JP2013226467A - Electronic endoscope apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To obtain a spectral image in which a vascular pattern is clearly shown without providing a band pass filter of an optical wavelength narrow band only for a spectral image in a light source by making a spectral image signal using a color-image signal obtained from a usual electronic endoscope image.SOLUTION: An electronic endoscope apparatus 100, which irradiates an inside of a subject with a light from an illuminating light source 41, and obtains a color-image signal by a solid imaging element 21, includes a generation section 436 that generates a spectral image signal corresponding to the image of a narrow band, by performing prescribed calculation with respect to a color-image signal.

Description

  The present invention relates to an electronic endoscope apparatus used for medical treatment or the like.

  In recent years, attention has been focused on spectral imaging combined with a narrow band-pass filter in an electronic endoscope apparatus using a solid-state imaging device. Presented by Sano, Yoshida, Kobayashi et al. At the Annual Meeting of the Japanese Gastroenterological Endoscopy Society held in October 2000, it was spectroscopic compared to the conventional image with illumination light by the RGB frame sequential method. It was shown that the image with illumination light by the RGB surface sequential method with narrow band characteristics can extract the fine structure of the biological mucous membrane (tongue) more accurately (see Non-Patent Document 1 below). In addition, at the Annual Meeting of the Japan Gastroenterological Endoscopy Society held in May 2001, the presenter announced the results of clinical application in the gastrointestinal field. It was shown that the fine structure that was not extracted was extracted.

  The endoscope apparatus shown in this conventional example uses a surface sequential type, and the RGB color filters are changed to three optical wavelength narrow band-pass filters, and the respective optical wavelength narrow band band-pass filters are used. Each of the three spectral images is generated by the illumination light transmitted through.

N. Sano, Masahiko Kobayashi, Shigeaki Yoshida “Narrow Band Imaging (NBI) Development and Clinical Application of NBI”, Japan Gastroenterological Endoscopy Society, Gastroenterological Endoscopy, Vol.42 (Suppl .2), 1520, 2000

However, this conventional example has the following problems.
(B) An optical wavelength narrowband bandpass filter having spectral characteristics to extract a fine structure must be provided separately from a normal endoscope apparatus, and a space for installing this filter is required. The entire endoscope becomes larger.
(B) In order to obtain a spectral image using a new bandpass filter, the optical wavelength narrowband bandpass filter provided in the light source section must be replaced or added.

  An object of the present invention is to solve the above problems and obtain a spectral image without providing an optical wavelength narrow band-pass filter for spectral images in the light source section.

  According to a first aspect of the present invention, in an electronic endoscope apparatus that irradiates a subject with light from an illumination light source and obtains a color image signal by a solid-state imaging device, a predetermined calculation is performed on the color image signal. To generate a spectral image signal corresponding to a narrow-band image.

It is the conceptual diagram which showed the flow of the signal at the time of producing a spectral image signal from the color image signal in 1st Embodiment based on this invention. It is a conceptual diagram which shows the integration calculation of the color image signal in 1st Embodiment based on this invention. 1 is an external view of an electronic endoscope apparatus according to a first embodiment of the present invention. 1 is a block diagram of an electronic endoscope apparatus according to a first embodiment of the present invention. It is the figure which showed the arrangement | sequence of the color filter in 1st Embodiment based on this invention. It is the figure which showed the spectral sensitivity characteristic of each color filter in 1st Embodiment which concerns on this invention. It is a spectrum figure of the light source in 1st Embodiment based on this invention. It is a reflection spectrum figure of the living body in a 1st embodiment concerning the present invention. 1 is an external view of a chopper in a first embodiment according to the present invention. It is a normal endoscopic image in 1st Embodiment which concerns on this invention. It is a spectral image corresponded to the band pass filter F3 in 1st Embodiment which concerns on this invention. It is a spectral image equivalent to the band pass filter F2 in 1st Embodiment based on this invention. It is a spectral image equivalent to the band pass filter F1 in 1st Embodiment which concerns on this invention. It is a block diagram of the electronic endoscope apparatus in a 2nd embodiment concerning the present invention. It is a circuit diagram of the matrix calculating part in the 2nd Embodiment concerning this invention. It is a block diagram of the matrix calculating part in the 3rd Embodiment concerning this invention. It is a block diagram of the electronic endoscope apparatus in the 4th Embodiment concerning this invention. It is the figure which showed the electric charge accumulation time in 4th Embodiment based on this invention. It is the figure which showed the electric charge accumulation time in 5th Embodiment based on this invention. It is the figure which showed the arrangement | sequence of the color filter in 6th Embodiment based on this invention. It is the figure which showed the spectral sensitivity characteristic of each color filter in the 6th Embodiment concerning this invention. It is a flowchart figure in the case of the matrix calculation in the modification which concerns on this invention.

