JP6245710B2 - Endoscope system and operating method thereof - Google Patents

Description

  The present invention relates to an endoscope system that enables narrow-band light observation and an operating method thereof.

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

  As an observation method used in an endoscope system, in addition to normal light observation using ordinary light (white light) having a wide wavelength range as illumination light, special light (narrow band light) having a narrow wavelength range is used as illumination light. Narrow-band light observation is known. The narrow-band light observation can be displayed with improved visibility of the state of blood vessel running on the surface of the mucosa, which is easily buried with optical information obtained in the case of white light, for example. For this reason, in narrow-band light observation, attention can be paid to the superficial blood vessel even during blood vessel running, and the degree of progression of the lesioned part, the depth of the depth direction, and the like can be determined according to the form of the superficial blood vessel.

  In this narrow-band light observation, two narrow-band lights (blue narrow-band light having a center wavelength near 415 nm and green narrow-band light having a center wavelength near 540 nm) that are easily absorbed by hemoglobin in blood are used. Yes. As an imaging method in narrowband light observation, in addition to a surface sequential method of alternately illuminating blue narrowband light and green narrowband light and using a monochrome imaging device for each narrowband light irradiation, A simultaneous method is known in which blue narrow-band light and green narrow-band light are simultaneously irradiated and imaged with a simultaneous imaging device having a color filter (see Patent Documents 1 and 2). The simultaneous method has a lower resolution than the frame sequential method, but has the advantage that the image is less likely to be blurred and the configuration of the endoscope system is simplified.

  The simultaneous image sensor includes a primary color image sensor having a primary color filter and a complementary color image sensor having a complementary color filter. The primary color image sensor is inferior in sensitivity to the complementary color image sensor, but has excellent color reproducibility, and is therefore used in an endoscope system that places importance on color. On the other hand, the complementary color image pickup device is used in an endoscope system in which sensitivity is important because it has a high sensitivity although color reproducibility is inferior to a primary color image pickup device. Therefore, since the primary color image sensor and the complementary color image sensor are each pros and cons, future endoscope systems will be used in a primary color endoscope incorporating a primary color image sensor and a complementary color image sensor incorporating a complementary color image sensor. There is a need for an endoscope system that can be connected to both endoscopes.

  Patent Documents 1 and 2 show complementary color checkered color difference line sequential systems having four types of pixels of magenta (Mg), green (G), cyan (Cy), and yellow (Ye) as complementary color imaging devices. Has been. In this complementary color checkered color difference line sequential method, pixel signals of two adjacent rows are mixed (added) and read by field reading. Specifically, it is read out by four combinations of Mg pixel and Cy pixel, G pixel and Ye pixel, Mg pixel and Ye pixel, G pixel and Cy pixel. This complementary checkered color difference line sequential method has an advantage that Y / C signals and RGB signals can be easily generated simply by performing addition / subtraction based on the signals of four types of mixed pixels.

Japanese Patent No. 4009626 Japanese Patent No. 4847250

  When performing narrow-band light observation with the endoscope system described above, in the primary color imaging device, blue narrow-band light and green narrow-band light are individually captured by blue (B) pixels and green (G) pixels, respectively. Therefore, an image having good color separation and excellent visibility of the superficial blood vessel (contrast between the superficial blood vessel and the mucous membrane) can be obtained. On the other hand, in the complementary color imaging device, two narrowband lights of blue narrowband light and green narrowband light are sensed simultaneously by each mixed pixel (that is, color mixing occurs), so that color separation is poor. There is a problem in that the visibility of the superficial blood vessels decreases due to the superficial blood vessels being blurred by the influence of scattered light.

  Further, as shown in Patent Document 2 (FIGS. 19 and 21), if the spectral sensitivity of the pixels varies, the amount of the color mixture component varies, and therefore it is impossible to perform color mixture correction uniformly by an optical method. Have difficulty.

  Further, even in the primary color image sensor, when each pixel has sensitivity to both of two narrow band lights used in narrow band light observation, as in the case of a complementary color image sensor, color separation and There is a problem that the visibility of the superficial blood vessels is lowered.

  It is an object of the present invention to provide an endoscope system and an operating method thereof that can improve color separation and surface blood vessel visibility in narrow-band light observation.

ここで、β _１１ 〜β _２３ の６個の係数は、それぞれ０以上１以下の値であり、係数β _１１ 及びβ _２２ は、その他の係数より大きな値に設定されている。

ここで、Ｋ₁は、第１狭帯域光のみを独立照射した場合における第１表示用信号に対する第２表示用信号の信号値の比を表す第１補正係数であり、Ｋ₂は、第２狭帯域光のみを独立照射した場合における第２表示用信号に対する第１表示用信号の信号値の比を表す第２補正係数である。 In order to achieve the above object, an endoscope system according to the present invention includes a first narrowband light having a center wavelength in a blue or violet wavelength range and a second narrowband having a center wavelength in a green wavelength range. A light source device that simultaneously generates light, and a primary color separation filter composed of red, green, and blue color filter segments. The red pixel signal R is read from the red pixel, and the green pixel signal G is read from the green pixel. Is read out, and the primary pixel imaging device from which the blue pixel signal B is read out from the blue pixel , the red pixel signal R, the green pixel signal G, and the blue pixel signal B are subjected to matrix calculation based on the following equation (a). The matrix calculation unit for generating the first and second display signals D1, D2 and the first and second display signals D1, D2 are corrected based on the following equation (b). And a color mixing corrector.

Here, the six coefficients of β ₁₁ ~β ₂₃ are each 0 or 1 or less, the coefficient beta ₁₁ and beta ₂₂ is set to a value greater than other coefficients.

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is the second correction coefficient. It is a 2nd correction coefficient showing the ratio of the signal value of the 1st display signal to the 2nd display signal at the time of carrying out independent irradiation only of narrow-band light.

First and second correction coefficients K ₁ and K ₂ are calculated based on the signal values of the first and second display signals obtained by independently irradiating the first and second narrowband lights from the light source device, respectively. It is preferable to provide a correction coefficient acquisition unit to be obtained.

In the formula (a), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, and D1 = B and D2 = G may be satisfied.

The light source device, a primary color-type endoscope having a primary color system imaging device, and the complementary endoscope having a complementary color system imaging device preferably connected detachably.

  Each of the complementary color type endoscope and the primary color type endoscope has an information storage unit that stores unique information, and reads out the unique information from the information storage unit of the endoscope connected to the light source device. It is preferable to provide a control unit for determining the type of mirror.

The information storage unit stores the first and second correction coefficients K ₁ and K ₂ , and the control unit stores information when a complementary color type endoscope or a primary color type endoscope is connected to the light source device. It is preferable that the first and second correction coefficients K ₁ and K ₂ are read from the unit and input to the color mixture correction unit.

