JP5883668B2 - Spectral data collection system and electronic endoscope system - Google Patents

Description

  The present invention relates to a spectral data collection system capable of collecting spectral data for assisting diagnosis and an electronic endoscope system.

  In the medical equipment field, an electronic endoscope system capable of taking a spectral image is known in order to more effectively diagnose a lesion. A specific configuration of this type of electronic endoscope system is described in Patent Document 1, for example.

  The electronic endoscope system described in Patent Document 1 performs spectral imaging combined with a narrow band-pass filter based on estimation of spectral reflectance in the digestive organs (gastric mucosa, etc.). Specifically, the electronic endoscope system described in Patent Document 1 is provided with three narrow-band bandpass filters instead of the frame-sequential R, G, and B rotation filters. By sequentially outputting narrowband light through a bandpass filter and performing the same processing as in the case of RGB signals while changing the respective weights for the three signals obtained with each narrowband light, a spectral image is obtained. Generate.

JP 2006-255324 A

  However, the electronic endoscope system described in Patent Document 1 merely generates a pseudo spectral image estimated from a subject image irradiated with narrowband light. Therefore, in the electronic endoscope system described in Patent Document 1, a problem is pointed out that accuracy of spectral analysis using a spectral image is low.

  In order to solve the above problems, a spectral data collection system according to an aspect of the present invention includes a light source that emits irradiation light irradiated on a subject, and a spectral having a plurality of peak wavelengths of irradiation light or reflected light from the subject. A filter that splits light into light, a transmission wavelength variable filter in which the peak wavelength of the light to be split is variable, and a color filter array group consisting of an array of a plurality of types of predetermined color filters are installed on the imaging element surface, An imaging element that generates an imaging signal having color information by capturing an object image to which spectral characteristics of the transmission wavelength variable filter are given through a color filter array group, an imaging signal of the object generated by the imaging element, and Based on the spectral characteristics of each color filter for each peak wavelength set by the transmission wavelength variable filter when shooting the subject Entering the child, a system characterized in that it comprises a spectral calculation means for calculating the intensity of light of each peak wavelength.

  According to the present invention, high-quality spectral data (intensity of light at each peak wavelength) can be collected by using an optical spectral filter, and a color imaging device that has been widely used in recent years, By using a transmission wavelength tunable filter capable of setting the transmission peak wavelength, spectral data of a plurality of peak wavelengths can be collected simultaneously. Therefore, it is possible to shorten the spectral data collection time. That is, according to the present invention, more high-quality spectral data can be collected within a limited time, so that the accuracy of processing using spectral data such as spectral analysis is improved.

  In addition, the spectral data collection system according to an aspect of the present invention may further include a spectroscopic measurement unit that measures the spectral characteristics of the spectroscopic light split by the transmission wavelength variable filter. In this case, the spectral calculation means includes the subject imaging signal generated by the imaging device, the spectral characteristics of each color filter for each peak wavelength set by the transmission wavelength variable filter at the time of photographing the subject, and the spectral measurement means Based on the spectral characteristics of the spectral light measured by the above, it is possible to calculate the intensity of light of each peak wavelength incident on the image sensor from the subject.

  In addition, the spectral data collection system according to an aspect of the present invention is configured so that the peak wavelength of the spectral light by the transmission wavelength variable filter changes every time the light intensity of a plurality of peak wavelengths is calculated by the spectral calculation means. The filter drive control means for driving and controlling the transmission wavelength variable filter may be further provided.

  The spectral data collection system according to an aspect of the present invention is a rotational type in which a transmission wavelength variable filter and at least one filter having spectral characteristics different from the transmission wavelength variable filter are arranged in the circumferential direction. A filter turret, and a turret drive control unit that drives and controls the rotary filter turret and selectively inserts one of the filters in the rotary filter turret in the optical path between the light source and the image sensor. It is good also as a structure provided.

  In addition, the spectral data collection system according to one aspect of the present invention guides the irradiation light to the first or second optical path by transmitting or reflecting the irradiation light with the mirror and transmitting or reflecting the irradiation light with the mirror. It is good also as a structure further provided with the mirror drive control means. The transmission wavelength tunable filter is disposed, for example, in the first optical path, and the irradiation light guided to the first optical path irradiates the subject through the transmission wavelength tunable filter and is guided to the second optical path. The irradiated light irradiates the subject without passing through the transmission wavelength variable filter.

