JPH0380834A - Endoscope device - Google Patents

Abstract

PURPOSE:To execute the measurement of the blood flow rate and the oxygen saturation quantity of an interest area and to facilitate the time lapse comparison by providing an image file means for storing an image signal so as to be retrievable, an area designating means of a display, and an arithmetic processing means of the blood flow rate or the oxygen saturation degree. CONSTITUTION:Light beams of R, G and B are radiated to a body to be photographed from the tip through a light guide 21, and tits reflected light is brought to image formation on a CCD 32 by an objective lens system 31 and an image of the body to be photographed is brought to image pickup. Accordingly, on a monitor 7, a visible image is brought to color display. Also, a hemoglobin distribution image (IHb distribution image) and an oxygen saturation degree distribution image (SO2 distribution image) are displayed by allowing them to pass through a real time processing unit 6. On the other hand, with respect to an endoscope image obtained under a special light illumination or an arbitrary interest area of an image stored in an image file device 8, a blood flow analytic system 12 calculates an analytic image of a hemoglobin quantity distribution, an oxygen saturation degree distribution, etc., by using a computer 10. Also, since this device is provided with an image file means, the change with lapse of time in the condition of a disease at the position a patient is concerned can also be known.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to an endoscope apparatus having a function of calculating blood flow, oxygen saturation, etc. from an image of a subject.

[Prior Art] In recent years, various studies have been conducted to clarify the relationship between blood flow in the mucous membranes of organs such as the stomach and diseases, and attempts have been made to calculate blood flow and oxygen saturation to aid in diagnosis. It is being said.

In the document "Medical Coarse Range Spectrum Analysis V Device"("LaserResearch" 1985 Vol. 13, No. 2@, written by Jun Hiraki and Masahiko Kanda), the spectral reflection spectrum of the gastric mucosa was measured and the absorbance was determined. It has been shown that there is a certain correlation between blood flow rate (hemoglobin amount) and oxygen saturation. Figure 17 shows the absorption spectrum of hemoglobin in human blood.

In the figure, at the two points of wavelength 569 nm (nanometers, same below) and wavelength 586 nm, the spectral values do not change (fixed point ),
At the wavelength of 577 nm, the absorption increases as 302 increases,
Conversely, in terms of wavelength 650 n1ll, if 302 increases, it decreases.

Utilizing these characteristics, oxygen saturation (802
> and the blood flow rate (hemoglobin MT b) can be determined using the formula % and I Hb = 200C.

By the way, if the above-mentioned spectrum measurement is performed on each point on the surface of the mucous membrane, it will take a long time to investigate the entire wide surface.

In endoscopy, this type of investigation method is particularly impractical because it causes considerable pain to the patient and because the object to be measured, such as the stomach, is constantly moving due to the beating of the heart.

Therefore, it has been desired to be able to measure blood flow and oxygen saturation distribution as two-dimensional image information in a short time.

For this reason, Japanese Patent Application Laid-Open No. 63-311937 discloses an endoscope apparatus that can rapidly obtain blood flow and oxygen saturation imaging such as two-dimensional prepackaging PLA.

Problems to be Solved by the Invention The conventional example of the above publication obtains two-dimensional imaging of blood flow and oxygen saturation in the gastric mucosa, etc. Direct reading was difficult.

Furthermore, since there is no image file function, it is difficult to observe and measure the same patient over time.

The present invention has been made in view of the above points, and is capable of measuring blood flow and oxygen saturation in any region of interest in the gastric mucosa, etc., and recording multiple images.
It is an object of the present invention to provide an endoscope device that has a readable file function and allows easy comparison over time.

[Means and effects for solving the problem] The present invention provides an image file means for retrieably recording an image signal transmitted by light passing through a plurality of narrow band filters, and an image file means for retrieably recording an image signal transmitted by light passing through a plurality of narrow band filters, and By providing an area specifying means for specifying an area using a specified area, and an arithmetic processing means for calculating a blood flow rate or oxygen saturation level for the specified area specification, the blood flow rate or oxygen saturation level for a desired image area can be calculated. The degree can be calculated as a numerical value. or,
By using the image file means, it is possible to record images, search recorded images, and easily examine changes over time.

[Example] Hereinafter, the present invention will be specifically described with reference to the drawings.