ここで、β _１１ 〜β _２３ の６個の係数は、それぞれ０以上１以下の値であり、係数β _１１ 及びβ _２２ は、その他の係数より大きな値に設定されている。

ここで、Ｋ₁は、第１狭帯域光のみを独立照射した場合における第１表示用信号に対する第２表示用信号の信号値の比を表す第１補正係数であり、Ｋ₂は、第２狭帯域光のみを独立照射した場合における第２表示用信号に対する第１表示用信号の信号値の比を表す第２補正係数であり、Ｒ₁は、第１表示用信号の補正後の信号値Ｄ１’中の第２狭帯域光成分の割合を表す第１混色率であり、Ｒ₂は、第２表示用信号の補正後の信号値Ｄ２’中の第１狭帯域光成分の割合を表す第２混色率である。 The endoscope system of the present invention simultaneously generates first narrowband light having a center wavelength in the blue or violet wavelength region and second narrowband light having the center wavelength in the green wavelength region. A light source device and a primary color separation filter composed of red, green, and blue color filter segments. The red pixel signal R is read from the red pixel, the green pixel signal G is read from the green pixel, and blue A primary color image pickup device from which a blue pixel signal B is read out from a pixel , a red pixel signal R, a green pixel signal G, and a blue pixel signal B are subjected to matrix calculation based on the following equation (c), and first and second A matrix calculation unit that generates display signals D1 and D2 and a color mixture correction unit that corrects the first and second display signals D1 and D2 based on the following equation (d). .

Here, the six coefficients of β ₁₁ ~β ₂₃ are each 0 or 1 or less, the coefficient beta ₁₁ and beta ₂₂ is set to a value greater than other coefficients.

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is the second correction coefficient. R 2 is a second correction coefficient that represents the ratio of the signal value of the first display signal to the second display signal when only narrow-band light is irradiated independently, and R ₁ is the signal value after correction of the first display signal D1 'is a first color mixing ratio which represents a ratio of the second narrowband light components in, R ₂ is the signal value D2 corrected in the second display signal' represents the ratio of the first narrowband light components in This is the second color mixing ratio.

The light source device, a primary color-type endoscope having a primary color system imaging device, and the complementary endoscope having a complementary color system imaging device is detachably connected, complementary endoscope and primary endoscope, Each of the information storage units stores the first and second color mixing ratios R ₁ and R _{2. When the} complementary color type endoscope or the primary color image sensor is connected to the light source device, the information storage unit stores the first and second color mixing ratios R ₁ and R ₂ . It is preferable to provide a control unit that reads out the first and second color mixing ratios R ₁ and R ₂ and inputs them to the color mixing correction unit.

A structure enhancement processing unit that performs blood vessel enhancement processing on images based on the signal values D1 ′ and D2 ′ is provided, and the structure enhancement processing unit increases the degree of enhancement of the surface blood vessel portion as the first color mixing ratio R ₁ increases. It is preferable. In the formula (c), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, and D1 = B and D2 = G may be satisfied.

ここで、Ｋ₁は、第１狭帯域光のみを独立照射した場合における第１表示用信号に対する第２表示用信号の信号値の比を表す第１補正係数であり、Ｋ₂は、第２狭帯域光のみを独立照射した場合における第２表示用信号に対する第１表示用信号の信号値の比を表す第２補正係数である。 In addition, according to the operation method of the endoscope system of the present invention, the light source device includes a first narrowband light having a center wavelength in the blue or violet wavelength range and a second narrowband having the center wavelength in the green wavelength range. A primary color imaging device having a step of simultaneously generating band light and a primary color separation filter composed of red, green, and blue color filter segments outputs a red pixel signal R from the red pixel and green from the green pixel; The step of outputting the pixel signal G and outputting the blue pixel signal B from the blue pixel, and the matrix calculation unit, the red pixel signal R, the green pixel signal G, and the blue pixel signal B based on the following equation (e) The matrix calculation to generate the first and second display signals D1 and D2, and the color mixture correction unit converts the first and second display signals D1 and D2 And a step of correcting, based on the following equation (f).

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is the second correction coefficient. It is a 2nd correction coefficient showing the ratio of the signal value of the 1st display signal to the 2nd display signal at the time of carrying out independent irradiation only of narrow-band light.

In the equation (e), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, and D1 = B and D2 = G may be used.

  According to the present invention, first and second display signals D1 and D2 are generated by performing matrix calculation on signal values from a plurality of types of pixels sensitive to both the first and second narrowband lights, Since the second display signals D1 and D2 are subjected to color mixing correction, color separation and surface blood vessel visibility are improved in narrowband light observation.

It is an external view of an endoscope system. It is a block diagram which shows the internal structure of an endoscope system. It is a graph which shows the emission spectrum of purple narrow-band light. It is a graph which shows the emission spectrum of normal light. It is a figure explaining the structure of a multiplexing part. It is a graph which shows the emission spectrum of green narrow-band light. It is a schematic diagram which shows a complementary color system color separation filter. It is a schematic diagram which shows a primary color system color separation filter. It is a figure which shows the drive timing of the light source and complementary color type image pick-up element at the time of narrow band light observation mode. It is a figure which shows the output signal from a complementary color type image pick-up element. It is a graph which illustrates the spectral sensitivity characteristic of a complementary color system image sensor. It is a graph which illustrates the spectral sensitivity characteristic of the 1st-the 4th mixed pixel. It is a block diagram which shows the structure of the 1st process part for complementary colors. It is a figure which shows the drive timing of the light source and complementary color type image sensor in a calibration mode. It is a flowchart explaining the effect | action of an endoscope system. It is a figure explaining the color mixing correction process of the 1st and 2nd mixing pixel signal according to the 1st and 2nd color mixing rate. It is a block diagram which shows the structure of the 1st process part for complementary colors which has a structure enhancement process part. It is a graph which shows the emission spectrum of blue narrow-band light. It is a schematic diagram which shows the modification of a complementary color type | system | group color separation filter.

[First Embodiment]
In FIG. 1, an endoscope system 10 includes a light source device 11, a processor device 12, and an electronic endoscope (hereinafter simply referred to as an endoscope) 13 that can be detachably connected to the light source device 11 and the processor device 12. It is configured. The light source device 11 generates illumination light and supplies it to the endoscope 13. The endoscope 13 is inserted into the body cavity or the like of the specimen to image the inside of the body cavity. The processor device 12 controls the imaging of the endoscope 13 and performs signal processing on the imaging signal acquired by the endoscope 13.

  An image display device 14 and an input device 15 are connected to the processor device 12. The image display device 14 is a liquid crystal monitor or the like, and displays a sample image representing an image in the sample generated by the processor device 12. The input device 15 includes a keyboard and a mouse, and inputs various information to the processor device 12.

  The endoscope 13 includes a complementary color endoscope 13a including a complementary color imaging device 28 (see FIG. 2) and a primary color endoscope 13b including a primary color imaging device 29 (see FIG. 2). The light source device 11 and the processor device 12 can be connected. The complementary color endoscope 13a and the primary color endoscope 13b have the same configuration except for the image sensor, and the insertion portion 16, the operation portion 17, the universal cable 18, the light guide connector 19a, and the signal connector 19b. It is comprised by.