  Hereinafter, before describing the first embodiment of the present invention, a) a matrix that is the basis of the present invention will be described. Here, the matrix is a predetermined coefficient used when generating a spectral image signal from a color image signal acquired to generate a color image (hereinafter referred to as a normal image). Further, following this description, b) a correction method for obtaining a more accurate spectral image signal, and c) a method for improving the S / N ratio of the generated spectral image signal will be described. Note that this correction method and S / N improvement method may be used as necessary.

  a) FIG. 1 shows a color image signal (here, RGB is used for simplicity of explanation, but in a complementary color solid-state imaging device as in the embodiments described later, G, Cy, Mg, Ye) FIG. 4 is a conceptual diagram showing a signal flow when generating a spectral image signal corresponding to an image corresponding to an image having a narrower optical wavelength band.

First, each RGB color sensitivity characteristic as an electronic endoscope apparatus is converted into numerical data. Here, the RGB color sensitivity characteristics are output characteristics with respect to wavelengths obtained when a white subject is imaged using a white light source. The color sensitivity characteristics of RGB are shown on the right side of each data as a simplified graph.

  In addition, the RGB color sensitivity characteristics at this time are each an n-dimensional column vector RGB. Next, spectral band narrow-pass filter F1, F2, F3 (knowing the characteristics of the filter that can efficiently extract the structure as foresight information. The characteristics of this filter are that the wavelength band is approximately 590 nm- 610 nm, about 530 nm to about 550 nm, and about 400 m to about 430 nm, respectively, are used as passbands). Here, “substantially” is a concept including about ± 10 nm in wavelength.

The filter characteristics at this time are n-dimensional column vectors F ₁ , F _2, and F ₃ , respectively. Based on the obtained numerical data, an optimum coefficient set that approximates the following relationship is obtained. That is,

What is necessary is just to obtain the elements of the matrix. The solution of the above optimization proposition is given mathematically as follows: Assuming that the matrix representing the RGB color sensitivity characteristics is C, the matrix representing the spectral characteristics of the narrowband Pandpass filter to be extracted is F, and the coefficient matrix to be obtained is A.

It becomes. Therefore, the proposition shown in the equation (1) is equivalent to obtaining a matrix A that satisfies the following relationship.

Here, since the number of point sequences n as spectral data representing spectral characteristics is n> 3, equation (3) is not a one-dimensional simultaneous equation but is given as a solution of the linear least square method. That is, Equation (3) may be solved as a pseudo simultaneous equation. If the transposed matrix of matrix C is ^t C, equation (3) is

It becomes. ^{Since t} CC is an n × n square matrix, equation (4) can be viewed as a simultaneous equation for matrix A, and its solution is

And given. By converting the left side of the equation (3) for the matrix A obtained by the equation (5), it is possible to approximate the characteristics of the narrow band pan-pass filters F1, F2, and F3 to be extracted. The above is the description of the matrix on which the present invention is based.

  b) Next, a correction method for obtaining a more accurate spectral image signal will be described. In the description of the processing method described above, the light beam received by a solid-state imaging device such as a CCD is completely white light (all wavelength intensities are the same in the visible range), and is applied accurately. That is, the approximation is optimal when the RGB outputs are the same.

  However, under an actual endoscope, the illuminating light beam (light beam from the light source) is not completely white light, and the reflection spectrum of the living body is not uniform, so the light beam received by the solid-state imaging device is not white light (the color is The RGB values are not the same because they have arrived.) Therefore, in an actual process, in order to solve the proposition shown in the expression (3) more accurately, it is desirable to consider the spectral characteristics of illumination light and the reflection characteristics of a living body in addition to RGB color sensitivity characteristics.

Here, the color sensitivity characteristics are respectively R (λ), G (λ), and B (λ), an example of the spectral characteristic of the illumination light is S (λ), and an example of the reflection characteristic of the living body is H (λ). . Note that the spectral characteristics of the illumination light and the reflection characteristics of the living body do not necessarily have to be the characteristics of the inspection apparatus and the subject, and may be general characteristics acquired in advance, for example. Using these coefficients, the correction coefficients k _R · k _G · k _B are

Given in. If the sensitivity correction matrix is K, it is given as follows.

  Therefore, the coefficient matrix A is as follows by adding the correction of the equation (7) to the equation (5).

  When the optimization is actually performed, when the spectral sensitivity characteristics of the target filter (F1, F2, and F3 in FIG. 1) are negative, it becomes 0 on the image display (that is, the spectral sensitivity characteristics of the filter). Of these, only a part having a positive sensitivity is used), and it is added that a part of the optimized sensitivity distribution is allowed to be negative. In order to generate a narrower spectral sensitivity characteristic than a broad spectral sensitivity characteristic, the sensitivity is obtained by adding a negative sensitivity characteristic to the target F1, F2, F3 characteristics as shown in FIG. A component approximating the band can be generated.

c) Next, a method for improving the S / N and accuracy of the generated spectral image signal will be described. This method for improving the S / N ratio solves the following problems by adding to the processing method described above.
(A) If any of the original signals (RGB) in the above-described processing method is saturated, the characteristics of the filters F1 to F3 in the processing method are the characteristics of the filter that can extract the structure efficiently (ideal characteristics). It can be very different. (If only two signals are generated in RGB, neither of the two original signals is saturated).
(B) When a color image signal is converted into a spectral image signal, a narrowband filter is generated from a wideband filter. Therefore, sensitivity degradation occurs, and the component of the generated spectral image signal is also reduced. N ratio is not good.