1 to 16 relate to one embodiment of the present invention;
The figure is a block diagram showing the overall configuration of one embodiment, and the second figure is a block diagram showing the overall configuration of one embodiment.
FIG. 3 is a block diagram showing the structure of the video processor, etc., FIG. 4 is a front view showing the structure of the rotating filter, and FIG. 5 is a characteristic diagram showing the transmission characteristics of the rotating filter. , FIG. 6 is a characteristic diagram showing changes in blood absorbance due to changes in oxygen saturation of hemoglobin, FIG. 7 is a block diagram showing the configuration of a real-time processing unit, and FIG.
Figure 9 is a flow diagram showing the overall processing of the blood flow analysis system, Figure 9 is an explanatory diagram showing the selection menu for setting processing conditions, Figure 1
Figure 0 is an explanatory diagram showing how only the image part is cut out,
Figure 11 is a flow diagram of the itching process to determine hemoglobin a, Figure 12 is a flow diagram of the calculation process to determine oxygen saturation,
Fig. 13 is an explanatory diagram showing that a scale is displayed near the image output to the CRT, Fig. 14 is an explanatory diagram showing the area specification menu, and Fig. 15 is an explanatory diagram showing the area specified by area specification. FIG. 16 is an explanatory diagram showing how a region is specified.

As shown in FIG. 1 or 2, an embodiment of the endoscope apparatus 1
comprises an electronic endoscope 2 equipped with an imaging means, a light source device 3 that supplies illumination light to the electronic endoscope 2, and a signal processing circuit 4 (
(See Figure 3) is connected to the video processor 5, which processes the oxygen saturation amount, etc. in real time! ial! ! unit 6 and an image display color monitor (CRT
) 7 connected to the video processor 5;
An image file device 8 that records images output from the video processor 5 together with search data and allows the recorded images to be searched; )
9. An image processing computer 10 that performs image processing on the image of the image file device 8; this computer 1o;
The blood flow analysis system 12 includes an operation monitor 11 that displays processing menus, etc.

The image file device 8 shown in FIG. 1 is built into the computer 10 in FIG. Also computer 10
The processed image can be displayed on the color monitor 9.

As shown in FIG. 2, the electronic endoscope 2 has an elongated and, for example, flexible insertion section 13. A large-diameter operating section 14 is connected to the two ends.

A flexible cable 15 extends laterally from the operating section 14, and a connector 16 is provided at the tip of the cable 15. This electronic endoscope 2 can be connected to the video processor 5 via the connector 16 described above.

On the distal end side of the insertion portion 13, there is a rigid distal end portion 17 and a bending aid portion 18 adjacent to the distal end portion 17 that can be bent rearward.
are set up in sequence. Furthermore, by rotating a bending operation knob 19 provided on the operating section 14, the curved surface section 18 can be bent in the left-right direction or the up-down direction. Further, the operating section 14 is provided with an insertion port 20 that is provided in the insertion section 13 and communicates with a treatment instrument channel.

As shown in FIG. 3, a light guide 21 for transmitting illumination light is inserted into the insertion section 13 of the electronic endoscope 2. As shown in FIG. This light guide 21 is connected to the cable 15 shown in FIG.
By passing through the light guide 21 and connecting it to the video processor 5, color-sequential illumination light is supplied from the light source device @3 to the end face of the light guide 21 on the incident side.

A lamp 2 that emits light by power supplied from a power source 22
The illumination light of No. 3 passes through the rotary filter 25 which is rotationally driven by the motor 24.
When the outermost part of the light beam is inserted in the optical path, the red light is attached in the circumferential direction.

The light of each wavelength of red, green, and blue is sequentially passed through the green and blue transmission filters 26R, 26G, and 26B, that is, the three primary colors are sequentially turned into light, and the end face of the light guide 21 is irradiated with the light.

The lamp 23 emits broadband light ranging from ultraviolet rays to infrared rays, and can be a xenon lamp, a strobe lamp, or the like.

The motor 24 is driven and controlled by a motor driver 28 so that its rotational speed is constant.

The illumination light transmitted by the light guide 21 is emitted forward from the end surface of the insertion section 13 on the distal end side. The object illuminated with this illumination light is imaged by an objective lens 31 attached to the distal end side of the insertion section 13 on a CCD 32 as a solid-state image sensor disposed at its focal plane.

This CCD 32 has sensitivity in a wide wavelength range from ultraviolet to infrared regions, including the visible region, photoelectrically converts the optical image formed on this CCD 32, and accumulates it as a signal charge.