  The insertion portion 16 is elongated and inserted into the body cavity of the specimen. The operation unit 17 is connected to the rear end of the insertion unit 16 and is provided with a scope switch, a bending operation dial, and the like. The scope switch includes a mode switch 17a for switching the observation mode.

  The universal cable 18 extends from the operation unit 17. The light guide connector 19 a and the signal connector 19 b are provided at the end of the universal cable 18. The light guide connector 19a is detachably connected to the light source device 11. The signal connector 19b is detachably connected to the processor device 12.

  The endoscope system 10 has a normal light observation mode and a narrow-band light observation mode as observation modes. In the normal light observation mode, imaging is performed by irradiating the specimen with normal light (white light) whose wavelength range extends from the blue band to the red band, and a normal light image is generated. In the narrowband light observation mode, imaging is performed by irradiating the specimen with narrowband light (purple narrowband light Vn and green narrowband light Gn, which will be described later) having a narrow wavelength range, and a narrowband light image is generated. The normal light observation mode and the narrow-band light observation mode are possible when either the complementary color endoscope 13a or the primary color endoscope 13b is used.

  The normal light observation mode and the narrowband light observation mode can be switched by the mode switch 17a described above, but are provided on a foot switch (not shown) that can be connected to the processor device 12 or on the front panel of the processor device 12. It may be possible to switch between the buttons, the input device 15 and the like.

  In FIG. 2, the light source device 11 includes a plurality of LED (Light Emitting Diode) light sources 20, a light source control unit 21, and a multiplexing unit 24. The LED light source 20 includes a purple LED (V-LED) 20a and a white LED (WL-LED) 20b. The V-LED 20a generates purple narrowband light Vn having a light intensity spectrum as shown in FIG. 3 and having a wavelength range of 380 to 440 nm and a center wavelength of about 405 nm. The WL-LED 20b generates white light WL in a wide wavelength region having a light intensity spectrum as shown in FIG. The light source control unit 21 performs light emission control of the V-LED 20a and the WL-LED 20b.

  As illustrated in FIG. 5, the multiplexing unit 24 includes a dichroic mirror 22 and first to third lenses 23 a to 23 c. The first and second lenses 23a and 23b are disposed corresponding to the LEDs 20a and 20b, respectively, and condense the light emitted from the LEDs 20a and 20b into parallel light. The V-LED 20a and the WL-LED 20b are disposed so that their optical axes are orthogonal to each other, and a dichroic mirror 22 is disposed at the intersection of the optical axes.

  The dichroic mirror 22 has an optical characteristic of transmitting light in a wavelength region of, for example, 530 nm or more and less than 550 nm and reflecting light in a wavelength region of less than 530 nm or 550 nm or more. Therefore, the purple narrow band light Vn is reflected by the dichroic mirror 22 and collected by the third lens 23c. One part of the white light WL passes through the dichroic mirror 22, and as shown in FIG. 6, the third lens 23c becomes green narrowband light Gn having a wavelength range of 530 to 550 nm and a center wavelength of about 540 nm. It is condensed by.

  In the narrow-band light observation mode, the V-LED 20a and the WL-LED 20b are turned on at the same time, and the purple narrow-band light Vn and the green narrow-band light Gn are combined by the dichroic mirror 22 and condensed by the third lens 23c. Incident on the guide 27.

  In the normal light observation mode, the dichroic mirror 22 is moved outside the optical axis of the WL-LED 20b by a moving mechanism (not shown). Accordingly, in the normal light observation mode, the white light WL is directly incident on the third lens 23 c and supplied to the light guide 27. In the normal light observation mode, since the dichroic mirror 22 is retracted, the purple narrowband light Vn emitted from the V-LED 20a does not enter the third lens 23c even if it is reflected by the dichroic mirror 22. For this reason, in the normal light observation mode, the V-LED 20a may be either lit or not lit.

  The purple narrow band light Vn has a center wavelength of about 405 nm, and has a high hemoglobin absorption coefficient in the visible light region. The green narrow band light Gn has a center wavelength of about 540 nm, and has a high hemoglobin absorption coefficient in the green light wavelength region. Further, the green narrow band light Gn has a characteristic that the reflectance at the mucous membrane is higher than that of the purple narrow band light Vn.

  An illumination window and an observation window are provided adjacent to each other at the distal end of the insertion portion 16 of the endoscope 13, an illumination lens 25 is attached to the illumination window, and an objective lens 26 is attached to the observation window. Yes. A light guide 27 is inserted into the endoscope 13, and one end of the light guide 27 faces the illumination lens 25. The other end of the light guide 27 is disposed on the light guide connector 19 a and is inserted into the light source device 11.

  The illumination lens 25 is incident on the light guide 27 from the light source device 11, collects the light emitted from the light guide 27, and irradiates the sample. The objective lens 26 collects the reflected light from the biological tissue of the specimen and forms an optical image. At the imaging position of the objective lens 26, an image pickup device that picks up an optical image and generates an image pickup signal (in the case of the complementary color type endoscope 13a, the complementary color type image pickup device 28, in the case of the primary color type endoscope 13b). A primary color image sensor 29) is arranged. The complementary color image sensor 28 and the primary color image sensor 29 are CCD (Charge Coupled Device) image sensors.

  A complementary color system color separation filter 28 a that optically separates an optical image for each pixel is provided on the imaging surface of the complementary color image sensor 28. As shown in FIG. 7, the complementary color separation filter 28a has four color filter segments of magenta (Mg), green (G), cyan (Cy), and yellow (Ye). Are attached in pixel units. Therefore, the complementary color image sensor 28 has four kinds of pixels of Mg, G, Cy, and Ye, and odd-numbered columns are arranged in the order of Mg pixels, Cy pixels, Mg pixels, Ye pixels,. , G pixel, Ye pixel, G pixel, Cy pixel,..., Mg pixels and G pixels are alternately arranged in odd rows, and Cy pixels and Ye pixels are alternately arranged in even rows. Has been placed. This color filter array is called a complementary color checkered color difference line sequential method.

  A primary color separation filter 29 a is provided on the imaging surface of the primary color imaging device 29. As shown in FIG. 8, the primary color separation filter 29a has three types of color filter segments, red (R), green (G), and blue (B). Each color filter segment is attached in units of pixels. It has been. Therefore, the primary color image pickup device 29 has three types of pixels of R, G, and B, G pixels and B pixels are alternately arranged in odd columns, and R pixels and G pixels are alternately arranged in even columns. G pixels and R pixels are alternately arranged in odd rows, and B pixels and G pixels are alternately arranged in even rows. This color filter array is called a primary color Bayer system.

  The endoscope 13 is provided with an information storage unit 30 composed of a nonvolatile memory such as a flash memory. The information storage unit 30 stores unique information of the endoscope 13 (color filter array of the image sensor, number of pixels, correction coefficient described later), and the like.

  The processor device 12 includes a control unit 31, an imaging control unit 32, a correlated double sampling (CDS) circuit 33, an A / D conversion circuit 34, a brightness detection circuit 35, a dimming circuit 36, and signal processing. Unit 37 and channel allocation unit 38.