  In addition, the spectral data collection system according to one aspect of the present invention guides the reflected light to the first or second optical path by transmitting or reflecting the reflected light by the mirror and transmitting or reflecting the reflected light by the mirror. It is good also as a structure further provided with the mirror drive control means. The transmission wavelength tunable filter is disposed, for example, in the first optical path, and the reflected light guided to the first optical path enters the image sensor through the transmission wavelength tunable filter and is guided to the second optical path. The irradiated light enters the image sensor without going through the transmission wavelength variable filter.

  In addition, an electronic endoscope system according to an aspect of the present invention incorporates the spectral data collection system, and includes a processor and an electronic endoscope. The electronic endoscope includes an image sensor, and the processor includes at least a light source, a transmission wavelength variable filter, and a spectral calculation unit.

  According to the spectral data collection system and the electronic endoscope system according to the present invention, high-quality spectral data can be collected by using an optical spectral filter. In addition, since spectral data of a plurality of peak wavelengths can be collected at the same time, spectral data collection time can be shortened. That is, according to the spectroscopic data collection system and the electronic endoscope system according to the present invention, more high-quality spectroscopic data can be collected within a limited time. Processing accuracy is improved.

It is a block diagram which shows the structure of the electronic endoscope system which concerns on embodiment of this invention. It is a figure which shows the relationship between the spectral characteristic of Ye filter, and the output value of yellow pixel Ye. It is a flowchart which shows the spectral data collection process performed with the electronic endoscope system which concerns on embodiment of this invention. It is a figure which shows the structure of the rotary filter turret with which the spectroscopy unit which concerns on another embodiment is equipped. It is a block diagram which shows the structure of the modification 1 of the electronic endoscope system which concerns on embodiment of this invention. It is a block diagram which shows the structure of the modification 2 of the electronic endoscope system which concerns on embodiment of this invention. It is a block diagram which shows the structure of the modification 3 of the electronic endoscope system which concerns on embodiment of this invention. It is a block diagram which shows the structure of the modification 4 of the electronic endoscope system which concerns on embodiment of this invention.

  Hereinafter, an electronic endoscope system according to an embodiment of the present invention will be described with reference to the drawings.

  FIG. 1 is a block diagram illustrating a configuration of an electronic endoscope system 1 according to the present embodiment. As shown in FIG. 1, the electronic endoscope system 1 is a medical imaging system, and includes an electronic scope 100, a processor 200, and a monitor 300. The proximal end of the electronic scope 100 is optically and electrically connected to the processor 200. The processor 200 integrally includes an image processing device that processes an imaging signal output from the electronic scope 100 to generate an image, and a light source device that irradiates a body cavity that does not reach natural light via the electronic scope 100. It is a processor. In another embodiment, the image processing device and the light source device may be configured as separate devices instead of an integrated device.

  As shown in FIG. 1, the processor 200 includes a system controller 202 and a timing controller 204. The system controller 202 controls each element constituting the electronic endoscope system 1. The timing controller 204 outputs a clock pulse for adjusting the signal processing timing to various circuits in the electronic endoscope system 1.

  The lamp 208 emits white light after being started by the lamp power igniter 206. As the lamp 208, a high-intensity lamp such as a xenon lamp, a halogen lamp, a mercury lamp, or a metal halide lamp is suitable. Irradiation light emitted from the lamp 208 enters the spectroscopic unit 210.

  Here, in general, the wavelength band of a spectral image useful for diagnosis differs depending on a region to be diagnosed and a lesion. In addition, depending on the type of site or lesion, there are some that require a plurality of spectral images captured in different wavelength bands. The electronic endoscope system 1 according to the present embodiment is configured to capture a spectral image in an arbitrary wavelength band in order to meet such a demand. Specifically, the spectroscopic unit 210 includes a spectroscope 210a on which a gap variable etalon is mounted. The variable gap etalon is a variable transmission spectrum based on the same principle as a Fabry-Perot interferometer. A pair of transmission substrates with a reflective film formed on one side are arranged in parallel so that the reflective films face each other. The light incident on the transmission substrate is subjected to multiple reflection and interference between the reflection films, and is split into light having peaks at specific wavelengths (hereinafter referred to as “band-limited light”). The plurality of peak wavelengths of the band-limited light emitted from the gap-variable etalon is determined by the gap between the reflective films, that is, the gap between the transmissive substrates. The gap between the transmissive substrates can be changed by driving and controlling a piezoelectric actuator built in the spectrometer 210a.