The driving pulse transmitted from the driver 33 in the signal processing circuit 4 via the signal line 34a causes the CCD to
32 signal charges are read out and input to the preamplifier 35 in the signal processing circuit 4 via the signal line 34b.

The video signal amplified by the preamplifier 35 is input to a process circuit 36, where it undergoes signal processing such as γ correction and white balance, and is converted into a digital signal by an A/D converter 37. This digital video signal is selected, for example, as red (R) by the select circuit 38.

It is designed to be selectively stored in three first memories 39a, second memories 39b, and third memories 39C corresponding to each color of green (G> and blue (R).The above metlJ39a,
The No. 15 data stored in 39b and 39c are simultaneously read out, converted into analog signals by the A/D converter 41, outputted as R, G, and B color signals, and also manually inputted to the encoder 42. From NT
It is output as an SC composite signal.

The composite video signal output from the encoder 42 can be input to the color monitor 7 via the switch S, and the subject image is displayed in color.

The signal processing circuit 4 is provided with a timing generator 43 that generates the timing of the entire system, and the output signals of the timing generator 43 synchronize the motor driver 28 and driver 33 circuits.

In this embodiment, when the filter switching device 45 is controlled by the switching circuit 44 and the outermost portion of the rotary filter 25 is inserted into the illumination optical path, the light emitted from the lamp 23 is as shown in FIG. Provided at the outermost periphery of the rotary filter 24, R
, G, and B, and is sequentially divided into light in the R, G, and B wavelength ranges.

Incidentally, the transmission characteristics of these filters 26R, 26G, and 26B are shown in FIG. 5 (a>).

The R, G, and B lights are irradiated onto the subject from the tip of the light guide 21. R in this visible band
, G, B, the repulsion light from the subject due to the sequential illumination light is
An objective lens system 31 forms an image on a CCD 32, and a subject image is conveyed by this CCD 32. Therefore,
The monitor 7 displays 7J normal visible images.

On the other hand, in the switching circuit 44, the filter switching device 45
When the rotary filter 25 is moved downward, the fourth
Intermediate narrowband filter groups 51a and 5i shown in the figure
b, 51 C are successively interposed in the illumination optical path. Moving further downward, the innermost narrow band filter group 52a,
52b and 52c are sequentially interposed in the illumination optical path.

The narrowband filter groups 51a, 51b, and 51c are, for example, 211. in FIG. λ12. The transmission characteristics are shown in FIG. 5(b), which pass wavelength bands around λ13 as the center. In addition, each wavelength λ11. λ12. λ1
The wavelength band centered at Wl 1. Wl 2. Wl
Represented by 3.

Similarly, the narrow band filter groups 52a, 52b, 52C are
Wavelength λ21 in FIG. λ22. A narrow wavelength band W21. centered around λ23. W22. Only W23 is allowed to pass therethrough. In this example, the wavelength group (λ11
．． λ12. Two wavelength groups (λ11.λ12.λ13) and (λ13) to (λ51.λ52.λ53)
21°λ22. λ23), but by replacing the rotary filter 25, it is also possible to select other wavelength groups.

Therefore, when a wavelength band of the above wavelength group is selected, the light of the selected wavelength band passes through the light guide 21,
The light is transmitted to the tip 17 and irradiated onto the subject. The reflected light from the object caused by this illumination light is imaged on the CCD 32 by the objective lens 31, and by this CCD 32,
A subject image is captured. In this case, when the switch S outputs this signal to the monitor 7, the wavelength band W11. W1
2°Wl3 or W21. W22. By W23 (R.

A special light image is displayed in pseudo color with respect to the normal light image of the G and B filters.

Further, by passing the image through the real-time processing unit 6, a hemoglobin distribution image (IHb distribution image) and an oxygen saturation distribution image 61 (802 distribution image) are displayed.

Selected wavelength band W11. Wl 2. Wl3 or W
21. W22. Let each (center) wavelength of W23 be λ1. λ2.
As expressed by λ3, the above real-time processing unit 6
The structure and operation of this will be explained below with reference to FIG. Here, λ1°λ3 represents a wavelength at which the absorbance does not change at all due to SO2, and wavelength λ2 represents a wavelength at which the absorbance greatly changes due to SO2.