  The control unit 31 controls each unit in the processor device 12 and the light source device 11. When the endoscope 13 is connected to the light source device 11 and the processor device 12, the control unit 31 reads the unique information of the endoscope 13 from the information storage unit 30, and the connected endoscope 13 It is determined whether the endoscope 13a or the primary color endoscope 13b. The imaging control unit 32 drives the imaging device (the complementary color imaging device 28 or the primary color imaging device 29) according to the type of the endoscope 13 determined by the control unit 31.

  In the case of the complementary color imaging device 28, the imaging control unit 32 drives the complementary color imaging device 28 by the field readout method in accordance with the light emission timing of the light source device 11. Specifically, in the field readout method, at the time of each readout of the odd field and the even field, two pixels adjacent in the column direction are mixed (added) and read out (see FIG. 7). . This mixing of pixel signals is performed in a horizontal transfer path (not shown) of the CCD image sensor. FIG. 9 shows the drive timing in the narrow-band light observation mode. The drive timing in the normal light observation mode is the same as in the narrow-band light observation mode except that the illumination light is white light WL.

  With this field readout method, the complementary color image sensor 28 has mixed pixel signals (hereinafter referred to as first mixed pixel signals) of Mg pixels and Cy pixels as shown in FIG. 10 in each of the odd field and the even field. ) M1, a mixed pixel signal of G pixel and Ye pixel (hereinafter referred to as a second mixed pixel signal) M2, a mixed pixel signal of Mg pixel and Ye pixel (hereinafter referred to as a third mixed pixel signal) M3, A mixed pixel signal (hereinafter referred to as a fourth mixed pixel signal) M4 of the G pixel and the Cy pixel is output.

  Since each pixel of the complementary color image sensor 28 has, for example, the spectral sensitivity characteristic shown in FIG. 11 according to the color filter segment, each mixed pixel has the spectral sensitivity characteristic shown in FIG. 12, for example. According to this spectral sensitivity characteristic, among the first to fourth mixed pixels, the first mixed pixel (Mg + Cy) is the most sensitive to the purple narrowband light Vn (center wavelength 405 nm), and the second mixed pixel (G + Ye). ) Is the most sensitive to the green narrowband light Gn (center wavelength 540 nm). However, the first mixed pixel (Mg + Cy) has high sensitivity to the green narrowband light Gn, and the second mixed pixel (G + Ye) has some sensitivity to the purple narrowband light Vn. doing.

  In the case of the primary color imaging device 29, the imaging control unit 32 drives the primary color imaging device 29 by a known progressive readout method in accordance with the light emission timing of the light source device 11. In this progressive readout method, pixel signals are individually read out one frame at a time without mixing pixel signals.

  Signals output from the complementary color image sensor 28 and the primary color image sensor 29 are input to the CDS circuit 33. The CDS circuit 33 performs correlated double sampling on the input signal to remove noise components generated by the CCD image sensor. The signal from which the noise component has been removed by the CDS circuit 33 is input to the A / D conversion circuit 34 and also to the brightness detection circuit 35. The A / D conversion circuit 34 converts the signal input from the CDS circuit 33 into a digital signal and inputs the digital signal to the signal processing unit 37.

  The brightness detection circuit 35 detects brightness (average luminance of the signal) based on the signal input from the CDS circuit 33. The light control circuit 36 generates a light control signal that is a difference between the brightness signal detected by the brightness detection circuit 35 and the reference brightness (target value of light control). This dimming signal is input to the light source control unit 21. The light source control unit 21 adjusts the light emission amounts of the plurality of LED light sources 20 so that the reference brightness is obtained.

  The control unit 31 receives a mode switching signal that is generated when the mode switch 17a of the endoscope 13 is operated, and based on the received mode switching signal, the light emission method of the light source device 11 and the signal processing unit 37. Switch the signal processing method.

  The signal processing unit 37 includes a selector 40, a first complementary color processing unit 41, a second complementary color processing unit 42, a first primary color processing unit 43, a second primary color processing unit 44, and a correction coefficient acquisition unit. 45. The selector 40 selects any one of the processing units 41 to 45 according to the type of the endoscope 13 and the observation mode determined by the control unit 31.

  The first processing unit for complementary color 41 is selected when the type of the endoscope 13 is a complementary color type and the observation mode is the normal light observation mode. The first to fourth mixed pixel signals M <b> 1 to M <b> 4 (see FIG. 10) are input from the complementary color imaging device 28 to the first processing unit 41 for complementary colors. The first complementary color processing unit 41 performs a well-known Y / C conversion used in the complementary color checkered color difference line sequential method to generate the luminance signal Y and the color difference signals Cr and Cb, and further performs the matrix calculation to the luminance signal Y and the color difference. Signals Cr and Cb are converted into RGB signals. The RGB signals are sent to the channel assignment unit 38. Specifically, the luminance signal Y and the color difference signals Cr and Cb are added and subtracted between the first mixed pixel signal M1 and the second mixed pixel signal M2 adjacent in the row direction, and the third mixed pixel signal M3 adjacent in the row direction. And the fourth mixed pixel signal M4.

  The complementary color second processing unit 42 is selected when the type of the endoscope 13 is a complementary color type and the observation mode is the narrow-band light observation mode. As illustrated in FIG. 13, the complementary color second processing unit 42 includes a matrix calculation unit 46, an interpolation processing unit 47, and a color mixture correction unit 48.

  The matrix calculation unit 46 performs a matrix calculation represented by Expression (1) on each set of the first to fourth mixed pixel signals M1 to M4 input from the complementary color image pickup device 28, and performs the first and first. 2 display signals D1 and D2 are generated. Specifically, for example, the matrix calculation is performed with each of the first to fourth mixed pixel signals M1 to M4 having a relative positional relationship illustrated in FIG.

As will be described in detail later, in the narrowband light observation mode, the purple narrowband light Vn is imaged based on the first display signal D1, and the green narrowband light Gn is visualized based on the second display signal D2. Imaging is performed. The eight coefficients α _{11 to} α ₂₄ are set to values of 0 or more and 1 or less, but the first mixed pixel signal M1 among the first to fourth mixed pixel signals M1 to M4 is purple narrowband light Vn. Since the second mixed pixel signal M2 has the highest sensitivity to the green narrowband light Gn, the coefficients α ₁₁ and α ₂₂ are set to values larger than the other coefficients. That is, the first mixed pixel signal M1 is the main signal of the first display signal D1, and the second mixed pixel signal M2 is the main signal of the second display signal D2. For example, α ₁₁ = α ₂₂ = 1, α ₁₂ = α ₁₃ = α ₁₄ = α ₂₁ = α ₂₃ = α ₂₄ = 0 (that is, D1 = M1, D2 = M2) may be set.

  The first and second display signals D1 and D2 generated by the matrix calculation unit 46 are input to the interpolation processing unit 47. The interpolation processing unit 47 performs a known pixel interpolation process, and generates a set of first and second display signals D1 and D2 for each pixel position. The color mixture correction unit 48 performs color mixture correction processing using equation (2).