  Further, since the gap variable type etalon is a minute and precise mechanical part, there is a possibility that the optical performance largely fluctuates due to a slight change in mechanical characteristics or electrical characteristics due to temperature change or aging change. For example, even if the frame holding the transparent substrate is slightly deformed due to thermal expansion, the gap may change and the spectral characteristics (transmission spectrum) may change greatly. Therefore, in the present embodiment, the spectroscopic unit 210 is provided with a spectroscopic instrument 210b that measures the spectroscopic characteristics of the band-limited light emitted from the spectroscope 210a. The spectrometer 210b measures the reflection component of the half mirror 210d and outputs the measured value to the spectrometer control unit 210c. The spectrometer control unit 210c drives the spectrometer 210a (piezoelectric actuator) based on the measurement value input from the spectrometer 210b to adjust the gap between the transmission substrates, and the spectral characteristic of the band-limited light becomes the target value. Feedback control is performed to converge. The target value is set, for example, according to a target value setting operation of the user interface 212 by the surgeon, or is set when a spectral data collection process described later is executed.

  The spectroscope 210a is inserted into or retracted from the optical path of the irradiation light by the actuator 210ACT. In this specification, the mode in which the spectroscope 210a is inserted in the optical path, and the spectroscopic data is collected by using the spectroscope 210a is referred to as “spectral data collection mode”, and the spectroscope 210a is retracted from the optical path. A mode in which a normal color image is generated without being used is referred to as a “normal observation mode”. By operating the mode switching button 114 provided on the electronic scope 100 or the user interface 212 provided on the processor 200 to drive the actuator 210ACT, the spectroscope 210a can be selectively inserted in the optical path. In FIG. 1, for the sake of simplicity, the connection between the mode switching button 114 and other circuits is omitted.

  First, the normal observation mode will be described. In the normal observation mode, the spectroscope 210a is retracted from the optical path of the irradiation light. Therefore, the irradiation light incident on the spectroscopic unit 210 is incident on an incident end of an LCB (Light Carrying Bundle) 102 without passing through the spectroscope 210a. In the present embodiment, description and illustration of the diaphragm, coupling lens, and the like disposed between the lamp 208 and the LCB 102 are omitted for convenience.

  Irradiation light incident on the incident end of the LCB 102 propagates by repeating total reflection in the LCB 102. Irradiation light propagating through the LCB 102 is emitted from the emission end of the LCB 102 disposed at the tip of the electronic scope 100. Irradiation light emitted from the exit end of the LCB 102 irradiates the subject via the light distribution lens 104. The reflected light from the subject forms an optical image at each pixel on the light receiving surface of the solid-state image sensor 108 via the objective lens 106.

  The solid-state image sensor 108 is, for example, a single-plate color CCD (Charge Coupled Device) image sensor having a complementary color checkered pixel arrangement, and accumulates an optical image formed by each pixel on the light receiving surface as a charge corresponding to the amount of light. , Yellow Ye, cyan Cy, green G, and magenta Mg. The converted image signal is amplified by the preamplifier 110 and then input to the signal processing circuit 220 via the driver signal processing circuit 112. The solid-state image sensor 108 may be a single-plate color CCD image sensor having a Bayer pixel arrangement, for example. Moreover, other imagers, such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor, may be used.

  The timing controller 204 supplies clock pulses to the driver signal processing circuit 112 in accordance with timing control by the system controller 202. The driver signal processing circuit 112 drives and controls the solid-state imaging device 108 at a timing synchronized with the frame rate of the video processed on the processor 200 side, according to the clock pulse supplied from the timing controller 204.