The wavelength λ1. λ2. A wavelength band W1. whose center wavelength is λ3. Signals conveyed under the illumination lights W2 and W3 (to make it easy to understand, these are also expressed as Wl, W2°W3) t and three selectors 61a, 61b, 61c with 3 manual outputs.
through the inverse γ correction circuits 62a, 62b, 62C, respectively.
is input. For example, the selector 61a selects the wavelength band W.
1, the selector 61b outputs an image signal corresponding to wavelength band W2, and the selector 61G outputs an image value g corresponding to wavelength band W3 to inverse γ correction circuits 62a, 62b, and 62c, respectively. The settings are as follows.

Since the inverse γ correction circuits 62a, 62b, and 62c have already performed γ correction in the video processor 5,
Inverse gamma correction is performed to restore this. The outputs of the inverse γ correction circuits 62a, 62b, and 62C are each sent to a level adjustment circuit 63a.

It is input to 63b and 63G. This level adjustment circuit 63
a, 63b, and 63c are level adjustment control signal generation circuits 6;
The level is adjusted by a level adjustment control signal from 4, and the overall level is adjusted by three level adjustment circuits 63a, 63b, and 63c. Furthermore, since the vertical axis of a diagram showing changes in blood absorbance due to changes in oxygen saturation, such as shown in FIG.
Logarithmic transformation is performed by amplifiers 65a, 65b, and 65c.

Two of the three log amplifiers 6
The outputs of 5a and 65c are input to a differential amplifier 66b,
The difference between the image signal corresponding to wavelength band W1 and the image signal corresponding to wavelength band W3 is calculated. Similarly, two log amplifiers 65b and 65c
The output of W is input to the differential amplifier 66a, and the output of W
The difference between the image signal corresponding to wavelength band W3 and the image signal corresponding to wavelength band W3 is calculated. In this way, it is possible to know how much oxygen has dissolved into the subject, that is, the oxygen saturation level, from the difference between the image signals corresponding to the two wavelengths. Also, the fact that a lot of oxygen is dissolved means that a lot of oxygen is being consumed, and this tells us how much blood flow is being carried out.

The output of the differential amplifiers 66a and 66b is the oxygen saturation S
It is used to calculate O2 and is input to the divider 67,
By performing a predetermined operation with this divider 67, the S
O2 is required. Further, the output 1ooW 1 - 1oaW 3 of the differential amplifier 66b represents hemoglobin l (I day b).

The output of the L divider 67 and the output of the differential amplifier 66b are:
A signal indicating SO2, blood flow rate, and hemoglobin ff1 (
One of the signals indicating "I day b>" is selectively output.

When the output signal of the selector 68 is used for measurement, it is taken out as is, but when it is displayed,
The γ correction circuit 69 performs γ correction again, and the monitor 7
is output to.

The above real-time processing unit 6 is 802 in video mode.
Distribution images and IHb distribution images can be displayed.

On the other hand, the blood flow analysis system 12 uses the computer 10 to analyze hemoglobin in an arbitrary region of interest in an endoscopic image obtained under special light illumination or an image stored in an image file system @8. Calculate analysis images such as volume distribution and oxygen saturation distribution.

In combination with a digital image input device, this blood flow analysis system 12 allows input/output, condition setting, and processing to be performed interactively within one program.

Therefore, as the image processing computer 10, for example, a PC-9801RA5 (calculator body and 40 Mb
The execution environment uses a 32-bit CPU (30386<Intel) and several fl.
Used with i-arithmetic processor 30387.

In this embodiment, the image file device 8 is a 40 Mb built-in computer PC-9801RA5.
It consists of a yt hard disk.

The computer 10 also has a frame memory for image storage (for example, Δ5TRODESIGN GG125-A/
D) was installed and used. In addition, in this viewer 10, in order to set an arbitrary region of interest, the mouse 71
For example, a PC-9872U) is connected. Furthermore, each menu can be selected using only the function keys of the keyboard 72, for example.

For example, a PC-KD853 can be used as the monitor 11 for performing the operating procedures and the like using the computer 10 in an interactive manner.

Also, as the monitor 9 for displaying the processed image, for example, a 5ON
PVM-1371Q of Y can be used.

The input image input to the computer 10 is as follows:
Endoscopic images from a digital image input device (e.g. 51
2 x 480 dots, integer 1 byte x 3) and numerical data image processed by this program (e.g. 365 x 385
dot, real number 4 bytes) F.

The processing contents by this computer 10 include arithmetic processing (for example, with real number 4-byte data) and (for example, 365-byte data)
Processes are performed to create black and white image data (eg, 365 x 385 dots, 1 byte integer data) and pseudo color data (eg, 365 x 385 dots, 1 byte integer x 3 data).

