized.

  According to the endoscope apparatus of the present invention, even if the emission wavelength of the excitation light in the light source is changed or even if the excitation light quantity of the phosphor is changed, the white balance that does not change in color is maintained. A captured image can be acquired.

1 is an external view showing a configuration of an endoscope apparatus according to a first embodiment of the present invention. It is a block diagram which shows the internal structure of the endoscope apparatus which concerns on 1st Embodiment of this invention. (A) is a graph showing the wavelength profile of the emission spectrum of the second fluorescent light obtained by wavelength-converting the blue-violet laser light and the blue laser light from the blue-violet laser light source according to the endoscope apparatus of the present invention. (B) is a graph showing the wavelength profile of the emission spectrum of the first fluorescent light in which the blue laser light and the blue laser light from the blue laser light source of the present invention have been wavelength-converted by the phosphor. 5 is a flowchart defining a procedure for calculating information of a correction table for correcting an additional laser light quantity (blue violet laser light emission quantity) with respect to an excitation light quantity (blue laser light emission quantity) in the first embodiment of the present invention. In the endoscope apparatus according to the present invention, it is an explanatory diagram in the case of measuring the fluorescence characteristics of a phosphor by calculating the white balance of a captured image (signal). (A) is the G / B ratio (G light component / B light) of the illumination light including the excitation light quantity and the first fluorescent light from the phosphor in the endoscope apparatus according to the first embodiment of the present invention. (B) is a graph showing the relationship between the G / B ratio (G light component / G) of illumination light including fluctuations in the excitation wavelength and the amount of excitation light, and the first fluorescent light from the phosphor. (C) is a graph showing the relationship between the fluctuation of the additional laser wavelength and the additional laser light amount, and the G / B ratio of the illumination light including the second fluorescent light from the phosphor. It is a graph which shows a relationship, (D) is a graph which shows the relationship between an excitation light quantity and the additional laser light quantity required in order to maintain a captured image (signal) to a reference | standard white balance. It is a block diagram which shows the internal structure of the endoscope apparatus which concerns on 2nd Embodiment of this invention. In the second embodiment of the present invention, it is a flowchart defining a procedure for calculating information of a correction table for correcting the gain of the B light component (B light image signal) of the captured image signal with respect to the excitation light amount. (A) is the graph which shows the relationship between the fluctuation | variation of excitation wavelength, excitation light quantity, and G / B ratio of illumination light in the endoscope apparatus which concerns on 2nd Embodiment of this invention, (B), It is a graph which shows the relationship between excitation light quantity and B light gain required in order to maintain a captured image (signal) at the reference | standard white balance.

  An endoscope apparatus according to the present invention will be described in detail below based on a preferred embodiment shown in the accompanying drawings.

FIG. 1 is an external view as an example of an endoscope apparatus of the present invention, and FIG. 2 is a diagram for explaining a first embodiment of the endoscope apparatus of the present invention, and is a concept of the endoscope apparatus. It is a typical block diagram.
As shown in FIGS. 1 and 2, the endoscope apparatus 10 according to the first embodiment of the present invention includes an endoscope 11, a light source device 12, and a processor device 13. The processor device 13 is connected to a display unit 15 that displays image information and an input unit 17 that receives an input operation. The endoscope 11 includes an illumination optical system that emits illumination light from the distal end of the endoscope insertion unit 19 and an imaging optical system that includes an imaging element 26 (see FIG. 2) that captures an observation region. It is a endoscope.
Illumination light refers to light emitted from the endoscope 11 toward the subject regardless of narrow-band light or white light.

  The endoscope 11 includes a flexible endoscope insertion portion 19 that is inserted into the subject, an operation portion 23 that performs a bending operation and observation operation of the distal end of the endoscope insertion portion, Connector units 25A and 25B are provided for detachably connecting the endoscope 11 to the light source device 12 and the processor device 13. Although not shown, various channels such as a forceps channel for inserting a tissue collection treatment instrument and the like, a channel for air supply / water supply, and the like are provided inside the operation unit 23 and the endoscope insertion unit 19. .

  The endoscope insertion portion 19 includes a flexible soft portion 31, a bending portion 33, and a distal end portion (hereinafter also referred to as an endoscope distal end portion) 35. As shown in FIG. 2, the endoscope distal end portion 35 has an irradiation port 21 that irradiates illumination light to the observation region, a CCD (Charge Coupled Device) image sensor that acquires image information of the observation region, and a CMOS ( An image pickup device 26 such as a complementary metal-oxide semiconductor (image sensor) is disposed. In the back of the irradiation port 21, a phosphor 20 that emits fluorescence upon receiving excitation light from the light source device is disposed at the tip of the optical fiber 18, and an objective lens unit 24 is disposed on the light receiving surface of the image sensor 26. .

  In addition, as shown in FIG. 2, the endoscope 11 serves as a signal processing system for an image signal of a captured image from the image sensor 26, and performs correlated double sampling (CDS) and automatic gain control on a captured image signal that is an analog signal. A CDS / AGC circuit 27 for performing (AGC), and an A / D converter (A / D converter) 28 for converting an analog image signal subjected to sampling and gain control in the CDS / AGC circuit 27 into a digital image signal And a fluorescence characteristic storage unit 29 that stores the fluorescence characteristics of the phosphor 20 described above. When the endoscope 11 and the processor device 13 are connected, the fluorescence property storage unit 29 outputs the fluorescence property of the phosphor 20 unique to each endoscope 11 to the processor device 13. The digital image signal A / D converted by the A / D converter 28 is input to the image processing unit 52 of the processor device 13 via the connector unit 25B.