As shown in FIG. 2, the method of improving the S / N ratio is that illumination light is irradiated several times (for example, n times, n times) in one field (one frame) of a normal image (general color image). Is divided into two or more integers) (irradiation intensity may be changed at each time, which is indicated by I _{0 to} In in FIG. 2. This is only by controlling illumination light. This makes it possible to reduce the intensity of a single irradiation, and to suppress the saturation of any of the RGB signals.

  In addition, the image signal divided into several times is added n times in the subsequent stage. Thereby, a signal component can be enlarged and S / N ratio can be improved. The above is the description of the matrix on which the present invention is based, the correction method for obtaining an accurate spectral image signal that can be carried out together with the matrix, and the method for improving the S / N ratio of the generated spectral image signal. is there.

  Next, a specific configuration of the electronic endoscope apparatus according to the first embodiment of the present invention will be described with reference to FIG. 2 and FIG. FIG. 2 is a conceptual diagram showing the integration operation of the color image signal, and FIG. 3 is an external view of the electronic endoscope apparatus according to the present embodiment. Note that the other embodiments described below have the same appearance.

The electronic endoscope apparatus 100 includes a scope 101, an endoscope apparatus main body 105, and a display monitor 106. The scope 101 is inserted into the body of the subject, the leading portion 102 provided at the tip of the guiding portion 102, and the tip portion 103 of the leading portion 102. It is mainly composed of an angle operation unit 104 for instructing a bending operation or the like. The subject image acquired by the scope 101 is subjected to predetermined signal processing in the endoscope apparatus main body 105, and the processed image is displayed on the display monitor 106.

  Next, the endoscope apparatus main body 105 will be described in detail with reference to FIG. FIG. 4 is a block diagram of the electronic endoscope apparatus 100. As shown in the figure, the endoscope apparatus main body 105 mainly includes a light source section 41, a control section 42, and a main body processing apparatus 43. In this embodiment, the endoscope apparatus main body, which is one unit, is described as having a light source unit and a main body processing apparatus that performs image processing. However, these can be removed as separate units. It may be configured as such.

  The light source unit 41 is connected to the control unit 42 and the scope 101, and emits white light (including a case where the light is not perfect white light) with a predetermined light amount based on a signal from the control unit 42. The light source unit 41 includes a lamp 15 as a white light source, a chopper 16 for adjusting the light amount, and a chopper driving unit 17 for driving the chopper 16.

As shown in FIG. 9, the chopper 16 has a configuration in which a notch portion having a predetermined length in the circumferential direction is provided in a disk-shaped structure having a predetermined radius r and having a center at a point 17 a. The center point 17a is connected to a rotating shaft provided in the chopper driving unit 17. That is, the chopper 16 performs rotational movement around the center point 17a. In addition, a plurality of notches are provided for each predetermined radius. In the figure, the notch has a maximum length = 2πr × 180 degrees / 360 degrees and a width = rr ₁ between the radius r and the radius r ₁ . Similarly, the maximum length = 2πr ₁ × 90 ° / 360 ° between the radius r ₁ and the radius r ₂ , the width = r ₁ −r ₂ , and the maximum between the radius r ₂ and the radius r ₃ Length = 2πr ₂ × 30 degrees / 360 degrees and width = r ₂ -r ₃ (the respective radii are r> r ₁ > r ₂ > r ₃ ).
Note that the length and width of the notch in the chopper 16 are examples, and are not limited to the present embodiment. Further, the chopper 16 has a protrusion 160a extending in the radial direction substantially at the center of the notch. In addition, by switching the frame when the light is blocked by the protrusion 160a, the interval between the light irradiated one frame before and after one frame is minimized, and the blur due to the movement of the subject is minimized. It is.

  Further, the chopper driving unit 17 is configured to be movable in the direction with respect to the lamp 15 as indicated by an arrow in FIG. That is, the distance R between the rotation center 17a of the chopper 16 shown in FIG. 9 and the luminous flux from the lamp (shown by a dotted circle) can be changed. For example, in the state shown in FIG. 9, since the distance R is quite small, the amount of illumination light is small. By increasing the distance R (the chopper driving unit 17 is moved away from the lamp 15), the cutout portion through which the light beam can pass becomes longer, so that the irradiation time becomes longer and the amount of illumination light can be increased.

  As described above, the newly generated spectral image may not be sufficient as S / N, and the correct calculation was performed when any signal required for generation was saturated. Therefore, it is necessary to control the amount of illumination light. The light amount adjustment is performed by the chopper 16 and the chopper driving unit 17.