Here, K ₁ is a ratio (D2v / D1v) of the second display signal D2v to the first display signal D1v obtained when only the purple narrowband light Vn is independently irradiated. K ₂ is a ratio (D1g / D2g) of the first display signal D1g to the second display signal D2g obtained when only the green narrow-band light Gn is independently irradiated.

The endoscope system 10 has a calibration mode for acquiring the correction coefficients K ₁ and K ₂ . This calibration mode can be selected by operating the input device 15 or the like. In this calibration mode, the control unit 31 lights the V-LED 20a and the WL-LED 20b individually with the dichroic mirror 22 arranged at the intersection of the optical axes of the V-LED 20a and the WL-LED 20b. As shown in FIG. 5, the purple narrow band light Vn and the green narrow band light Gn are irradiated in a time-sharing manner, and the complementary color image sensor 28 is driven in accordance with each irradiation timing.

The correction coefficient acquisition unit 45 calculates the aforementioned first display signals D1v and D1g and the second display signals D2g and D2v by matrix calculation based on Expression (1) in the calibration mode, and K ₁ = D2v / D1v, Correction coefficients K ₁ and K ₂ are calculated based on the relational expression of K ₂ = D1g / D2g. The correction coefficients K ₁ and K ₂ are preferably calculated using respective average values of the plurality of first display signals D1v and D1g and the second display signals D2g and D2v. The correction coefficients K ₁ and K ₂ acquired by the correction coefficient acquisition unit 45 are input to the color mixture correction unit 48. The color mixture correction unit 48 keeps the input correction coefficients K ₁ and K ₂ until calibration is performed again and uses them for the color mixture correction process.

The correction coefficients K ₁ and K ₂ are obtained at the manufacturing stage and are stored in advance in the information storage unit 30 of the complementary color endoscope 13a. When the complementary color endoscope 13 a is connected to the light source device 11 and the processor device 12, the control unit 31 reads the correction coefficients K ₁ and K ₂ from the information storage unit 30 and inputs them to the color mixture correction unit 48. When calibration is performed, the correction coefficients K ₁ and K ₂ stored in the information storage unit 30 of the complementary color endoscope 13a are deleted, and the correction coefficients K ₁ and K calculated by the color mixture correction unit 48 are deleted. Rewritten to ₂ .

  The color mixture correction processing of Expression (2) reduces the color mixture components (the green narrowband light Gn component in the first display signal D1 and the purple narrowband light Vn component in the second display signal D2). The first and second display signals D1 'and D2' after the color mixture correction are sent to the channel allocation unit 38.

  The primary color first processing unit 43 is selected when the type of the endoscope 13 is a primary color type and the observation mode is the normal light observation mode. RGB signals are input from the primary color image sensor 29 to the primary color first processing unit 43. This RGB signal is obtained by assigning one of R, G, and B signals to one pixel. The first primary color processing unit 43 performs a known pixel interpolation process, and generates three signals R, G, and B for each pixel. The RGB signal after this pixel interpolation processing is sent to the channel allocation unit 38.

  The primary color second processing unit 44 is selected when the type of the endoscope 13 is the primary color type and the observation mode is the narrow-band light observation mode. RGB signals are input from the primary color image sensor 29 to the second primary color processing unit 44. The primary color second processing unit 44 extracts the B signal and the G signal that are sensitive to the purple narrowband light Vn and the green narrowband light Gn, and similarly performs the pixel interpolation process, thereby performing the B signal and the G signal for each pixel. Is generated. The B signal and G signal are sent to the channel allocation unit 38.

  When the observation mode is the normal light observation mode, the channel allocating unit 38 receives RGB signals regardless of the type of the endoscope 13, so that the R, G, and B signals are respectively input to the image display device 14. Assigned to each channel of Rch, Gch, and Bch. As a result, a normal image on which an image of the specimen illuminated with the normal light is displayed is displayed on the image display device 14.

  Further, when the type of the endoscope 13 is a complementary color type and the observation mode is a narrow band light observation mode, the channel allocation unit 38 receives the first and second input from the second processing unit for complementary color 42. The display signals D1 ′ and D2 ′ are assigned to each channel of the image display device 14 and displayed as shown in Expression (3).

  As a result, a special image in which an image of the specimen illuminated by the purple narrow band light Vn and the green narrow band light Gn is displayed on the image display device 14 is displayed. In the expression (3), since the first display signal D1 ′ that is highly sensitive to the purple narrowband light Vn is assigned to two channels and displayed, the special image is a surface blood vessel (capillary blood vessel near the living body surface). Etc.) is easily visible. Note that the first and second display signals D1 'and D2' may be weighted with a coefficient other than "1" and "0" and assigned to the channel.

  Furthermore, when the type of the endoscope 13 is the primary color type and the observation mode is the narrow-band light observation mode, the channel allocation unit 38 receives the B signal and the G signal input from the primary color second processing unit 44. Is assigned to each channel of the image display device 14 and displayed as shown in equation (4).

  As a result, a special image in which an image of the specimen illuminated by the purple narrow band light Vn and the green narrow band light Gn is displayed on the image display device 14 is displayed. This special image is an image in which the structure of a surface blood vessel or the like in the vicinity of the living body surface is easily visible. Similarly, the B signal and the G signal may be weighted with a coefficient other than “1” and “0” and assigned to the channel.

Next, the operation of the color mixture correction process will be described. First, the light amounts of the purple narrowband light Vn and the green narrowband light Gn that are simultaneously irradiated into the specimen from the complementary color endoscope 13a are set to “X” and “Y”, respectively, and the purple narrowband light of the first display signal D1. The average sensitivity with respect to the light Vn is “a ₁ ”, the average sensitivity with respect to the green narrow-band light Gn of the first display signal D1 is “b ₁ ”, and the average with respect to the green narrow-band light Gn of the second display signal D2 Assuming that the average sensitivity is “a ₂ ” and the average sensitivity of the second display signal D2 to the purple narrowband light Vn is “b ₂ ”, the first and second display signals D1 and D2 ). The average sensitivity is an average of the sensitivity in the wavelength region of each narrow band light.

Further, using these sensitivities a ₁ , b ₁ , a ₂ , and b ₂ , correction coefficients K ₁ and K ₂ used for the color mixture correction processing are expressed by equations (6) and (7).

  When the color mixture correction processing of Formula (2) is performed on the first and second display signals D1, D2 represented by Formula (5), the first and second display signals D1 ′, D2 ′ is expressed by equations (8) and (9), and the color mixture component is removed.

In Expressions (8) and (9), “a ₁ X” and “a ₂ Y” are the first display signal D1v and the amount of light Y when the violet narrowband light Vn having the amount of light X is independently irradiated. This corresponds to the second display signal D2g when only the green narrow band light Gn is independently irradiated. Therefore, the first and second display signals D1 ′ and D2 ′ after the color mixture correction are (1−K ₁ K) as compared to the first and second display signals D1v and D2g when the time-division irradiation is performed. ₂ ) Indicates that the signal value is low by a factor of _two .