  The image pickup signal input to the signal processing circuit 220 is subjected to processing such as clamping, knee, γ correction, interpolation processing, AGC (Auto Gain Control), AD conversion, and the like, and corresponds to each color of R, G, B for each color signal for each frame. Buffered in a frame memory (not shown). Each buffered color signal is swept from the frame memory at a timing controlled by the timing controller 204, and converted into a video signal conforming to a predetermined standard such as NTSC (National Television System Committee) or PAL (Phase Alternating Line). Converted. By sequentially inputting the converted video signals to the monitor 300, a normal color image of the subject is displayed on the display screen of the monitor 300.

  The signal processing circuit 220 includes a spectral calculation unit 220a, a spectral analysis unit 220b, a spectral data storage unit 220c, and an image integration unit 220d. These are components necessary for executing the spectral data collection mode, and in the normal observation mode, for example, to suppress standby power, the power supply is turned off and is in a sleep state.

  Next, the spectral data collection mode will be described. In the spectral data collection mode, the spectroscope 210a is inserted in the optical path of the irradiation light, and the spectral calculation unit 220a, the spectral analysis unit 220b, the spectral data storage unit 220c, and the image integration unit 220d are activated. Therefore, the irradiation light that has entered the spectroscopic unit 210 is transmitted through the spectroscope 210 a and split into band-limited light, and the subject is irradiated through the LCB 102 and the light distribution lens 104. The reflected light from the subject is received by the solid-state imaging device 108 via the objective lens 106 and converted into an imaging signal, and then transmitted to the signal processing circuit 220 (spectral calculation unit 220a) via the preamplifier 110 and the driver signal processing circuit 112. input. Hereinafter, for convenience of explanation, the reflected light from the subject incident on the solid-state image sensor 108 in the spectral data collection mode (that is, the spectroscope 210a is disposed in the optical path between the lamp 208 and the solid-state image sensor 108) is expressed as “ "Spectral reflected light". The intensity data of the spectral reflected light is spectral data to be collected.

  Here, as in the present embodiment, when an object irradiated with band-limited light having a plurality of peak wavelengths (for example, wavelengths λ1 to λ4) is imaged by a color image sensor, the output value of each pixel is transmitted through the color filter. It is a value obtained by integrating the spectral reflection light intensities having the wavelengths λ1 to λ4. For example, FIG. 2 shows the relationship between the spectral characteristics of the Ye filter and the output value of the yellow pixel Ye. In FIG. 2, the vertical axis indicates the spectral reflected light intensity and the transmittance of the Ye filter, and the horizontal axis indicates the wavelength (unit: nm). The solid line (thin line) indicates the spectral reflected light intensity before entering the Ye filter, the solid line (thick line) indicates the spectral reflected light intensity after passing through the Ye filter (that is, the output value of the yellow pixel Ye), and the broken line indicates The spectral characteristics of the Ye filter are shown. As shown in FIG. 2, spectral reflected light having peak wavelengths λ1 to λ4 is incident on the yellow pixel Ye, and the output value of the spectral reflected light intensity of the peak wavelengths λ1 to λ4 indicated by the solid line (thick line). The integrated value is a value in which each wavelength component is mixed. In order to collect the pixel output value as spectral data in peak wavelength units, it is necessary to decompose the pixel output value for each peak wavelength.

  Therefore, the spectral calculation unit 220a defines illumi (λn) (n = 1 to 4) as the spectral reflected light intensity of the peak wavelength λn, and Cy (λn), Mg (λn), Ye (λn), G ( λn) is defined as the transmittance of the Cy filter, Mg filter, Ye filter, and G filter with respect to the peak wavelength λn, and Cy, Mg, Ye, and G are cyan pixel Cy, magenta pixel Mg, yellow pixel Ye, and green, respectively. When the output value of the pixel G is defined, the calculation shown in the following equation (1) is performed. The spectral calculation unit 220a applies the peak wavelengths λ1 to λ4 of the target value determined by the target value setting operation or the like of the user interface 212 to the following equation (1). In addition, the spectral calculation unit 220a applies measured values (that is, peak wavelengths λ1 to λ4 measured by the spectroscopic instrument 210b) to the following equation (1) instead of the target values in order to improve the accuracy of the spectral data. May be. Further, in order to improve the accuracy of the spectroscopic data, the spectroscopic calculation unit 220a calculates, for example, Cy (λn), the transmittance of the Cy filter with respect to the peak wavelength λn, and the intensity of the peak wavelength λn measured by the spectrophotometer 210b. A multiplied value may be used. The same applies to Mg (λn), Ye (λn), and G (λn).