  The scope 101 connected to the light source unit 41 via the connector 11 includes an objective lens 19 and a solid-state imaging device 21 such as a CCD (hereinafter simply referred to as a CCD) at the distal end portion 103. The CCD in this embodiment is a single plate type (CCD used for a simultaneous electronic endoscope) and is a primary color type. The arrangement of the color filters is shown in FIG. FIG. 6 shows the spectral sensitivity characteristics of RGB.

  Further, the light guiding section 102 has a light guide 14 for guiding the light emitted from the light source section 41 to the tip section 103, a signal line for transmitting an image of the subject obtained by the CCD to the main body processing apparatus 43, and A forceps channel 28 and the like for performing a treatment are provided. A forceps port 29 for inserting forceps into the forceps channel 28 is provided in the vicinity of the operation unit 104.

  Further, the main body processing device 43 is connected to the scope 101 via the connector 11, similarly to the light source unit 41. The main body processing device 43 is provided with a CCD drive 431 for driving the CCD 21. In addition, a luminance signal processing system and a color signal processing system are provided as signal circuit systems for obtaining a normal image. The luminance signal processing system includes a contour correction unit 432 that is connected to the CCD 21 and performs contour correction, and a luminance signal processing unit 434 that generates a luminance signal from data corrected by the contour correction unit 432.

  The color signal processing system is connected to the CCD 21, and samples and signals obtained by the CCD 21 are sampled and the like, and sample and hold circuits (S / H circuits) 433a to 433c and S / H circuits 433a to 433c are generated. A color signal processing unit 435 is connected to the output and generates a color signal. In addition, a normal image generation unit 437 that generates one normal image from the outputs of the luminance signal processing system and the color signal processing system is provided, and a Y signal is output from the normal image generation unit 437 to the display monitor 106 via the switching unit 439. RY signal and BY signal are sent.

  On the other hand, as a signal circuit system for obtaining a spectral image, a matrix calculation unit 436 as a generation unit is provided at the output of the S / H circuits 433a to 433c, and a predetermined matrix calculation is performed on the RGB signals. Matrix calculation refers to a process of performing addition processing or the like between color image signals and multiplying the matrix obtained as described above.

  In this embodiment, a method using electronic circuit processing (processing by hardware using an electronic circuit) will be described as the matrix calculation method. However, as in the embodiment described later, numerical data processing is performed. (Processing by software using a program) may be used. Moreover, when implementing, it is also possible to combine these.

  FIG. 15 shows a circuit diagram of the matrix calculation unit 436. The RGB signals are input to the amplifiers 32a to 32c through the resistor groups 31a to 31c, respectively. Each resistor group has a plurality of resistors to which RGB signals are respectively connected, and the resistance value of each resistor is a value corresponding to the matrix coefficient.

  In other words, the gain of the RGB signal is changed by each resistor, and the amplifiers add (or subtract). The outputs of the amplifiers 32a to 32c are the outputs of the matrix calculation unit. That is, the matrix calculation unit 436 performs so-called weighted addition processing. Note that the resistance value of each resistor used here may be variable.

The outputs of the matrix calculation unit 436 are connected to the integration units 438a to 438c, respectively, are subjected to integration calculation, and then sent to the display monitor 106 as the respective spectral image signals ΣF _{1 to} ΣF ₃ via the switching unit 439. . Note that the switching unit 439 switches between a normal image and a spectral image, and can also switch between spectral images. That is, the operator can selectively display a normal image, a spectral image by ΣF _1, a spectral image by ΣF _{2, or} a spectral image by ΣF ₃ .

Further, any two or more images may be displayed on the display monitor 106 at the same time. In particular, when the normal image and the spectral image can be displayed simultaneously, it is possible to easily compare the normal image and the spectral image that are generally observed, and each feature (the characteristic of the normal image is the degree of color). It is easy to observe close to the normal visual observation.The characteristic of the spectroscopic image can observe a predetermined blood vessel etc. that cannot be observed with the normal image.) It is.

  Next, the operation of the electronic endoscope apparatus 100 according to the present embodiment will be described in detail with reference to FIG. In the following, the operation when observing a normal image will be described first, and the operation when observing a spectral image will be described later.

  First, the operation of the light source unit 41 will be described. Based on a control signal from the control unit 42, the chopper driving unit 17 is set to a predetermined position and rotates the chopper 16. The light flux from the lamp 15 passes through the notch portion of the chopper 16 and is incident on the light guide 14 that is an optical fiber bundle provided in the connector 11 at the connection portion of the scope 101 and the light source portion 41 by the condenser lens. At the end, it is condensed. The condensed light flux passes through the light guide 14 and is irradiated into the body of the subject from the illumination optical system provided at the distal end portion 103. The irradiated light beam is reflected in the subject, and signals are collected for each color filter shown in FIG.

  The collected signals are input in parallel to the luminance signal processing system and the color signal processing system. The luminance signal-based contour correction unit 432 adds the signals collected for each color filter for each pixel and inputs them. After contour correction, the signals are input to the luminance signal processing unit 434. In the luminance signal processing unit 434, a luminance signal is generated and input to the normal image generating unit 437.