  The bending portion 33 is provided between the soft portion 31 and the distal end portion 35 and is freely bent by the rotation operation of the angle knob 22 disposed in the operation portion 23. The bending portion 33 can be bent in an arbitrary direction and an arbitrary angle according to a part of the subject in which the endoscope 11 is used, and observation of the irradiation port 21 of the endoscope tip 35 and the imaging element 26. The direction can be directed to the desired observation site. Although illustration is omitted, a cover glass or a lens is disposed at the irradiation port 21 of the endoscope insertion portion 19.

  The light source device 12 generates illumination light to be supplied to the irradiation port 21 of the endoscope distal end portion 35, and the processor device 13 includes an image processing unit 52 that performs image processing on an image signal from the imaging element 26. The light source device 12 is connected to the endoscope 11 via the connector portion 25A, and the processor device 13 is connected to the endoscope 11 via the connector portion 25B. The display unit 15 and the input unit 17 are connected to the processor device 13. Based on instructions from the input unit 15 and the operation unit 23, the processor device 13 performs image processing on the imaging signal transmitted from the endoscope 11, and generates and supplies a display image to the display unit 15.

As shown in FIG. 2, the light source device 12 includes a blue laser light source (LD1) 42 as a first light source and a blue-violet laser light source (LD2) 44 as a second light source. Specifically, the blue laser light source 42 is a laser diode that emits blue laser light having a central emission wavelength λ ₁ (445 nm) as first narrowband light, and is installed at the endoscope tip 35 as an excitation light source. It acts as excitation light that causes a phosphor 20 described later to emit fluorescence. The blue laser light is mixed with the first fluorescent light that is fluorescently emitted, and is irradiated to the subject as white (pseudo white) irradiation light.

The blue-violet laser light source 44 is a laser diode that emits blue-violet laser light having a central emission wavelength λ ₀ (405 nm) as second narrowband light, and serves as an additional laser light source for the B light component ( As additional laser light that compensates for the shortage of the blue light component), a captured image picked up by the return light from the subject by illumination light is irradiated to maintain the reference white balance in a predetermined range.
In addition, a part of the second narrowband light from the blue-violet laser light source 44 also acts as excitation light that causes a phosphor 20 (described later) installed at the endoscope distal end 35 to emit fluorescence. The amount of emitted light is about 1/20 as compared with the first fluorescent light described above. The second fluorescent light is also applied to the subject as part of the illumination light.

The actual blue laser light source 42 and blue violet laser light source 44 are often slightly shifted from their ideal center emission wavelengths λ ₁ and λ _{0 in} the individual light source devices 12. Therefore, the actual wavelength of the first narrowband light emitted from the blue laser light source 42 is set as the first wavelength, and the actual wavelength of the second narrowband light emitted from the blue-violet laser light source 44 is set as the second wavelength. The wavelength.
Further, the deviation from the central emission wavelength of each of the first wavelength and the second wavelength is regarded as a fluctuation, and the maximum width of the deviation that can be assumed is expressed as ± Δλ as a predetermined fluctuation range. Thus, using the central emission wavelengths λ ₁ and λ ₀ , the first wavelength is in the range of λ ₁ ± Δλ, and the second wavelength is in the range of λ ₀ ± Δλ.

  As the blue laser light source 42 and the blue-violet laser light source 44, a broad area type InGaN laser diode can be used, and an InGaNAs laser diode or a GaNAs laser diode can also be used. In addition, a light-emitting body such as a light-emitting diode may be used as the light source.

  The light emission from the blue laser light source 42 and the blue violet laser light source 44 is individually controlled by the light source control unit 40, and the light amount ratio between the emitted light amount of the blue laser light source 42 and the emitted light amount of the blue violet laser light source 44. Is changeable.

  The blue laser light and the blue-violet laser light emitted from the blue laser light source 42 and the blue-violet laser light source 44 are respectively input to optical fibers by a condenser lens (not shown), and are combined by a multiplexer 46, and are connected to a connector. Is transmitted to the unit 25A. However, the present invention is not limited to this, and the configuration may be such that the laser light from the blue laser light source 42 and the blue-violet laser light source 44 is sent directly to the connector portion 25A without using the multiplexer 46.

  The combined light obtained by combining the first narrowband light and the second narrowband light supplied to the connector portion 25A passes through the optical fiber 18 to the endoscope distal end portion 35 of the endoscope 11. Is transmitted.

  The optical fiber 18 is a multimode fiber, and as an example, a thin cable having a core diameter of 105 μm, a cladding diameter of 125 μm, and a diameter including a protective layer serving as an outer shell of φ0.3 to 0.5 mm can be used.