  From the above formula (1), the spectral reflected light intensity illumi (λ1) to illumi (λ4) of the peak wavelengths λ1 to λ4, that is, four spectral data of the subject are calculated simultaneously from the output values of the respective color pixels. Since the solid-state imaging device having the Bayer-type pixel arrangement is an RGB three-color filter, when the calculation is performed in the same manner as in the above formula (1) using the output values of the RGB pixels, a maximum of three spectral data can be obtained. It can be calculated simultaneously. That is, the maximum number of spectral data that can be calculated simultaneously is equal to the number of colors that constitute the color filter of the solid-state imaging device.

<Spectroscopic data collection processing>
FIG. 3 is a flowchart showing spectral data collection processing executed in the electronic endoscope system 1 of the present embodiment. In the spectral data collection process, spectral data of a subject is collected in 5 nm increments (61 spectral data in total) in a predetermined wavelength range (for example, 400 nm to 700 nm). For convenience of explanation, the processing step is abbreviated as “S” in the description and drawings in this specification.

<S1 in FIG. 3 (calculation of initial applied voltage to the spectrometer 210a)>
When execution of the spectral data collection process is started, the spectroscope control unit 210c calculates an initial voltage to be applied to the spectroscope 210a based on a predetermined initial target peak wavelength. For example, the initial voltage is set to such a value that peaks appear at four locations of 400 nm to 700 nm in order to simultaneously calculate four pieces of spectral data of the subject. Note that the execution of the spectral data collection process is started by, for example, a transition from the normal observation mode to the spectral data collection mode or a start operation to the user interface 212 as a trigger.

  In the variable gap etalon, the peak wavelength appears periodically at discrete positions in the spectral distribution in principle. For this reason, it is not possible to give a peak only to four consecutive wavelengths of 5 nm within 400 nm to 700 nm. Therefore, in the spectral data collection process of FIG. 3, spectral data of a plurality of discrete peak wavelengths within 400 nm to 700 nm are collected, and this collection operation is repeated until there is no spectral data of uncollected peak wavelengths. Finally, when a total of 61 pieces of spectral data in 5 nm increments within 400 nm to 700 nm are collected, this spectral data collection process ends. Note that the number of spectral data collected at one time (in other words, the number of target peak wavelengths and the number of peak wavelengths in the band-limited light) is not always four, and the distribution of uncollected spectral data It may be reduced to 1 to 3 depending on the remaining number.

<S2 in FIG. 3 (voltage application to the spectroscope 210a)>
The spectroscope control unit 210c applies the calculated voltage to the spectroscope 210a. The spectroscope 210a to which the voltage is applied splits the irradiation light incident from the lamp 208 into band-limited light having a peak wavelength that substantially matches the target peak wavelength.

<S3 in FIG. 3 (Measurement of spectral characteristics of band-limited light)>
The spectrometer 210b measures the spectral characteristics of the band-limited light emitted from the spectrometer 210a. The measurement value obtained by the spectrometer 210b is input to the spectrometer control unit 210c.

<S4, 5 in FIG. 3 (control of measured peak wavelength)>
The spectrometer control unit 210c calculates a peak wavelength (hereinafter referred to as “measured peak wavelength”) from the spectral characteristics of the band-limited light input from the spectrometer 210b. The spectroscope control unit 210c determines whether or not the calculated actual peak wavelength falls within an allowable tolerance based on the target peak wavelength. If a plurality of target peak wavelengths are set, it is determined whether or not all of the corresponding actually measured peak wavelengths fall within the allowable tolerance. If the measured peak wavelength (at least one in the case of a plurality) deviates from the allowable tolerance (S4: NO in FIG. 3), a correction voltage value based on the difference between the measured peak wavelength and the target peak wavelength is calculated (FIG. 3). S5), the corrected voltage is applied to the spectroscope 210a (S2 in FIG. 3). The loop of S4, S5, S2, S3, S4... In FIG. 3 continues until the measured peak wavelength falls within the allowable tolerance. When the actually measured peak wavelengths (all in the case of a plurality) fall within the allowable tolerance (S4 in FIG. 3: YES), the process proceeds to S6 in FIG.