  On the other hand, signals collected by the CCD 21 are input to the S / H circuits 433a to 433c for each filter, and RGB signals are generated. Further, the RGB signal is generated by the color signal processing unit 435, and the normal image generation unit 437 generates the Y signal, the RY signal, and the BY signal from the luminance signal and the color signal, and the switching unit. A normal image of the subject is displayed on the display monitor 106 via 439.

  Next, the operation when observing a spectral image will be described. In addition, what performs the same operation | movement as observation of a normal image is abbreviate | omitted here. The operator gives an instruction to observe the spectral image from the normal image by operating a keyboard or the like provided on the main body 105 or a switch or the like provided on the operation unit 104 of the scope 101. At this time, the control unit 42 changes the control state of the light source unit 41 and the main body processing device 43.

  Specifically, the amount of light emitted from the light source unit 41 is changed as necessary. As described above, since it is not desirable that the output from the CCD 21 is saturated, the amount of illumination light is reduced as compared with a normal image. Further, it is possible to control the output signal from the CCD not to be saturated, and to change the amount of illumination light within a range where the output signal is not saturated.

  Further, as a control change to the main body processing device 43, the signal output from the switching unit 439 is switched to the signal output from the normal image generation unit 437 to the integration units 438a to 438c.

  The outputs of the S / H circuits 433a to 433c are amplified and added by the matrix calculation unit 436, and output to the integration units 438a to 438c according to the respective bands. Even when the amount of illumination light is reduced by the chopper 16, the signal intensity can be increased and the S / N can be improved as shown in FIG. 2 by storing and integrating in the integrating units 438 a to 438 c. Spectral images can be obtained.

Hereinafter, specific matrix processing in the present embodiment will be described. In the present embodiment, from the RGB spectral sensitivity characteristics indicated by the solid line in FIG. 6, the ideal narrow-band bandpass filters F1 to F3 (in this case, the respective transmission wavelength regions are F1: When trying to create a bandpass filter (hereinafter referred to as a pseudo bandpass filter) close to 590nm-620nm, F2: 520nm-560nm, F3: 400nm-440nm), the above formulas (1) to (5) The following matrix is optimal according to the contents shown in.

  Further, when correction is performed according to the contents shown in the equations (6) and (7), the following correction coefficients are obtained.

  Note that the light source spectrum shown in the equation (6) uses foresight information as shown in FIG. 7, and the reflection spectrum of the target living body shown in the equation (7) uses that shown in FIG. Accordingly, the processing performed in the matrix portion is mathematically equivalent to the following matrix operation.

By performing this matrix operation, pseudo filter characteristics (shown as characteristics of filter pseudo F _{1 to} F _{3 in} FIG. 6) are obtained.

  That is, the matrix processing described above creates a spectral image signal using a pseudo bandpass filter (matrix) generated in advance as described above for a color image signal.

  An example of an endoscopic image generated using this pseudo filter characteristic is shown below. The subject is the gastrointestinal mucosal surface, and FIG. 10 is a normal endoscopic image. 11 is a spectral image corresponding to the bandpass filter F3 shown in FIG. 6 obtained after processing, and FIG. 12 is a spectral image equivalent to the bandpass filter F2 shown in FIG. 6 obtained after processing. FIG. 13 is a spectral image corresponding to the bandpass filter F1 shown in FIG. 6 obtained after processing.

  Each of the spectroscopic images shown in FIGS. 11 to 13 clearly extracts a blood vessel pattern equivalent to or higher than the normal image shown in FIG. In particular, the spectroscopic images using the filters of the bands of about 400 to about 440 nm and about 520 to about 560 nm shown in FIGS. 11 and 12 extract the blood vessel pattern more clearly.

  As is clear from the above, according to the present embodiment, a pseudo narrowband filter is generated using a color image signal for generating a normal electronic endoscopic image (normal image). Thus, a spectral image in which a blood vessel pattern is clearly displayed can be obtained without using an optical wavelength narrow bandpass filter for spectral images.

  Further, in particular, in a wavelength range of approximately 400 to approximately 440 nm and approximately 520 to approximately 560 nm, a spectroscopic image in which a blood vessel pattern is extracted more clearly can be obtained.

  Hereinafter, a second embodiment of the present invention will be described with reference to FIG.

  FIG. 14 is a block diagram of the electronic endoscope apparatus 100 according to the present embodiment. In addition, the thing of the same structure as 1st Embodiment attaches | subjects the same number, and abbreviate | omits description.

  This embodiment is mainly different from the first embodiment in the light source unit that controls the amount of illumination light. In the present embodiment, the amount of light emitted from the light source unit is controlled not by the chopper but by the current control of the lamp.

  Specifically, a current control device 16 'is provided in the lamp 15 shown in FIG.

  As an operation of the present embodiment, the control unit 42 controls the current flowing through the lamp 15 so that none of the RGB color image signals are saturated. Thereby, since the current used for light emission in the lamp 15 is controlled, the amount of light changes according to the magnitude of the current. Other operations are the same as those in the first embodiment, and are omitted here.