The phosphor 20 functions as a wavelength conversion member, and emits fluorescent light upon receiving narrowband light acting as excitation light, as described above. The phosphor 20 mainly includes a plurality of types of phosphors that absorb part of the energy of the blue laser light and emit fluorescent light from green to yellow. As a specific example of the phosphor 20, for example, a YAG phosphor, a phosphor containing BAM (BaMgAl ₁₀ O ₁₇ ), or the like can be used. Therefore, white (pseudo white) illumination light is obtained as a result of the combination of the green to yellow first fluorescent light that uses blue laser light as excitation light and the blue laser light that is transmitted without being absorbed by the phosphor 20. Is emitted from the irradiation port 21 of the endoscope distal end portion 35. If a blue laser light source is used as an excitation light source as in this embodiment, white light with a high light emission amount can be obtained with high light emission efficiency, and the light emission amount of white light can be easily adjusted.

The phosphor 20 described above can prevent the occurrence of noise superposition, which is an obstacle to imaging, or flickering when performing moving image display, due to speckle caused by the coherence of laser light. In addition, the phosphor 20 takes into account the difference in refractive index between the phosphor constituting the phosphor and the fixing / solidifying resin serving as the filler, and the particle size of the phosphor itself and the filler is set to light in the infrared region. In contrast, it is preferable to use a material that has low absorption and high scattering. As a result, the scattering effect is enhanced without reducing the light intensity with respect to light in the red or infrared region, and an optical path changing means such as a concave lens becomes unnecessary, and the optical loss is reduced.

  FIG. 3 shows a wavelength profile (A) that is an emission spectrum of the second fluorescent light in which the blue-violet laser light and the blue laser light from the blue-violet laser light source 44 are wavelength-converted by the phosphor 20 in the present embodiment, 4 is a graph showing a blue laser light from a blue laser light source and a wavelength profile (B) that is an emission spectrum of first fluorescent light in which the wavelength of the blue laser light is converted by the phosphor.

The blue laser light is represented by a bright line having a central emission wavelength of 445 nm, and the first fluorescent light from the phosphor 20 by the blue laser light has a spectral intensity distribution in which the emission intensity increases in a wavelength band of approximately 450 nm to 700 nm. The white light (pseudo white light) described above is formed by the profile B of the first fluorescent light and the blue laser light.
The blue-violet laser light is represented by a bright line having a central emission wavelength of 405 nm, and the second fluorescent light from the phosphor 20 caused by the blue-violet laser light is also 1/20 of the first fluorescent light as described above. However, the spectral intensity distribution increases in emission intensity in a wavelength band substantially equivalent to that of the first fluorescent light. Further, the profile A based on the second fluorescent light and the blue-violet laser light is irradiated as substantially blue-violet light alone because the light emission amount of the second fluorescent light is small as described above.

The illumination light consisting of the profile A and the profile B is reflected by the subject and detected as a picked-up image signal by the image pickup device as return light.
As shown in FIG. 3, the profile A and the profile B are mainly composed of the B light component mainly composed of blue-violet laser light and blue laser light, and the undulating central portion of the first fluorescent light and the second fluorescent light. The G light component to be detected and the R light component mainly composed of the above-described undulating long-wavelength side portion are mainly classified and detected as captured image signals.

  As described above, the white balance of the captured image is the ratio of the signal intensities of the R light component, G light component, and B light component detected by the image sensor. Therefore, in order to maintain the reference white balance in the captured image, it is necessary to maintain the signal intensity ratio of the R light component, the G light component, and the B light component in the captured image within a predetermined range.

Moreover, in the fluorescent substance 20, it has been found that the emitted light quantity of the fluorescent light with respect to the excitation light quantity is not always constant, and the fluorescence characteristics of the fluorescent substance 20 change according to the excitation light quantity.
Here, the excitation light amount is the light amount of the excitation light, and the excitation light is a concept including not only the first narrowband light but also the second narrowband light added as the additional laser light. In the specification, hereinafter, the first narrow-band light and the light amount thereof are described as the excitation light and the excitation light amount, and the second narrow-band light and the light amount thereof are separately described as the additional laser light and the additional laser light amount.

In addition, as described above, the white balance of the captured image changes depending on the excitation light amount. Therefore, in order to emit the additional laser light and maintain the captured image at the reference white balance, the white balance changes with respect to the excitation light amount and the additional laser light amount. Information is required.
Therefore, in the endoscope, the white balance change in the captured image when the white plate is imaged is calculated as a graph with respect to the excitation light amount and the additional laser light amount, and the information of the graph is stored as the fluorescence characteristics of the phosphor. This is used to adjust the additional laser light quantity with respect to the excitation light quantity.
Here, the fluorescence characteristics of the phosphor 20 can be broadly classified according to the oscillation wavelength. The first fluorescence characteristics for the excitation light and the second fluorescence characteristics for the additional laser light can be considered.

Note that the shapes of the wavelength profiles of the first fluorescent light and the second fluorescent light do not change so much with respect to the excitation light amount and the additional laser light amount, and the B light component of the excitation light and additional laser light that excites the phosphor. On the other hand, since the R light component and the G light component, which are mainly the first fluorescent light and the second fluorescent light, change at a substantially constant rate, the G light component and the B light component are It is possible to use the G / B ratio, which is the ratio of the signal intensity.
Therefore, in the present invention, changes in the G / B ratio with respect to the excitation light amount and the additional laser light amount are respectively calculated as graphs, and information on these graphs is stored as the first fluorescence characteristic and the second fluorescence characteristic.

  Further, as described above, the central emission wavelengths of the excitation light source and the additional laser light source vary somewhat for each light source and have a predetermined fluctuation range. Therefore, as described above, the central emission for each light source can be obtained simply by storing the change in the fluorescence characteristic of the phosphor with respect to the excitation light amount and the additional laser light amount as information on the graph of the change in G / B ratio with respect to the excitation light amount and the additional laser light amount. It cannot cope with wavelength variations.