The above calculation processing includes calculation of a hemoglobin amount distribution image (abbreviated as I-day distribution image), and calculation of an oxygen saturation distribution image (802
Calculate the distribution image (abbreviated as distribution image).

Furthermore, the creation of black and white image data involves expanding the display range by converting the real value image of the I-day or 302 distribution image into an integer and flattening the histogram.

The creation of pseudo color data involves converting the black and white image data into pseudo colors (32 colors).

Also, the output image is, for example, 365 x 385 dots.
, is output as a numerical data image in 4-byte real numbers.

Next, the processing flow of the system 12 will be explained below with reference to FIG.

When the program of the system 12 is started, the menu for processing P1 for setting image input conditions is displayed on the monitor 11. A selection is made and a hard disk or floppy disk is selected as the input medium.

If an unprocessed image is selected in the above selection, processing P2 for setting processing conditions shown in FIG. 9 is performed. In other words, SO2 or IH
A selection is made as to which process is to be performed.

Next, in the image input and cropping process P3, the endoscopic image is transferred to the frame memory, and as shown in Fig. 10, unnecessary areas or errors are removed from the entire endoscopic image for calculation processing of patient data, etc. Processing is performed to extract only the image part by cutting the area.

Next, inverse γ correction processing P4 is performed. Since γ correction has been performed on the unprocessed image (endoscopic image), the image is returned to an image without γ correction by inverse γ correction.

Next, calculation processing P5 calculates IHb or 802 shown in FIG. 11 or 12, and the processing result is used in data storage processing P6, data storage & CRT output processing P7, or CRT output processing P8. Perform either process.

The data storage process P6 is to save the numerical data image calculated for IHb or SO2, and the CRT output process P8 is to convert it into black and white or pseudo color and output it to the CRT9. Also, data storage & CRT output processing P
7 performs both P6 and P8 processing.

On the other hand, if the processed image is selected, the output condition setting process P9 selects whether to output it in black and white or pseudo color, and the next image input process P10 stores the numerical data image in the frame memory. Make a transfer.

When this transfer to the frame memory is performed, the processed image is displayed on the CRT 9 through CRT output processing P8.

Then, by area designation and numerical output processing P11 for the image displayed on the CRT 9, numerical data for the designated point or designated area is displayed on the CRT 11 through the processing shown in FIG. Therefore, if you specify a region of interest with the mouse 71, IH in the specified region
The numerical data of SO2 is calculated and the result is C
Displayed on RTI 1.

Next, each process will be explained.

In the image input condition setting process P1, an unprocessed image or a processed image is selected as the input image condition, and a hard disk or floppy disk is selected as the input medium. Incidentally, when the unprocessed image is recorded on the hard disk as the image file storage 8, the image data is recorded together with secondary data for retrieval such as patient data and date. Therefore, when searching, patient data, dates, etc. can be used.

In the process P1, if an unprocessed image and a hard disk are selected, the image selection routine of the digital image input device is used, and otherwise the file name is entered manually.

The input image is, for example, 51 for unprocessed endoscopic images.
For example, a processed numerical data image of 2×480 dots and 1 byte of integer is composed of 365×385 dots and 4 bytes of real number.

Regarding the processed image, numerical parameters (maximum value, minimum value) are attached to the beginning of the image data.

Next, processing condition setting process fP2 when an unprocessed image is selected and output condition setting process P9 when a processed image is selected will be described.

In these cases, as shown in FIG. 9, selection of port b302 or selection of wavelength band W1. W2. selection of W3, selection of black and white or pseudo color output format, selection of whether to output CRT output, selection of whether to save data or not, and whether to save data to a hard disk or floppy disk. Configure the file name, etc.

In the case of processed images, the only items that can be selected are the output formats, YES for CRT output, and No for data storage.
becomes.

By making it possible to select the wavelength band, it is possible to deal with cases where light source devices have different filter configurations.

For unprocessed images, perform the next image input & cropping process P3
For example, 512X480 dots, integer i byte
FIG. 10 shows how only an image portion of 365 x 385 dots is extracted from the entire endoscope screen. ) R
GF3IvA is stored in a separate array.

On the other hand, in image input processing P10 for the processed image, two numerical parameters (maximum value, minimum value) at the beginning of the file are read, and then the image data (365
x 385 dots, real number 4 bytes).