  According to the present embodiment, a spectral image in which a blood vessel pattern is clearly displayed can be obtained as in the first embodiment. In addition, the present embodiment has an advantage that the control method is simpler than the light amount control method using the chopper as in the first embodiment.

  Hereinafter, a third embodiment according to the present invention will be described with reference to FIG.

  This embodiment is mainly different from the first embodiment in the matrix calculation unit 436. In the first embodiment, the matrix operation is performed by so-called hardware processing by an electronic circuit. In the present embodiment, this operation is performed by numerical data processing (processing by software using a program).

  FIG. 16 shows a specific configuration of the matrix calculation unit in the present embodiment. The matrix calculation unit has an image memory 50 for storing RGB color image signals. Further, it has a counting register 51 in which each value of the matrix A ′ shown in the equation (11) is stored as numerical data.

  The counting register 51 and the image memory 50 are connected to the multipliers 53a to 53i, the multipliers 53a, 53d, and 53g are connected to the multiplier 54a, and the output of the multiplier 54a is connected to the integrating unit 438a in FIG. Is done. The multipliers 53b, 53e, and 53h are connected to the multiplier 54b, and the output thereof is connected to the integrating unit 438b. The multipliers 53c, 53f, and 53i are connected to the multiplier 54c, and the output thereof is connected to the integrating unit 438c.

  In the operation of the present embodiment, the input RGB image data is once stored in the image memory 50. Next, the RGB image data stored in the image memory 50 is multiplied with the RGB image data stored in the image memory 50 from the counting register 51 by a multiplier by an arithmetic program stored in a predetermined storage device (not shown).

  FIG. 16 shows an example in which the R signal and each matrix count are multiplied by multipliers 53a to 53c. Also, as shown in the figure, the G signal and each matrix count are multiplied by multipliers 53d to 53f, and the B signal and each matrix count are multiplied by multipliers 53g to 53i. The data multiplied by the matrix count is obtained by multiplying the outputs of the multipliers 53a, 53d and 53g by the multiplier 54a, the outputs of the multipliers 53b, 53e and 53h by the multiplier 54b, and the multipliers 53c, 53f, The outputs of 53i are respectively multiplied by the multiplier 54c.

  The output of the multiplier 54a is sent to the integrating unit 438a. The outputs of the multiplier 54b and the multiplier 54c are sent to the integrating units 438b and 438c, respectively.

  According to the present embodiment, a spectral image in which a blood vessel pattern is clearly displayed can be obtained as in the first embodiment. In the present embodiment, matrix processing is not performed by hardware as in the first embodiment, but is performed by software. For example, it is possible to respond quickly to changes in each matrix count, for example. it can.

  Further, the matrix count is stored not only as a result value, that is, as S (λ), H (λ), R (λ), G (λ), and B (λ), but as a matrix A ′. When the matrix A ′ is obtained and used by calculating according to the above, only one of the elements can be changed, and convenience is improved. For example, it is possible to change only the spectral characteristic S (λ) of the illumination light.

  Next, a fourth embodiment according to the present invention will be described with reference to FIG. In the present embodiment, the light source unit 41 and the CCD 21 are mainly different from the first embodiment. In the first embodiment, the CCD 21 is provided with the color filter shown in FIG. 2 and a color signal is generated by this color filter. In contrast, in this embodiment, the illumination light is converted into RGB. A so-called frame sequential method is used in which a color signal is generated by illuminating in the order.

  In the light source unit 41 in the present embodiment, a diaphragm 25 is provided in front of the lamp 15, and an RGB filter 23 is provided in front of the diaphragm 25. In addition, the diaphragm 25 is connected to the diaphragm control unit 24, and restricts the light beam to be transmitted among the light beams emitted from the lamp 15 in accordance with a control signal from the diaphragm control unit 24, thereby changing the light amount. The RGB rotation filter 23 is connected to the RGB rotation filter control unit 26 and rotates at a predetermined rotation speed.

  As an operation of the light source unit in the present embodiment, the light beam output from the lamp 15 is limited to a predetermined light amount by the diaphragm 25, and the light beam transmitted through the diaphragm 25 passes through the RGB filter every predetermined time. Are output from the light source section as RGB illumination lights.

  Each illumination light is reflected in the subject and received by the CCD 21. Signals obtained by the CCD 21 are distributed by a switching unit (not shown) provided in the endoscope apparatus main body 105 according to the irradiation time, and input to the S / H circuits 433a to 433c, respectively. That is, when the illumination light is irradiated from the light source unit 41 through the R filter, the signal obtained by the CCD 21 is input to the S / H circuit 433a. Other operations are the same as those in the first embodiment, and are omitted here.

  According to the present embodiment, a spectral image in which a blood vessel pattern is clearly displayed can be obtained as in the first embodiment. Also, in the present embodiment, unlike the first embodiment, it is possible to enjoy the advantages of the so-called frame sequential method. This merit includes, for example, the following fifth embodiment.