Therefore, as described above, in order to maintain the reference white balance in the captured image, in the endoscope, the center emission wavelength λ ₁ and the fluctuation range ± Δλ of the excitation light and the center emission wavelength λ ₀ of the additional laser light are further provided. In consideration of the fluctuation range ± Δλ, for each oscillation wavelength including these fluctuation ranges, the change in the G / B ratio with respect to the change in the excitation light amount and the additional laser light amount is calculated as a graph. Are also stored as the first fluorescence characteristic and the second fluorescence characteristic. Accordingly, even if the first wavelength of the excitation light and the second wavelength of the additional laser light are changed by a maximum ± Δλ from their center emission wavelengths λ ₁ and λ ₀ , it can be dealt with.

  In addition, the white light referred to in this specification is not limited to one that strictly includes all wavelength components of visible light, and includes light in a specific wavelength band such as R light, G light, and B light. For example, light including a wavelength component from green to red, light including a wavelength component from blue to green, and the like are included in a broad sense.

In the endoscope apparatus 10, illumination light having different characteristics can be obtained according to the mixing ratio of the profiles A and B by relatively increasing and decreasing the light amounts of the profile A and the profile B by the light source control unit 40. it can.
As described above, when the two laser beams are not multiplexed, the endoscope 11 has two irradiation ports (not shown) at the tip 35 of the endoscope, and one irradiation port at the tip. A configuration may be adopted in which a phosphor is provided and pseudo white light composed of blue laser light and fluorescence light is emitted, and the other irradiation port is not provided with a phosphor at the tip portion and is irradiated with blue-violet laser light as it is.

  Returning again to FIG. As described above, the illumination light including the excitation light, the first fluorescent light from the phosphor 20, the additional laser light, and the second fluorescent light from the phosphor 20 is reflected from the distal end portion 35 of the endoscope 11. Irradiation is directed toward the observation region of the specimen. Then, the state of the observation area irradiated with the illumination light is imaged on the light receiving surface of the image sensor 26 by the objective lens unit 24 and imaged.

  A captured image signal output from the image sensor 26 after imaging is subjected to sampling and gain control by the CDS / AGC circuit 27, and then transmitted to the A / D converter 28 to be converted into a digital signal. To the processor device 13.

  The processor device 13 includes a control unit 50 that controls the light source device 12 through the light source control unit 40, an image processing unit 52 that is connected to the control unit 50, and a correction information storage unit 54. As described above, when the light source device 12 and the processor device 13 are connected, information on the central emission wavelengths of the blue laser light source 42 and the blue-violet laser light source 44 of the light source device 12 is output to the control unit 50 of the processor device 13. Is done. Then, when the endoscope 11 is connected to the processor device 13, the control unit 50 controls the endoscope 11 based on the information on the respective central emission wavelengths of the blue laser light source 42 and the blue-violet laser light source 44. The first fluorescence characteristic and the second fluorescence characteristic included in the fluorescence characteristic storage unit 29 are acquired.

The control unit 50 captures captured image information from the image processing unit 52 or captured image signal from the CDS / AGC circuit 27 so that the captured image maintains the reference white balance even when the amount of excitation light from the blue laser light source 42 changes. The amount of additional laser light from the blue-violet laser beam source 44 necessary for white balance adjustment is calculated. Details of the calculation of the additional laser light amount with respect to the change in the excitation light amount will be described later.
The calculated relationship between the excitation light amount and the additional laser light amount is stored in advance in the correction information storage unit 54 as the correction table 56 and is used for controlling the blue-violet laser light source 44 through the light source control unit 40.

  Further, the light source control unit 40 controls drive currents in the blue laser light source 42 and the blue-violet laser light source 44, thereby controlling the amount of emitted light. Therefore, in the correction information storage unit 54, the relationship between the drive current for the blue laser light source 42 and the blue violet laser light source 44 and the amount of emitted light is also stored in advance as information. Then, the control unit 50 calculates drive current information necessary for the amount of emitted light, outputs the drive current information to the light source control unit 40, and the light source control unit 40 controls the drive current flowing through each light source. By doing so, the amount of emitted light is controlled.

The captured image signal output from the A / D converter 28 is input to the image processing unit 52 described above. The image processing unit 52 converts the input digital image signal into image data, performs appropriate image processing, and generates desired output image information. The generated output image information is output to the display unit 15 through the control unit 50 according to instructions from the input device 17 and the operation unit 23.
The above is the configuration of the endoscope apparatus according to the first embodiment of the present invention.

Next, in the endoscope apparatus 10 of the present invention, the relationship between the excitation light amount from the blue laser light source 42 and the additional laser light amount from the blue-violet laser light source 44 for keeping the white balance of the captured image signal at a reference value. The operation of creating the correction table 56 shown and storing it in the correction information storage unit 54 will be described with reference to the flowchart of FIG.
Further, hereinafter, the first embodiment will be basically described with white balance as the G / B ratio.