In particular, when α ₁₁ = α ₂₂ = 1, α ₁₂ = α ₁₃ = α ₁₄ = α ₂₁ = α ₂₃ = α ₂₄ = 0 (ie, D1 = M1, D2 = M2), refer to FIG. , A ₁ ≈0.45, a ₂ ≈0.98, b ₁ ≈0.53, b ₂ ≈0.07, and (1−K ₁ K ₂ ) ≈0.92, The reduction rate is about 8%.

  Next, the operation of the endoscope system 10 will be described along the flowchart shown in FIG. When the endoscope 13 is connected to the light source device 11 and the processor device 12 by the operator, the control unit 31 of the processor device 12 reads the unique information from the information storage unit 30 in the endoscope 13 and is connected. It is determined whether the endoscope 13 is a complementary color endoscope 13a or a primary color endoscope 13b. For example, in the case of the complementary color endoscope 13 a, the control unit 31 sets the light source device 11 and the processor device 12 to the normal light observation mode, and sends the complementary color first processing unit to the selector 40 in the signal processing unit 37. 41 is selected.

  In the normal light observation mode, the dichroic mirror 22 in the multiplexing unit 24 of the light source device 11 is retracted as described above, the WL-LED 20b is turned on, and normal light (white light) WL is generated. The light is supplied into the light guide 27 in the endoscope 13a. In addition, the complementary color imaging device 28 in the complementary color endoscope 13a is driven by the imaging control unit 32 in the field readout method and outputs the first to fourth mixed pixel signals M1 to M4. The first to fourth mixed pixel signals M1 to M4 are Y / C converted by the first processing unit for complementary color 41, converted to RGB signals, and displayed on the image display device 14 via the channel allocation unit 38. The As a result, a normal image captured under normal light is displayed on the image display device 14.

  The surgeon performs endoscopy by inserting the insertion portion 16 of the complementary color endoscope 13a into the body cavity of the patient. When it is desired to observe in more detail the running state of the surface blood vessels of the tissue to be examined such as an affected part in the body cavity, the mode switch 17a is operated by the operator. When the mode switch 17a is operated, the operation signal is detected by the control unit 31, and the light source device 11 and the processor device 12 are switched to the narrow-band light observation mode.

  In the narrow-band light observation mode, the complementary color second processing unit 42 is selected by the selector 40. In the narrow band light observation mode, the dichroic mirror 22 in the multiplexing unit 24 is disposed at the intersection of the optical axes of the V-LED 20a and the WL-LED 20b, and the V-LED 20a and the WL-LED 20b are lit simultaneously. A narrowband light in which the purple narrowband light Vn and the green narrowband light Gn are mixed is generated by the multiplexing unit 24 and supplied to the light guide 27 in the complementary color endoscope 13a. The complementary color image sensor 28 is driven by the field readout method and outputs the first to fourth mixed pixel signals M1 to M4.

  In the second processing unit for complementary color 42, the matrix calculation unit 46 performs matrix calculation on the first to fourth mixed pixel signals M1 to M4 to generate first and second display signals D1 and D2. The first and second display signals D1 and D2 are subjected to pixel interpolation processing by the interpolation processing unit 47 and then subjected to the above-described color mixing correction processing by the color mixing correction unit 48. In the first and second display signals D1 ′ and D2 ′ after the color mixture correction, the channel display unit 38 assigns the second display signal D2 ′ to Rch, and the first display signal D1 ′ to Gch and Bch. Assigned and displayed on the image display device 14. As a result, a special image picked up under narrowband light is displayed on the image display device 14.

  Since the purple narrowband light Vn can be transmitted from the surface of the specimen to the first transmission distance near the surface layer, the first image based on the purple narrowband light Vn includes a structure included in the first transmission distance such as a surface blood vessel. A lot of images are included. The first image is generated based on the first display signal D1. On the other hand, since the green narrow band light Gn can be transmitted from the surface of the specimen to the second transmission distance in the vicinity of the middle deep layer, the second transmission distance such as the middle depth blood vessel is included in the second image based on the green narrow band light Gn. There are many images of structures included in. Further, the second image is excellent in visibility of the fine pattern of the mucous membrane. The second image is generated based on the second display signal D2. A special image is a combination of the first image and the second image.

  In this embodiment, the color mixture component is removed by the color mixture correction process, and a special image with improved color separation and improved visibility of the superficial blood vessels (the contrast between the superficial blood vessels and the mucous membrane) is obtained.

  The display of the special image is repeatedly performed until the mode changeover switch 17a is operated or an ending operation for ending the diagnosis is performed by the input device 15. When the mode switch 17a is operated, the normal light observation mode is restored, and when the end operation is performed, the operation is ended.

  On the other hand, when the control unit 31 determines that the primary color endoscope 13b is connected to the light source device 11 and the processor device 12, the light source device 11 and the processor device 12 are set to the normal light observation mode and the selector 40 is set. Thus, the primary color first processing unit 43 is selected. In this normal light observation mode, as in the complementary color type, normal light (white light) WL is generated by the light source device 11 and supplied into the light guide 27 of the primary color type endoscope 13b.

  In this case, the primary color image pickup device 29 is driven by a progressive reading method and outputs RGB signals. The RGB signals are subjected to pixel interpolation processing and the like by the first primary color processing unit 43 and are displayed on the image display device 14 via the channel allocation unit 38. As a result, a normal image captured under normal light is displayed on the image display device 14.

  Thereafter, when the operator operates the mode switch 17a, the light source device 11 and the processor device 12 are switched to the narrow-band light observation mode. In the narrowband light observation mode, the primary color second processing unit 44 is selected by the selector 40, and the narrow band light Vn and the green narrowband light Gn are mixed by the light source device 11 as in the complementary color type. Band light is generated and supplied into the light guide 27 of the primary color endoscope 13b.

  Similarly, the primary color imaging device 29 is driven by the progressive readout method and outputs RGB signals. From this RGB signal, only the B signal and the G signal are extracted by the second primary color processing unit 44, subjected to pixel interpolation processing and the like, and displayed on the image display device 14 via the channel allocation unit 38. As a result, a special image picked up under narrowband light is displayed on the image display device 14.

  As in the case of the complementary color type, the display of the special image is repeatedly performed until the mode changeover switch 17a is operated or the end operation is performed by the input device 15. When the mode switch 17a is operated, the normal light observation mode is restored, and when the end operation is performed, the operation is ended.

When the complementary color endoscope 13a is connected to the light source device 11 and the processor device 12, calibration for obtaining correction coefficients K ₁ and K ₂ for color mixture correction by operating the input device 15 or the like. Execution is possible. This calibration is performed using a white plate or the like as an imaging target.

When calibration is performed, the correction coefficient acquisition unit 45 is selected by the selector 40, and time-division irradiation with the purple narrow band light Vn and the green narrow band light Gn is performed. At this time, first display signals D1v and D1g and second display signals D2g and D2v are generated based on the first to fourth mixed pixel signals M1 to M4 output from the complementary color image sensor 28, and each signal is generated. The average value is obtained. Then, correction coefficients K ₁ and K ₂ are calculated based on the relational expression of K ₁ = D2v / D1v and K ₂ = D1g / D2g. Calculated correction factor K _1, K ₂ is input to the color mixing correction unit 48 erases the correction factor K _1, K ₂ stored in the information storage unit 30 in the complementary color type endoscope 13a rewrite. The correction coefficients K ₁ and K ₂ stored in the information storage unit 30 in the complementary color endoscope 13a are read by the control unit 31 and input to the color mixing correction unit 48 when the complementary color endoscope 13a is used next time. Is done.