  In the above-described embodiment, the illumination light amount (light amount from the light source unit) is controlled and adjusted in order to avoid saturation of the RGB color signal. On the other hand, there is a method of adjusting the electronic shutter of the CCD. In the CCD, a charge proportional to the intensity of light incident within a predetermined time is accumulated, and the amount of the charge is used as a signal. The accumulation time corresponds to what is called an electronic shutter.

  By adjusting this electronic shutter, it is possible to adjust the charge accumulation amount, that is, the signal amount, so as shown in FIG. 18, by obtaining an RGB color image with the charge accumulation time sequentially changed, Similar spectral images can be obtained. That is, in each of the embodiments described above, the illumination light amount control is used to obtain a normal image, and when obtaining a spectral image, it is possible to avoid saturation of the RGB color signal by changing the electronic shutter. It is.

  Next, a fifth embodiment according to the present invention will be described with reference to FIG.

  In the present embodiment, as in the fourth embodiment, the frame sequential method is used, and this advantage is utilized. By adding weight to the charge accumulation time by the electronic shutter control in the fourth embodiment, the generation of spectral image data can be simplified. That is, in this embodiment, the CCD drive 431 that can change the charge accumulation time of the CCD is provided. Other configurations are the same as those of the fourth embodiment, and are omitted here.

As the operation of the present embodiment, as shown in FIG. 19, when each illumination light is irradiated through the RGB rotation filter, the charge accumulation time by the electronic shutter in the CCD is changed. Here, td _r , td _g , td _b are the charge accumulation times of the CCD when the illumination lights are RGB (in this figure, the color image signal of B is not provided with the accumulation time, so td _b is omitted). ). For example, the F3 pseudo filter image in the case of performing the matrix processing represented by the expression (11) is obtained from an RGB image obtained by a normal endoscope,

Therefore, the charge accumulation time by RGB electronic shutter control in FIG.

It should be set so that.

  In the matrix portion, the signal obtained by simply inverting only the R and G components and the B component are added. Thereby, the same spectral images as those in the first to fourth embodiments can be obtained.

  According to the present embodiment, a spectral image in which a blood vessel pattern is clearly displayed can be obtained as in the fourth embodiment. In this embodiment, as in the fourth embodiment, a color sequential method is used to create a color signal, and the charge accumulation time can be varied for each color signal using an electronic shutter. Therefore, it is possible to simplify the process by simply performing addition and difference processing in the matrix portion.

  Next, a sixth embodiment according to the present invention will be described. This embodiment is mainly different from the first embodiment in the color filter provided in the CCD. In the first embodiment, an RGB primary color filter is used as shown in FIG. 2, whereas in this embodiment, a complementary color filter is used. As shown in FIG. 20, the complementary color filter array includes G, Mg, Ye, and Cy elements. The relationship between each element of the primary color filter and each element of the complementary color filter is Mg = R + B, Cy = G + B, Ye = R + G.

  In this case, all the pixels of the solid-state imaging device are read out, and the image from each color filter is subjected to signal processing or image processing. Further, when the equations (1) to (11) for the primary color filter are modified in the case of the complementary color filter, the following equation (21) is obtained from the following equation (15). However, the characteristics of the target narrow-band bandpass filter are the same.

  FIG. 21 shows the spectral sensitivity characteristics when the complementary color filter is used, the target band-pass filter, and the characteristics of the pseudo band-pass filter obtained by the expressions (15) to (21). When the complementary color filter is used, it goes without saying that the S / H circuit shown in FIG. 4 is performed for G, Mg, Cy, and Ye instead of RGB.

  According to the present embodiment, a spectral image in which a blood vessel pattern is clearly displayed can be obtained as in the first embodiment. Further, in this embodiment, it is possible to enjoy the advantages of using a complementary color filter.

  The embodiments of the present invention have been described above. However, the present invention may be used by combining the above-described embodiments, and modifications within a range not departing from the spirit are also conceivable.

  For example, for all the embodiments described above, a new pseudo bandpass filter can be created by the operator himself at clinical or other timings and applied to the clinic. That is, in the first embodiment, a design unit (not shown) capable of calculating and calculating matrix coefficients is provided in the control unit 42 in FIG.

  Thereby, by inputting conditions via the keyboard provided in the endoscope main body shown in FIG. 3, a pseudo bandpass filter suitable for obtaining a spectral image that the operator wants to know is newly designed, Finally, correction coefficients (corresponding to each element of the matrix K in the expressions (10) and (20)) are applied to the calculated matrix coefficients (corresponding to the elements in the matrix A in the expressions (9) and (19)). By setting the matrix coefficient (corresponding to each element of the matrix A ′ in the equations (11) and (21)) in the matrix calculation unit 436 in FIG.