First, the endoscope 11 is connected to the reference light source device and the processor 13 (S10). Next, as shown in FIG. 5, the endoscope tip 35 is placed so as to face the white plate, and excitation light is emitted from the blue laser light source 42 (S <b> 12). Then, the reference light source device is operated to adjust the center emission wavelength of the blue laser light source 42 to λ ₁ (for example, 445 nm) (S14). As described above, the reference light source device is a light source device that can arbitrarily shift the center emission wavelengths of the blue laser light source 42 and the blue-violet laser light source 44 by a predetermined amount.

After adjusting the center emission wavelength of the blue laser light source 42 to lambda _1, the output (driving current value) as the maximum, the illumination light obtained by mixing the excitation light and fluorescence light is irradiated with the white plate, the return light An image is picked up by the image pickup element 26. The image sensor 26 outputs a captured image signal (captured image information) (S16).

The picked-up image signal picked up by the image pickup device 26 is correlated double-sampled by the CDS / AGC circuit 27 to remove reset noise and amplifier noise in the image pickup device, and the analog picked-up image signal is digitally converted by the A / D converter 28. It is converted as a captured image signal and output to the image processing unit 52.
In the image processing unit 52, for example, the captured image signal is separated into three components of an R light component, a G light component, and a B light component, and a display image signal to be displayed in the output unit 15 is generated. . The control unit 50 calculates the ratio of the signal values of the R light component, the G light component, and the B light component separated by the image processing unit 52, and calculates the reference white balance in the image sensor. As described above, the reference white balance may be the reference G / B ratio. In the embodiment of the present invention, the G / B ratio is used as the white balance. The white balance (G / B ratio) of the captured image may be calculated by the CDS / AGC circuit 27 (S18).
Then, the aforementioned G / B ratio calculated when the center emission wavelength of the blue laser light source is λ ₁ is stored in the fluorescence characteristic storage unit 29 of the endoscope 11 as a reference G / B ratio in the image sensor. (S20).

Next, the light source control unit 40 is operated to gradually decrease the excitation light amount. When the excitation light amount decreases, the white balance of the captured image deteriorates because the ratio of the emission light amount to the excitation light amount in the phosphor 20 is not constant. As described above, in practice, when the excitation light amount is reduced, the proportion of excitation light that passes through the phosphor decreases, and the light amount of the B light component becomes insufficient.
Specifically, in the control unit 50, the deterioration of the white balance of the captured image signal calculated by the image processing unit 52, here, the deterioration of the G / B ratio, is plotted in the control unit 50 with respect to the drive current value for driving the blue laser light source 42. And stored in the fluorescence characteristic storage unit 29 of the endoscope 11 as described above. As described above, since the ratio of the G light component and the R light component to the B light component does not change, the G / B ratio is used here as the white balance.
Therefore, in the fluorescence characteristic storage unit 29, information on the graph of FIG. 6A showing that the G / B ratio increases as the excitation light quantity decreases as the characteristic of the phosphor 20 unique to the endoscope 11 is shown. Stored (S22).

Next, the reference light source device is adjusted so that the center emission wavelength λ ₁ of the excitation light from the blue laser light source 42 is shifted to the short wavelength side by Δλ (for example, 10 nm). The wavelength variation Δλ here is the maximum deviation width that can be assumed within a predetermined variation range of the blue laser light source 42 and the blue-violet laser light source 44 of the light source device 12 as described above (S24).
The above steps S16, S18, and S22 are repeated by setting the center emission wavelength of the excitation light from the blue laser light source 42 to λ ₁ −Δλ. As a result, a graph in which the G / B ratio changes as the excitation light amount of the blue laser light source 42 decreases when the central emission wavelength is λ ₁ −Δλ shown in FIG. 6B is calculated. 29 (S26).

Next, the reference light source device is adjusted so that the central emission wavelength λ ₁ of the excitation light from the blue laser light source 42 is shifted by Δλ (for example, 10 nm) to the long wavelength side (S 28).
Steps S16, S18, and S22 are repeated in the same manner as described above, assuming that the center emission wavelength of the excitation light from the blue laser light source 42 is λ ₁ + Δλ. As a result, a graph in which the G / B ratio changes as the excitation light quantity of the blue laser light source 42 decreases in the case where the center emission wavelength is λ ₁ + Δλ shown in FIG. 6B is calculated. (S30).

The blue violet laser light source 44 operating as an additional laser light source is also subjected to the same processing as described above.
By operating the reference light source device, the center emission wavelength of the blue-violet laser light source 44 is adjusted to λ ₀ (for example, 405 nm), and steps S16 to S28 are repeated except for step S20 (S32).
By this step S32, as in the case of the blue laser light source 42, as shown in FIG. 6C, when the center emission wavelength of the blue-violet laser light source 44 is λ _0, and λ ₀ −Δλ, λ ₀ For each of the cases where + Δλ is set, a graph in which the G / B ratio changes as the amount of additional laser light from the blue-violet laser light source 44 decreases is calculated, and the information is stored in the fluorescence characteristic storage unit 29.

  The fluorescence characteristic storage unit 29 performs steps S10 to S32 in FIG. 4 to obtain information on the reference G / B ratio and the blue laser light source 42 as the first fluorescence characteristic of the phosphor 20 unique to the endoscope 11 as shown in FIG. The information of (B) and the information of FIG. 6 (C) for the blue-violet laser light source 44 as the second fluorescence characteristic are stored.