The image data that has been subjected to the image input and cropping process P3 is converted into an input image by the inverse γ correction process P4.
If the corrected output image is DAout, then DAout = (DAin) ``'' processing is performed on all image partial data.

Thereafter, arithmetic processing P5 is performed.

This calculation process P5 is as shown in FIG.
Regarding O2, the process shown in FIG. 12 is performed.

When the process shown in FIG. 11 starts, initial settings are first performed.

In other words, the two wavelengths λ1. λ
Each image data obtained under 3 illuminations is stored in an image storage area 1maae W1 (X 5ize.

Y 5ize), In1aoe W3 (X 5
ize, Y 5ize). Here x
5ize, y 5ize is gA in the x direction and Y direction
Represents the size of bX.

In addition, the IHb data storage area rHb (X 5iz
e.

Y 5ize) is also initialized, and the variable X used for calculation processing is
.

y is also initialized by assigning O.

After this initial setting process, arithmetic processing is performed.

In other words, the variable N is increased by 1, the variable X is also increased by 1, and the value of I for these numbers (x, y) is
Find Hb (X, V>. In other words, 10G (III
age-11? (X, V)) -10g(ImaGe-
W3(X,V)) and convert this value into Idayb(x
, y>.

Next, if this value of X is within the size of the image data area in the The area in the x direction for the value (in this case, 1)
Since It-1b for all ze is calculated, next y
By increasing the value of 1 by 1 and repeating the same process, the image data area 1i11X 5ize, Y
It-1b for all 5ize is calculated, and the calculation for calculating this one-day count is completed.

Further, the arithmetic processing of SO2 shown in FIG. 12 is similar to that shown in FIG. 11.

In the calculation process of S02, the initial setting is 1 sip, and the image data at wavelength 22 is further stored in the image data storage area Tmage W2 in the frame memory.
(X 5ize, Y 5ize) and I
Instead of Hb (X 5ize, Y 5ize), the data storage area VASo2 of S02 (X 5ize,
Y 5ize).

In addition, in the arithmetic processing, instead of the calculation to obtain (x, y) (x, y) in FIG. 11, the following is calculated and substituted into 802 (X, y).

The rest is the same as in FIG. 11.

In this way, the value of (l-1b, SO2) is determined for each pixel of the image data by the arithmetic processing P5, and is stored as array data in the frame memory corresponding to each pixel of the image data.

Incidentally, the maximum value and minimum value of (2) mouth b, 802 are also calculated.

Therefore, in the data storage process P6, the maximum value and minimum value are also stored together with the result.

In addition, in CRT output processing P8, the calculation result, the maximum value (M
AX) and the minimum value (MIN) to perform normalization processing.

In other words, DA out = (DA in - HIM)/
(HAX-MIN). Furthermore, the histogram is flattened and a rough γ correction is performed, that is, D A out = (D A in) 0.45.

Thereafter, black and white image formation processing, for example DAout =N INT [255xDAinl, is performed. Here, NINT[] means converting into an integer by rounding off.

Also, pseudo color data is created. Based on the above black and white data, it is converted into, for example, 32 colors.

The 32 colors are C0LORR (1), C0LORG (1
), C0LORB(1), and (7) are prepared in advance in three arrays (here, 1=1 to 32). Moreover, this ■ is determined by I=INT [DAin/8] +1.

However, INT[] means to truncate the decimal point.

As other processing in this CRT output processing P8, in the case of a black and white image, gray scale (0 to 255)
In the case of pseudo color, a color scale (32 colors) is output. This situation is shown in FIG. That is, the scale is displayed on the right side of the image, for example, with a size of 20×256 degrees Celsius.

Gray is represented by 0 to 255 continuously, and color is represented by 20×8 blocks.

Further, data storage and CRT output processing P7 for unprocessed images is a combination of P6 and P8.

Next, the area designation & numerical value output processing P11 will be explained.

In this embodiment, the first method of specifying an image displayed on the CRT 9 using the mouse 71 as an area specifying means is used.
As shown in Figure 4, one point designation or rectangular designation can be selected.

The point or area specified with the mouse 71 is displayed on the screen. In other words, it is displayed on Xl and Vl as specified coordinates,
In the case of a rectangular area, the upper left point of the area is displayed in xl and yl, and 5IZE X.

5IZE Y displays the size in the X direction and Y direction.