<S6 in FIG. 3 (Spectroscopic Data Collection)>
The spectroscope control unit 210c transfers information (wavelength and intensity) of the actually measured peak wavelength falling within the allowable tolerance to the spectroscopic calculation unit 220a. The spectral calculation unit 220a reads the transmittances of the Cy filter, Mg filter, Ye filter, and G filter for the measured peak wavelength from the storage medium such as the data storage unit 220c, and multiplies the measured peak wavelength by the intensity. Then, the spectral reflected light intensity (spectral data) at the maximum of four peak wavelengths λn is calculated using the imaging signal from the solid-state imaging device 108 input via the driver signal processing circuit 112. The calculated spectral data is transferred to the spectral analysis unit 220b and stored in the data storage unit 220c.

<S7, 8 in FIG. 3 (collection completion determination)>
The spectroscopic calculation unit 220a determines whether there is no spectral data of uncollected peak wavelengths, that is, whether all the spectral data of 61 peak wavelengths distributed in increments of 5 nm within 400 nm to 700 nm are collected. When there is spectral data of uncollected peak wavelengths (S7: NO in FIG. 3), the spectroscope control unit 210c receives the determination result of the spectroscopic calculation unit 220a and applies an applied voltage corresponding to the next target peak wavelength. Calculation is performed (S8 in FIG. 3), and the calculated voltage is applied to the spectroscope 210a (S2 in FIG. 3). When all the spectral data of the peak wavelength of the total 61 are collected (S7: YES in FIG. 3), the spectral data collection process in FIG. Note that the order of the target peak wavelengths to be set is determined in advance, and when the spectral data corresponding to all the target peak wavelengths are collected in accordance with the order, the spectral data of the actually measured peak wavelengths of 61 in total are prepared. Become.

  The spectral analysis unit 220b analyzes the spectral data group collected by the spectral data collection process of FIG. 3 to detect the health or abnormality of the subject (eg, suspected lesion), and uses the detection result to analyze the image (eg, abnormal). A part-enhanced image or the like) is generated. The generated analysis image is output to the monitor 300 through the image integration unit 220d, for example, and displayed on the display screen. The analysis image is displayed on the display screen of the monitor 300 after being synthesized with a normal color image taken in the normal observation mode by the image integration unit 220d. As the composite display, for example, an aspect in which an analysis image and a normal color image are displayed in parallel, or an aspect in which an analysis image and a normal color image are superimposed and displayed are assumed. The analysis image is stored in the data storage unit 220c and transferred to an external device (for example, a PC, a file server, an external storage medium, a sub display, etc.) via the data storage unit 220c. Note that the data storage unit 220c can also transfer the spectral data itself collected by the spectral data collection process of FIG. 3 to an external device (for example, a PC, a file server, an external storage medium, etc.).

  According to the present embodiment, high-quality spectral data can be collected by using the spectroscope 210a, and a color imaging element (solid-state imaging element 108) widely used in recent years, and a plurality of transmission peak wavelengths By using the spectroscope 210a capable of setting the spectral data, it is possible to simultaneously collect spectral data of a plurality of peak wavelengths. Therefore, it is possible to shorten the spectral data collection time. That is, according to the present invention, more high-quality spectral data can be collected within a limited time, so that the accuracy of processing using spectral data such as spectral analysis is improved.

  In addition, the electronic scope 100 according to the present embodiment does not need to include a dedicated component for collecting spectral data, and thus an existing configuration is sufficient.

  The above is the description of the embodiment of the present invention. The present invention is not limited to the above-described configuration, and various modifications can be made within the scope of the technical idea of the present invention. For example, in the present embodiment, the actuator 210ACT is driven to selectively insert the spectroscope 210a in the optical path of the irradiation light. In another embodiment, the rotation shown in FIG. You may replace with the structure provided with the type | formula filter turret. Specifically, the rotary filter turret 210FT is installed in place of the spectroscope 210a. As shown in FIG. 4A, a spectral filter (gap variable etalon or the like) and a white filter are provided. It is arranged in the circumferential direction. The white filter limits, for example, the irradiation light emitted from the lamp 208 to a predetermined visible light range. Further, as shown in FIG. 4B, the rotary filter turret 210FT 'has a spectral filter, a white filter, and a special observation filter arranged in the circumferential direction. The special observation filter has spectral characteristics optimized for specific narrow-band observation. The actuator 210ACT can selectively insert any one filter in the optical path of the irradiation light by rotating the rotary filter turret 210FT or 210FT '. In the example shown in FIG. 4A, spectral data collection and normal color image acquisition can be performed alternately by rotating the rotary filter turret 210FT at a predetermined cycle.