  The endoscope 11 in which the first fluorescent characteristic and the second fluorescent characteristic of the phosphor 20 unique to the endoscope are stored in the fluorescent characteristic storage unit 29 is put on the market, and the blue laser light source 42 and the blue-violet laser light source 44 is connected to the light source device 12 in which the respective central emission wavelengths vary slightly (S34). Variations in the central emission wavelengths of the blue laser light source 42 and the blue-violet laser light source 44 of the light source device 12 are unique to the light source device 12.

  When the endoscope 11, the light source device 12, and the processor 13 are connected to each other, the control unit 50 of the processor device 13 provides information on the central emission wavelengths of the blue laser light source 42 and the blue-violet laser light source 44 of the light source device 12. Is obtained from the light source information storage unit 48, and the first G and B ratios corresponding to the information on the reference G / B ratio and the information on the central emission wavelength are obtained from the fluorescence property storage unit 29 of the endoscope 11. Acquire fluorescence characteristics. Then, the controller 50 determines the excitation light amount from the relationship between the excitation light amount and the G / B ratio shown in FIG. 6B and the relationship between the additional laser light amount and the G / B ratio shown in FIG. Then, the additional laser light quantity required to compensate for the G / B ratio deteriorated as the excitation light quantity decreases is calculated as a correction table 56 that defines the relationship shown in the graph of FIG. It memorize | stores in the part 54 (S34).

  Therefore, in the endoscope apparatus 10 according to the first embodiment of the present invention, the emitted light amount of the blue laser light source 42 and the correction described above, regardless of the light source apparatus 12 connected to the endoscope 11 in the market. By determining the emission light amount of the blue-violet laser light source 44 from the table 56 and adding additional laser light from the blue-violet laser light source 44 based on the determined emission light amount, the G / B ratio is maintained, A captured image in which the reference white balance is maintained can be captured.

  Next, in the endoscope apparatus according to the first embodiment of the present invention, an operation when imaging a subject will be briefly described.

  First, an endoscope insertion portion is inserted into the subject, excitation light is emitted from the blue laser light source 42, excites the phosphor 20 at the endoscope tip 35, and irradiates white light toward the subject. Is done. For example, when the distance between the endoscope tip 35 and the subject is adjusted by the operator and the excitation light amount is adjusted according to the distance, the control unit 50 stores the excitation light amount and the correction information storage unit 54. The amount of additional laser light is calculated from the correction table 56 described above, and a predetermined amount of additional laser light is emitted from the blue-violet laser light source 44. By emitting the calculated additional laser light amount, the endoscope apparatus 10 can acquire a captured image in which the G / B ratio of the captured image is maintained at a reference value.

  In the first embodiment of the present invention, special light observation can be performed in addition to the above-described normal observation using white light. Specifically, by increasing the amount of additional laser light emitted from the blue-violet laser light source 44, which is the second light source, by a predetermined amount as compared to the normal observation described above, the captured image is present on the subject surface without darkening the image. It is possible to acquire a superficial blood vessel emphasized image in which superficial blood vessels are emphasized.

  In the first embodiment of the present invention, the wavelength band of the additional laser light that is the light from the second light source is on the shorter wavelength side than the wavelength band of the excitation light that is the light from the first light source. Although the case has been described, the wavelength band of the additional laser light may be on the longer wavelength side than the wavelength band of the excitation light. In this case, for example, if the additional laser light itself is light of the G light component, the amount of light of the G light component that greatly affects the brightness (luminance value) and color rendering of the captured image increases in the illumination light. In addition, the brightness and color rendering properties of the captured image can be improved.

  The above is the endoscope apparatus according to the first embodiment of the present invention. Next, a second embodiment of the present invention will be described.

As shown in FIG. 7, the difference in configuration between the first embodiment and the second embodiment is that the first embodiment has two lamps, a blue laser light source (LD1) 42 and a blue-violet laser light source (LD2) 44. In contrast, the second embodiment has a configuration in which one of the blue laser light source (LD1) 42 is used, and the control unit 50 is directly connected to the CDS. The AGC circuit 27 is directly controlled to adjust the white balance gain.
The white balance gain can be adjusted in the same manner in the image processing unit 52 that has acquired the captured image signal, in addition to the control unit 50 controlling the CDS / AGC circuit.

  In the second embodiment of the present invention, the gain multiplied by the B light component (B light image signal) in the captured image signal in order to maintain the excitation light amount from the blue laser light source 42 and the reference G / B ratio of the captured image. The operation of creating the correction table 56 showing the relationship with (B gain) and storing it in the correction information storage unit 54 will be described based on the flowchart of FIG.

  Also in the second embodiment, as in the first embodiment, the R light component, which is mainly fluorescent light, and the G light component change at a substantially constant rate with respect to the B light component, which is mainly excitation light. Therefore, the G / B ratio, which is the ratio of the signal intensity of the G light component and the B light component, is used as the white balance described above, and the G / B ratio is determined by adjusting the B light image signal with the B gain. Value can be maintained.

  Steps S110 to S130 in FIG. 8 are the same as steps S10 to S30 in the first embodiment of the present invention, and thus description thereof is omitted. The reference G / B ratio is calculated by a series of steps, and the graph of FIG. 9A showing the change in the G / B ratio with respect to the central emission wavelength and the excitation light quantity for each wavelength variation is the first fluorescence characteristic. And the information is stored in the fluorescence characteristic storage unit 29.