[Second Embodiment]
Next, an endoscope system according to a second embodiment will be described. The endoscope system according to the present embodiment is different from the endoscope system 10 according to the first embodiment in that the color mixing correction unit 48 performs color mixing correction processing using Expression (10).

Here, R ₁ is a first color mixing ratio that represents the ratio of the green narrowband light Gn component in the first display signal D1 ′. R ₂ is a second color mixing ratio that represents the ratio of the purple narrowband light Vn component in the second display signal D2 ′. R ₁ and R ₂ take values of 0 or more and 1 or less.

When R ₁ = 0 and R ₂ = 0, the expression (10) is the same as the expression (2) of the first embodiment, and the color mixture component is completely removed as shown in FIG. On the other hand, when R ₁ ≠ 0 and R ₂ ≠ 0, the green narrowband light Gn component and the purple narrowband light Vn component are included in the first and second display signals D1 ′ and D2 ′, respectively. The second color mixing ratios R ₁ and R ₂ are added. The first and second display signals D1 ′ and D2 ′ in the case of R ₁ ≠ 0 and R ₂ ≠ 0 are expressed by equations (11) and (12).

Each value of the first and second color mixing ratios R ₁ and R ₂ is corrected for color mixing so as to maintain compatibility with existing light source devices (for example, a light source device having a xenon lamp and a narrowband wavelength limiting filter). This is set in the section 48. The first and second color mixing ratios R ₁ and R ₂ are stored in the information storage unit 30 in the complementary color endoscope 13a, and the complementary color endoscope 13a is connected to the light source device 11 and the processor device 12. In this case, the control unit 31 may acquire the information from the information storage unit 30 and input it to the color mixture correction unit 48.

When R ₁ = 0 and R ₂ = 0, the signal values of the first and second display signals D1 ′ and D2 ′ are lower than in the case of time-division irradiation. The first and second color mixing ratios R ₁ and R ₂ are determined based on the equations (11) and (12) so that the first and second display signals D1 ′ and D2 ′ are at a predetermined level when it is larger. It is also preferable to do.

Further, as shown in FIG. 17, a structure enhancement processing unit 49 is provided after the color mixing correction unit 48 of the second embodiment, and the first and second display signals D1 ′ and D2 ′ output from the color mixing correction unit 48 are provided. The structure enhancement processing may be performed based on at least one of the first and second color mixing ratios R ₁ and R ₂ . For example, the structure enhancement processing unit 49 applies the blood vessel enhancement processing unit that performs frequency filtering disclosed in JP 2013-013656, the degree of enhancement of surface blood vessels portion, so high as the first color mixing ratio R ₁ is greater Set. This is because the contrast of the surface blood vessels described above decreases as the first color mixture ratio R ₁ increases.

In each of the above embodiments, the color mixing correction unit 48 performs color mixing correction on all the first and second display signals D1 and D2 using one set of correction coefficients K ₁ and K ₂ . Color mixing correction may be performed using different correction coefficients K ₁ and K ₂ for each set of the first and second display signals D1 and D2. In this case, for example, the first and second display signals D1 and D2 generated by the first to fourth mixed pixel signals M1 to M4 having the relative positional relationship shown in FIG. The correction coefficients K ₁ and K ₂ are calculated for each set using the first and second display signals when the purple narrow band light Vn and the green narrow band light Gn are independently irradiated in the calibration mode. good.

  In each of the above embodiments, the primary color second processing unit 44 assigns the B signal and the G signal included in the RGB signal to the display channel as they are, but the RGB signals are the purple narrowband light Vn and green. Since it may be sensitive to both the narrow-band light Gn, it is also preferable to perform matrix calculation and color mixture correction similar to the complementary color second processing unit 42.

  Specifically, the RGB signals (pixel signals R, G, and B) input to the primary color second processing unit 44 are subjected to matrix calculation represented by Expression (13), and the first and second display signals are displayed. D1 and D2 are generated.

The six coefficients β _{11 to} β ₂₃ are values of 0 or more and 1 or less. Specifically, the coefficients β ₁₁ and β ₂₂ are set larger than the other coefficients. For example, β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0 (that is, D1 = B, D2 = G) may be set.

The color mixture correction is the same as in the case of the complementary color second processing unit 42, and correction based on Expression (2) or Expression (10) is performed. The correction coefficients K ₁ and K ₂ irradiate the purple narrowband light Vn and the green narrowband light Gn in a time-sharing manner, perform a matrix operation on the RGB signals output from the primary color image sensor 29, and perform the first display signal D1v. , D1g and second display signals D2g, D2v are generated and calculated based on the relational expressions of K ₁ = D2v / D1v and K ₂ = D1g / D2g. The correction coefficients K ₁ and K ₂ are stored in the information storage unit 30 of the primary color endoscope 13b as in the case of the complementary color type. In addition, operations such as reading of the correction coefficients K ₁ and K ₂ from the information storage unit 30 and rewriting of the correction coefficients K ₁ and K ₂ are the same as in the case of the complementary color type, and thus description thereof is omitted.

  In each of the above embodiments, the V-LED 20a and the WL-LED 20b are used as the LED light source 20, but instead of the V-LED 20a, as shown in FIG. A blue LED that generates blue narrow band light Bn may be used. The center wavelength of the blue narrow band light Bn is in the range of about 410 nm to 420 nm, preferably about 415 nm.

  In addition, instead of the V-LED 20a and the WL-LED 20b, a plurality of LEDs having different emission wavelength ranges (for example, four LEDs) are provided, and normal light (white light) is generated by lighting all the plurality of LEDs. Alternatively, two narrowband lights may be generated by two of the plurality of LEDs. Further, other semiconductor light sources such as LD (Laser Diode) may be used instead of the LED.

  Moreover, it replaces with the light source device 11 of said each embodiment, and the light source device comprised by the lamp | ramp which emits light with a wide wavelength range, such as white light, disclosed by patent 4009626 etc. and the filter for narrow bands. May be used. This narrow band filter is a bimodal filter having band pass characteristics in two narrow bands, and is inserted into and removed from the optical axis of the lamp in accordance with the observation mode.

  Further, in each of the above embodiments, the complementary color image pickup element 28 having the complementary color checkered color difference line sequential type complementary color separation filter 28a shown in FIG. 7 is used, but the complementary color checkered color difference line sequential type complementary color shown in FIG. A complementary color image sensor having a system color separation filter may be used.

  In each of the above embodiments, the combination of the Mg pixel and the Cy pixel is a first mixed pixel, the combination of the G pixel and the Ye pixel is a second mixed pixel, and the combination of the Mg pixel and the Ye pixel is a third mixed pixel, Although the combination of the G pixel and the Cy pixel is the fourth mixed pixel, the combination of the mixed pixels is not limited to this and may be changed as appropriate.