  FIG. 5 is a block diagram showing a configuration of Modification 1 (electronic endoscope system 1Ma) of the electronic endoscope system 1 according to the present embodiment. In the first and subsequent modifications, the same or similar components as those in the electronic endoscope system 1 in FIG. 1 are denoted by the same or similar reference numerals, and description thereof will be simplified or omitted.

  As shown in FIG. 5, the electronic endoscope system 1Ma includes mirrors 210M1 to M4 that are arranged so as to bypass an optical path that goes straight from the lamp 208 to the spectroscope 210a. The mirrors 210M1 and 210M4 are, for example, movable switching mirrors, and retract from the optical path in the first switching state. Therefore, the irradiation light radiated from the lamp 208 passes through the mirror 210M1 and passes through the spectroscope 210a to be band-limited light, and then passes through the mirror 210M4 and enters the incident end of the LCB 102. The mirrors 210M1 and 210M4 are inserted in the optical path in the second switching state. The mirror 210M1 reflects the irradiation light emitted from the lamp 208 toward the mirror 210M2. The mirrors 210M2 and 210M3 are fixed mirrors. The irradiation light reflected by the mirror 210M1 is sequentially reflected by the mirrors 210M2 to M4 and enters the incident end of the LCB 102. That is, in this case, white light that does not pass through the spectroscope 210 a is supplied to the LCB 102. The mirrors 210M1 and M4 may be dimming mirrors that can switch the transmittance (transparent state and reflective state) according to the applied voltage, for example, instead of the movable switching mirror.

  FIG. 6 is a block diagram showing a configuration of Modification 2 (electronic endoscope system 1Mb) of the electronic endoscope system 1 of the present embodiment. As shown in FIG. 6, in the electronic endoscope system 1 </ b> Mb of the second modification, the electronic scope 100 includes a spectroscopic unit 210. The spectroscopic unit 210 is installed, for example, in the optical path between the objective optical system 106 and the solid-state image sensor 108. In addition to the spectroscopic unit 210, the spectroscopic calculation unit 220a may also be installed in the electronic scope 100.

  In the electronic endoscope system 1Mb according to the second modification shown in FIG. 6, a normal color image cannot be taken. Therefore, FIGS. 7 and 8 illustrate the configurations of Modification Example 3 (Electronic Endoscope System 1Mc) and Modification Example 4 (Electronic Endoscope System 1Md) of the electronic endoscope system 1 of the present embodiment, respectively. .

  As shown in FIG. 7, also in the electronic endoscope system 1 Mc of the third modification, the electronic scope 100 includes a spectroscopic unit 210. However, in the third modification, the mirror 210M1 is disposed in the optical path between the objective optical system 106 and the spectroscope 210a, and the reflected light from the subject is transmitted or reflected according to the switching state. In the first switching state, since the reflected light is passed through the spectrometer 210a, the band-limited light transmitted through the spectrometer 210a is incident on the solid-state image sensor 108. In the second switching state, the reflected light is reflected toward the mirror 210M2. The reflected light reflected by the mirror 210M1 is further reflected by the mirror 210M2 and enters the solid-state image sensor 108. That is, reflected light that does not pass through the spectroscope 210a is incident on the solid-state imaging device 108.

  Further, as shown in FIG. 8, also in the electronic endoscope system 1Md according to the fourth modification, the electronic scope 100 includes a spectroscopic unit 210. In the fourth modification, a solid-state imaging element 108M is arranged instead of the mirror 210M2 in the third modification. Therefore, in the first switching state, band-limited light that has passed through the spectroscope 210a is incident on the solid-state image sensor 108, and in the second switching state, reflected light that does not pass through the spectroscope 210a is incident on the solid-state image sensor 108M. . Further, by setting the transmittance: reflectance of the mirror 210M1 (light control mirror) to 1: 1, for example, reflected light from the subject is incident on both the solid-state imaging devices 108 and 108M. Therefore, it is possible to simultaneously collect spectral data and acquire a color image.