  The endoscope 11 having the reference G / B ratio information stored in the fluorescence characteristic storage unit 29 and the first fluorescence characteristic of the phosphor 20 specific to the endoscope 11 is put on the market, and the blue laser light source 42 is connected to the light source device 12 having a slight variation in the center emission wavelength (S130). The variation in the center emission wavelength of the blue laser light source 42 of the light source device 12 is unique to the light source device 12.

  When the endoscope 11, the light source device 12, and the processor 13 are connected to each other, the control unit 50 of the processor device 13 acquires information on the center emission wavelength of the blue laser light source 42 of the light source device 12 from the light source information storage unit 48. Then, the reference G / B ratio information and the first fluorescence characteristic corresponding to the center emission wavelength information are acquired from the fluorescence characteristic storage unit 29 of the endoscope 11. Then, the control unit 50 maintains the excitation light amount and the G / B ratio of the captured image signal at the reference G / B ratio from the relationship between the excitation light amount and the G / B ratio shown in FIG. The gain (B gain) for the B light component of the captured image signal necessary for the calculation is calculated as the correction table 56 that defines the relationship shown in the graph of FIG. 9B, and stored in the correction information storage unit 54 (S132). .

  Therefore, in the endoscope apparatus 10 according to the second embodiment of the present invention, the emitted light amount of the blue laser light source 42 and the correction described above, regardless of the light source apparatus 12 connected to the endoscope 11 in the market. A gain (B gain) with respect to the B light component of the captured image signal is determined from the table 56, and the G / B ratio is maintained by multiplying the captured image signal output from the image sensor by the above-described B gain. The captured image in which the white balance is maintained can be captured.

  Next, in the endoscope apparatus according to the second embodiment of the present invention, an operation when imaging a subject will be briefly described.

First, an endoscope insertion portion is inserted into the subject, excitation light is emitted from the blue laser light source 42, excites the phosphor 20 at the endoscope tip 35, and irradiates white light toward the subject. Is done. For example, when the distance between the endoscope tip 35 and the subject is adjusted by the operator and the excitation light amount is adjusted according to the distance, the control unit 50 stores the excitation light amount and the correction information storage unit 54. A necessary B gain is calculated from the correction table 56 described above.
The endoscope apparatus 10 maintains the G / B ratio by multiplying the B light image signal (B light image component) of the captured image signal acquired by the image sensor 26 by the calculated B gain. The captured image in which the reference white balance is maintained can be acquired.

  The above is the endoscope apparatus according to the second embodiment of the present invention.

The present invention also provides:
A first light source that emits a first narrowband light having a first wavelength band, a second light source that emits a second narrowband light having a second wavelength band different from the first wavelength band, And a phosphor that is excited by the first narrow-band light functioning as excitation light and generates first fluorescent light having a broad wavelength, and illuminates a subject from at least the excitation light and the first fluorescent light A light source device for generating illumination light;
An endoscope that integrally incorporates the phosphor;
Storage means for storing a change in color of the illumination light with respect to an increase or decrease in the excitation light;
Correction means for correcting a color change of the illumination light by mixing the second narrowband light from the second light source into the excitation light and the first fluorescent light, and
The correction means includes, as correction data, the mixing amount data of the second narrowband light for correcting the color change of the illumination light for each endoscope.
The storage means stores the first sensitivity of the phosphor due to the amount of the excitation light of the first light source and the second sensitivity of the phosphor due to the excitation wavelength variation of the excitation light,
The correction means provides an endoscope apparatus that calculates the correction data based on the first and second sensitivities of the phosphors stored in the storage means.

The second narrowband light of the second light source also excites the phosphor to generate a second fluorescent light having a wideband wavelength.
The storage means further stores a third sensitivity of the phosphor due to a wavelength variation of the second narrowband light of the second light source,
The correction means calculates the correction data based on the first, second and third sensitivities of the phosphor stored in the storage means,
The light source device combines the excitation light, the first fluorescent light, and the second narrowband light and the second fluorescent light mixed therein to illuminate the subject. Is preferably generated.

Here, the second narrowband light mixing amount data for correcting the color change of the illumination light, which is the correction data described above, is the correction table 56 in the first embodiment described above.
Further, the first sensitivity is the G / B ratio with respect to the excitation light amount shown in FIG. 6A, and the second sensitivity is the influence of the wavelength variation ± Δλ of the excitation light shown in FIG. 6B. G / B ratio with respect to the excitation light quantity considered, and the first sensitivity and the second sensitivity are included in the first fluorescence characteristic.
The third sensitivity is the G / B ratio with respect to the additional laser light amount in consideration of the influence of the wavelength variation ± Δλ of the additional laser light shown in FIG. 6C, and is included in the second fluorescence characteristic.

  Although the endoscope apparatus of the present invention has been described in detail above, 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. Good.