  Further, in each of the above embodiments, the imaging control unit 32, the CDS circuit 33, the A / D conversion circuit 34, and the like are provided in the processor device 12, but these may be provided in the endoscope 13.

  In the above embodiments, the complementary color image sensor 28 and the primary color image sensor 29 are CCD image sensors. However, these may be CMOS image sensors. In the case of a CMOS image sensor, the imaging control unit 32, the CDS circuit 33, the A / D conversion circuit 34, etc. can be formed in a CMOS semiconductor substrate on which the image sensor is formed.

  In each of the above embodiments, the complementary color endoscope and the primary color endoscope can be connected to the light source device and the processor device, but only the complementary color endoscope may be connected.

  In each of the above embodiments, the light source device and the processor device are configured as separate devices, but these may be a single device. Further, the light source device may be incorporated in the endoscope.

DESCRIPTION OF SYMBOLS 10 Endoscope system 11 Light source apparatus 12 Processor apparatus 13 Endoscope 13a Complementary color type | mold endoscope 13b Primary color type | mold endoscope 14 Image display apparatus 16 Insertion part 17 Operation part 17a Mode change switch 20 LED light source 22 Green narrow-band filter 24 Multiplexing unit 27 Light guide 28 Complementary color image sensor 28a Complementary color system color separation filter 29 Primary color system image sensor 29a Primary color system color separation filter 37 Signal processing unit

Claims (12)

A light source device that simultaneously generates a first narrowband light having a center wavelength in a blue or violet wavelength region and a second narrowband light having a center wavelength in a green wavelength region;
It has a primary color separation filter composed of red, green, and blue color filter segments. The red pixel signal R is read from the red pixel, the green pixel signal G is read from the green pixel, and the blue pixel to the blue pixel. A primary color image sensor from which the signal B is read ;
Matrix calculation unit for generating first and second display signals D1, D2 by performing matrix calculation on the red pixel signal R, the green pixel signal G, and the blue pixel signal B based on the following equation (a). When,
A color mixing correction unit that corrects the first and second display signals D1 and D2 based on the following equation (b);
An endoscope system comprising:

Here, the six coefficients of β ₁₁ ~β ₂₃ are each 0 or 1 or less, the coefficient beta ₁₁ and beta ₂₂ is set to a value greater than other coefficients.

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is And a second correction coefficient representing a ratio of a signal value of the first display signal to the second display signal when only the second narrowband light is independently irradiated. Based on the signal values of the first and second display signals obtained by independently irradiating the first and second narrowband lights from the light source device, the first and second correction coefficients K ₁ and K _{2 are used.} The endoscope system according to claim 1, further comprising: a correction coefficient acquisition unit that calculates and obtains. In the formula (a), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, D1 = B, and D2 = G. The endoscope system described in 1. The primary light type endoscope having the primary color image sensor and the complementary color endoscope having a complementary color image sensor are detachably connected to the light source device. The endoscope system according to claim 1. Each of the complementary color endoscope and the primary color endoscope has an information storage unit that stores unique information.
5. The control unit according to claim 4, further comprising a control unit that reads out the unique information from the information storage unit of the endoscope connected to the light source device and determines a type of the endoscope. Endoscope system. The information storage unit stores the first and second correction coefficients K ₁ and K ₂ ,
The control unit reads the first and second correction coefficients K ₁ and K ₂ from the information storage unit when the complementary color type endoscope or the primary color type endoscope is connected to the light source device. The endoscope system according to claim 5, wherein the endoscope is input to the color mixture correction unit. A light source device that simultaneously generates a first narrowband light having a center wavelength in a blue or violet wavelength region and a second narrowband light having a center wavelength in a green wavelength region;
It has a primary color separation filter composed of red, green, and blue color filter segments. The red pixel signal R is read from the red pixel, the green pixel signal G is read from the green pixel, and the blue pixel to the blue pixel. A primary color image sensor from which the signal B is read ;
Matrix calculation unit for generating first and second display signals D1 and D2 by performing matrix calculation on the red pixel signal R, the green pixel signal G, and the blue pixel signal B based on the following equation (c). When,
A color mixing correction unit that corrects the first and second display signals D1 and D2 based on the following equation (d);
An endoscope system comprising:

Here, the six coefficients of β ₁₁ ~β ₂₃ are each 0 or 1 or less, the coefficient beta ₁₁ and beta ₂₂ is set to a value greater than other coefficients.

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is , A second correction coefficient representing a ratio of a signal value of the first display signal to the second display signal when only the second narrowband light is independently irradiated, and R ₁ is the first display A first color mixture ratio representing a ratio of the second narrowband light component in the signal value D1 ′ after correction of the signal, and R ₂ is the signal value D2 ′ in the signal value D2 ′ after correction of the second display signal. It is the 2nd color mixture rate showing the ratio of the 1st narrow-band light component. Wherein the light source device, a primary color-type endoscope having the primary color system imaging device, and the complementary endoscope having a complementary color system imaging device is detachably connected, the complementary color type endoscope and within the primary mold The endoscope has an information storage unit that stores the first and second color mixing ratios R ₁ and R ₂ , respectively.
When the complementary color endoscope or the primary color image sensor is connected to the light source device, the first and second color mixing ratios R ₁ and R ₂ are read from the information storage unit, and the color mixing correction unit The endoscope system according to claim 7, further comprising a control unit for inputting. A structure enhancement processing unit for performing blood vessel enhancement processing on the image based on the signal values D1 ′ and D2 ′;
The endoscope system according to claim 8, wherein the structure enhancement processing unit increases the degree of enhancement of the surface blood vessel portion as the first color mixing ratio R ₁ increases. In the formula (c), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, D1 = B, and D2 = G. The endoscope system according to any one of the above. A light source device simultaneously generating a first narrowband light having a center wavelength in a blue or violet wavelength range and a second narrowband light having a center wavelength in a green wavelength range;
A primary color imaging device having primary color separation filters composed of red, green, and blue color filter segments outputs a red pixel signal R from a red pixel, a green pixel signal G from a green pixel, and a blue pixel. Outputting a blue pixel signal B ;
A matrix operation unit performs a matrix operation on the red pixel signal R, the green pixel signal G, and the blue pixel signal B based on the following equation (e) to obtain the first and second display signals D1 and D2. Generating step;
A step of correcting the first and second display signals D1 and D2 based on the following equation (f):
An operation method of an endoscope system comprising:

Here, K ₁ is a first correction coefficient that represents the ratio of the signal value of the second display signal to the first display signal when only the first narrowband light is irradiated independently, and K ₂ is And a second correction coefficient representing a ratio of a signal value of the first display signal to the second display signal when only the second narrowband light is independently irradiated. 12. In the formula (e), β ₁₁ = β ₂₂ = 1, β ₁₂ = β ₁₃ = β ₂₁ = β ₂₃ = 0, D1 = B, and D2 = G. Method of operation of the endoscope system.

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