1, 1Ma, 1Mb, 1Mc, 1Md Electronic endoscope system 100 Electronic scope 102 LCB
104 Light distribution lens 106 Objective optical system 108, 108M Solid-state imaging device 110 Preamplifier 112 Driver signal processing circuit 114 Mode switching button 200 Processor 202 System controller 204 Timing controller 206 Lamp power source igniter 208 Lamp 210 Spectrometer unit 210a Spectrometer 210b Spectrometer 210c Spectroscope control unit 210d Half mirror 210ACT Actuator 210FT, FT 'Rotating filter turret 210M1-M4 Mirror 212 User interface 220 Signal processing circuit 220a Spectral calculation unit 220b Spectral analysis unit 220c Spectral data storage unit 220d Image integration unit

Claims (7)

A light source that emits irradiation light irradiated to the subject;
A filter that separates the irradiation light or the reflected light from the subject into spectral light having a plurality of peak wavelengths, and a transmission wavelength variable filter in which the peak wavelength of the light to be dispersed is variable;
A color filter array group including a plurality of predetermined color filter arrays is installed on the image sensor surface, and a subject image to which the spectral characteristics of the transmission wavelength variable filter are added is photographed through the color filter array group. An image pickup device for generating an image pickup signal having color information,
A spectroscopic measuring means for measuring spectral characteristics of the spectral light split by the transmission wavelength variable filter;
Measured by the imaging signal of the subject generated by the imaging device, the spectral characteristics of the color filters for each peak wavelength set by the transmission wavelength variable filter at the time of photographing the subject , and the spectral measurement means Spectroscopic calculation means for calculating the intensity of light of each peak wavelength incident on the image sensor from the subject based on the spectral characteristics of the spectroscopic light ,
Equipped with a,
Spectroscopic data collection system. A filter that drives and controls the transmission wavelength variable filter so that the peak wavelength of the spectral light by the transmission wavelength variable filter changes each time the light intensity of the plurality of peak wavelengths is calculated by the spectral calculation means. A drive control means ;
The spectral data collection system according to claim 1.   The filter drive control means includes
    In calculating the intensity of the light of the plurality of peak wavelengths in the spectroscopic calculation unit, until each of the plurality of peak wavelengths of the spectroscopic light measured by the spectroscopic measurement unit converges to a target peak wavelength, Driving and controlling the transmission wavelength variable filter to adjust the peak wavelength of the spectral light by the transmission wavelength variable filter;
The spectral data collection system according to claim 2. A rotary filter turret in which the transmission wavelength variable filter and at least one filter having spectral characteristics different from the transmission wavelength variable filter are arranged in a circumferential direction;
Turret drive control means for driving and controlling the rotary filter turret, and selectively inserting any one of the filters in the rotary filter turret into an optical path between the light source and the imaging device;
Further comprising,
The spectral data collection system according to any one of claims 1 to 3. A mirror that transmits or reflects the irradiation light;
Mirror drive control means for guiding the irradiation light to the first or second optical path by transmitting or reflecting the irradiation light by the mirror;
Further comprising
The transmission wavelength tunable filter is disposed in the first optical path,
The irradiation light guided to the first optical path irradiates the subject through the transmission wavelength variable filter,
Irradiation light guided to the second optical path irradiates the subject without passing through the transmission wavelength variable filter ,
The spectral data collection system according to any one of claims 1 to 3. A mirror that transmits or reflects the reflected light;
Mirror drive control means for guiding the reflected light to the first or second optical path by transmitting or reflecting the reflected light by the mirror;
Further comprising
The transmission wavelength tunable filter is disposed in the first optical path,
The reflected light guided to the first optical path enters the image sensor through the transmission wavelength variable filter,
Irradiation light guided to the second optical path enters the image sensor without passing through the transmission wavelength variable filter ,
The spectral data collection system according to any one of claims 1 to 3. An electronic endoscope system in which the spectral data collection system according to any one of claims 1 to 6 is incorporated,
A processor;
An electronic endoscope,
With
The electronic endoscope includes the imaging device,
The processor includes at least the light source, the transmission wavelength variable filter, and the spectral calculation means .
Electronic endoscope system.

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