DESCRIPTION OF SYMBOLS 10 Endoscope apparatus 11 Endoscope 12 Light source apparatus 13 Processor apparatus 15 Display part 17 Input part 18 Optical fiber 19 Endoscope insertion part 20 Phosphor 21 Irradiation port 22 Angle knob 23 Operation part 24 Objective lens unit 25A, 25B Connector Unit 26 Imaging device 27 CDS / AGC circuit 28 A / D converter 29 Fluorescence characteristic storage unit 31 Flexible unit 33 Bending unit 35 Tip unit 40 Light source control unit 42 Blue laser light source (excitation light source)
44 Blue-violet laser light source (additional laser light source)
46 multiplexing unit 48 light source information storage unit 50 control unit 52 image processing unit 54 correction information storage unit 56 correction table

Claims (10)

A first light source that emits a first narrowband light having a narrowed first wavelength;
A second light source that emits a second narrowband light having a narrowed second wavelength, different from the first light source, and the first narrowband light from the first light source. A light source information storage unit for storing the first wavelength;
The first wavelength is within a predetermined variation range with respect to the first central emission wavelength of the first light source; and
The first narrowband light that is transmitted through at least a part of the first narrowband light and is excited by the first narrowband light that functions as excitation light, has a wavelength band different from the first wavelength that is an excitation wavelength. A phosphor that emits fluorescent light, and whose fluorescence characteristics change according to a variation in the excitation wavelength with respect to the amount of light emitted from the first narrowband light and the first central emission wavelength;
A fluorescence characteristic storage unit that stores the first fluorescence characteristic of the phosphor that changes in response to fluctuations in the amount of emission light and the excitation wavelength; and the excitation light that has passed through the phosphor and the light emitted from the phosphor The illumination from the subject irradiated with the light mixed with the first fluorescent light or the light mixed with the excitation light, the first fluorescent light, and the second narrowband light as illumination light An endoscope that includes an imaging unit that performs imaging with return light of light and outputs the captured image signal;
The excitation wavelength is read from the light source information storage unit of the light source device, and the emission light amount of the excitation light having the read excitation wavelength and the fluctuation of the excitation wavelength are read from the fluorescence characteristic storage unit of the endoscope. The first fluorescence characteristic of the phosphor is read out, and from the read first fluorescence characteristic, the excitation light from the first light source is maintained so that the captured image signal maintains a reference white balance. The amount of light emitted from the second light source added to the amount of light emitted from the second narrowband light is calculated, and the second amount of light emitted from the second narrowband light is calculated so as to be calculated. A processor device having a control unit for controlling the light source;
An endoscope apparatus comprising: The second wavelength of the second narrowband light from the second light source of the light source device falls within a predetermined fluctuation range with respect to a second central emission wavelength of the second light source. Yes,
The light source information storage unit further stores the second wavelength of the second narrowband light from the second light source,
The phosphor further transmits at least a part of the second narrowband light and is excited by the second narrowband light to emit second fluorescent light having a wavelength band different from the second wavelength. , And the fluorescence characteristics change according to the fluctuation of the second wavelength with respect to the second central emission wavelength,
The fluorescence characteristic storage unit further stores a second fluorescence characteristic of the phosphor that changes with respect to a variation in the second wavelength of the second narrowband light,
The endoscope uses light obtained by mixing the excitation light and the first fluorescent light, and the second narrowband light and the second fluorescent light as the illumination light,
The control unit of the processor device further reads the second wavelength from the light source information storage unit of the light source device, and further reads the second wavelength read from the fluorescence characteristic storage unit of the endoscope. The second fluorescence characteristic of the phosphor with respect to wavelength variation is read out, and the captured image signal maintains a reference white balance from the read first and second fluorescence characteristics of the phosphor. The amount of light emitted from the second light source is added to the amount of light emitted from the first narrow-band light from the first light source, and the amount of light emitted from the second light source is calculated. The endoscope apparatus according to claim 1, wherein the second light source is controlled to emit light of two narrowband lights.   The endoscope apparatus according to claim 1, wherein the fluorescent characteristic includes a light emission amount of the fluorescent light. Furthermore, the processor device corrects the correspondence between the amount of light emitted from the first light source and the amount of light emitted from the second light source necessary for the captured image signal to maintain a reference white balance. A correction information storage unit for storing the table;
When the light source device, the endoscope, and the processor device are connected to each other in the market, an endoscope device is configured.
The controller is
The first wavelength and the second wavelength stored in the light source information storage unit of the light source device, and the first fluorescence characteristic of the phosphor stored in the fluorescence characteristic storage unit of the endoscope And the second fluorescence characteristic, create the correction table, and store in the correction information storage unit,
Obtaining a necessary amount of emitted light of the second light source from the correction table and the amount of emitted light of the first light source, and controlling the amount of emitted light of the second light source based on the necessary amount of emitted light; The endoscope apparatus according to any one of claims 1 to 3.   The reference white balance is a white balance of the captured image signal when the emission from the second light source is stopped and the amount of light emitted from the first light source is maximized. The endoscope apparatus described in 1.   The endoscope apparatus according to claim 1, wherein a wavelength band of the second narrowband light is on a shorter wavelength side than a wavelength band of the first narrowband light.   The first light source is a blue laser light source having a first wavelength in a range of 445 ± 10 nm, and the second light source is a blue-violet laser light source having a second wavelength in a range of 405 ± 10 nm. The endoscope apparatus according to claim 6.   The endoscope apparatus according to claim 1, wherein a wavelength band of the second narrowband light is on a longer wavelength side than a wavelength band of the first narrowband light.   The endoscope apparatus according to claim 1, wherein a G / B ratio that is a ratio of a green light component and a blue light component of the captured image signal is used as the white balance.   The endoscope apparatus according to claim 1, wherein the illumination light is pseudo white light including a red light component, a green light component, and a blue light component in a predetermined wavelength band.

Images