  FIG. 22 shows a flow until application. This flow will be described in detail. First, the operator inputs information about a target bandpass filter (for example, a wavelength band) via a keyboard or the like. As a result, the matrix A ′ is calculated together with the characteristics of the light source / color filter already stored in a predetermined storage device or the like, and the matrix along with the characteristics of the target bandpass filter as shown in FIG. The calculation result (pseudo bandpass filter) by A ′ is displayed on the monitor as a spectrum diagram. After the operator confirms the calculation result, when using the newly created matrix A ′, the operator performs the setting, and an actual endoscopic image is generated using the matrix A ′. In addition, the newly created matrix A ′ is stored in a predetermined storage device and can be used again according to a predetermined operation by the operator. Thus, the operator can generate a new bandpass filter based on his / her own experience and the like without being constrained by the existing matrix A ′, and is particularly effective when used for research purposes.

  In addition, the following modifications can be considered. For example, in the above-described embodiment, in the generation of the F3 pseudo filter image shown in Expression (12), the R component is small enough to be ignored with respect to the G / B component. In such a case,

Thus, it is not necessary to use R image signals or numerical data. At this time, even if the signal of the R image or the numerical data is saturated, there is no effect on the processing in the matrix portion. Therefore, on the condition that the signal of the G image and the B image or the numerical data is not saturated, Electronic shutter control may be performed.

  As described above in detail, according to the present invention, a spectral image signal is generated using a color image signal obtained from a normal electronic endoscopic image. Even if no bandpass filter is provided, a spectral image in which a blood vessel pattern or the like is clearly displayed can be obtained.

  Although an embodiment of the present invention has been described, this embodiment is presented as an example and is not intended to limit the scope of the invention. This embodiment can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. This embodiment and its modifications are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 11 Connector 14 Light guide 15 Lamp 16 Chopper 17 Chopper drive part 19 Objective lens 21 Solid-state image sensor 23 RGB filter 24 Aperture control part 25 Aperture 26 RGB rotary filter control part 28 Forceps channel 29 Forceps port 31 Amplifier 32 Resistance group 33 Adder 41 Light source unit 42 Control unit 43 Main unit processing device 50 Image memory 51 Count register 53 Multiplier 54 Multiplier 101 Scope 102 Leading unit 103 Tip unit 104 Operation unit 105 Endoscope main unit 106 Display monitor

Claims (18)

In an electronic endoscope apparatus that irradiates light from a light source for illumination into a subject and acquires a color image signal by a solid-state imaging device,
An electronic endoscope apparatus comprising: a generation unit that generates a spectral image signal corresponding to a narrow-band image by performing a predetermined calculation on the color image signal.   The electronic endoscope apparatus according to claim 1, wherein a plurality of the narrow-band images are obtained by the spectral image signal generated by the generation unit.   The electronic endoscope apparatus according to claim 1, wherein the generation unit generates the spectral image signal by performing weighted addition processing on the color image signal.   The electronic endoscope apparatus according to claim 1, wherein the generation unit generates the spectral image signal by performing a coefficient multiplication process on the color image signal.   The electronic endoscope apparatus according to claim 1, further comprising a light amount control unit that controls a light amount emitted from the illumination light source.   The electronic endoscope apparatus according to claim 5, wherein the light amount control unit includes a chopper that blocks the light at a predetermined time interval.   The electronic endoscope apparatus according to claim 5, wherein the light amount control unit includes a current control unit that controls a current flowing through a lamp of the illumination light source.   The electronic endoscope apparatus according to claim 1, further comprising an electronic shutter control unit that controls an electronic shutter that determines a charge accumulation time by the solid-state imaging device.   The electronic endoscope apparatus according to claim 8, wherein the electronic shutter control unit can independently control the charge accumulation time for each color image signal.   A light amount limiting unit that controls the amount of light emitted from the illumination light source; and an electronic shutter control unit that controls an electronic shutter that determines a charge accumulation time by the solid-state imaging device, the light amount and the charge accumulation The electronic endoscope apparatus according to claim 1, wherein the time is controlled simultaneously.   The electronic endoscope apparatus according to claim 1, further comprising a setting unit capable of changing a predetermined coefficient used when generating the predetermined spectral image signal from the color image signal.   The electronic endoscope apparatus according to claim 1, wherein a color image generated based on the color image signal and a spectral image generated based on the spectral image signal can be switched and displayed.   The electronic endoscope apparatus according to claim 1, wherein a color image generated based on the color image signal and a spectral image generated based on the spectral image signal can be displayed on the same screen. .   The electronic endoscope apparatus according to claim 1, wherein the generation unit generates the spectral image signal from the color image signal using a predetermined coefficient obtained based on a color sensitivity characteristic.   The generation unit further uses the predetermined coefficient obtained based on at least one of the spectral characteristics of the illumination light source and the reflection characteristics in the subject to generate the spectral image signal from the color image signal. The electronic endoscope apparatus according to claim 14, wherein:   The electronic endoscope apparatus according to claim 1, wherein the spectral image signal includes a negative signal.   The electronic endoscope apparatus according to claim 1, wherein the color image signal is an RGB signal or a GCyMgYe signal. 18. The spectral image signal according to claim 1, wherein the spectral image signal is an image signal in a wavelength region of approximately 400 nm to approximately 440 nm, or an image signal in a wavelength region of approximately 520 nm to approximately 560 nm. Electronic endoscope device.

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