It should be noted that the display in the square corner of FIG. 14 is displayed after the specified routine using the mouse 71 is completed. However, for processed images, the processing condition settings become the output conditions.

When a region of interest is specified using the mouse 71, the data of the I date or 302 corresponding to the region, which has been determined in advance by arithmetic processing, is read out, and in the case of one point specified, the read data is , if a rectangle is specified, the total average value within that area is calculated and displayed.

The above area specification & numerical output process P11 is the first step.
This will be explained below with reference to FIG.

When the area designation & numerical output process P11 starts, a menu as shown in FIG. 14 appears, and the area designation method is set as one point designation or rectangular designation.

In the case of specifying one point, operate the mouse 71 to move the cursor to the desired location, press the set button to specify the coordinates (xl, yl) of the cursor point, and the computer 10 will correspond to the coordinate point. The numerical data for each sip or SO2 is read in. Then, the read data is displayed.

On the other hand, when a rectangle is specified, the coordinates of two points (x1, n1), (
×2. ×2).

In this case, by specifying the first point, the upper left coordinates (×1, yl
) is determined, and by specifying the next point, its coordinates in the direction of the phantom line (
×2. ×2) is determined.

Once the coordinates (xl, yl) and (x2.x2:) of the two points are determined, the numerical data within this rectangular area is read.

In other words, after the numerical data (accumulation) variable Total and the measurement point counter Count are set to O, the coordinate variable y
y1+1 is assigned to , x1+1 is assigned to
2 data are added, and the jj counter Count is incremented by 1. Therefore, this coordinate variable X is coordinate x 2
If it is smaller, increase the value of
Add (X, y) to the variable Total. In this way, the numerical data of all the X coordinates from x1 to x2 are cumulatively added to the y value, and then the y value is increased one by one, and eventually the coordinates of all the rectangular areas are The total amount of numerical data is calculated. Therefore, the value obtained by dividing this total amount by the value of the counter (:, ount) representing the size of the fi area is assigned to the IHb or SO2 data □ata, and the result is displayed on the CRTll.

For other points as well, if you select ``YES'' as to whether to continue if you want to obtain one bite or SO2, the process returns to the area specification method setting process. Also, if you select NO, the process will end.

According to this embodiment, by specifying the region of interest, I)-1b or S02 for a desired region can be obtained as a numerical value.

Furthermore, since it is equipped with an image file means, it is also possible to know, for example, changes over time in symptoms at a site of interest for the same patient.

In other words, by comparing the specific values of IHb or 802 for the same patient at the same site on different dates or times, you can determine how quickly the treatment is progressing or whether the symptoms are progressing. You can easily find out if there are any.

In addition, since changes over time can be easily determined in this way, it can be determined in a short time whether or not the treatment with drugs or other means is effective against the symptom.

Therefore, it is possible to provide useful data for diagnosis and other purposes.

In the above embodiment, the rotary filter 25 usually has R, G
, B color transmission filters 26R, 26G.

26B and the narrow band filters 51a, . . . , 52G are installed, but they may be provided separately.

Further, the present invention is not limited to the one using the electronic endoscope 2, but can be similarly applied to an optical endoscope such as a fiberscope with a television camera attached to the eyepiece.

In the above-described embodiment, the real-time processing unit 6 processes the IHb or SO2 distribution image in real time and is capable of displaying the processed image, but it also includes an accumulation means and a gate means that can be opened and closed υ controlled arbitrarily. , open the gate for the image part specified by the fin specifying means, accumulate the sum using the cumulative means, and divide by the time when the gate was opened to calculate the total amount of data for the specified area. 3
It is also possible to calculate 02 in real time or in a processing time close to this. Further, the real-time processing unit 6 can also be configured to display the IHb distribution image 802 distribution image or the IHb and SO2 for a designated area on the image read from the image file means.

Note that a light bar, a cursor mover on a keyboard, or the like may be used as the area specifying means.

[Effects of the Invention] As described above, according to the present invention, distribution images of blood flow and oxygen saturation can be obtained, and numerical data of blood flow and oxygen saturation can be obtained for any region of interest. It can be calculated. Furthermore, since it is equipped with an image file means, it is possible to measure changes over time, and the ability to diagnose lesions etc. can be improved.

[Brief explanation of drawings]

1 to 16 relate to one embodiment of the present invention;
Figure 2 is a block diagram showing the overall 4R command of the first embodiment, Figure 2 is a perspective view showing the overall configuration of the first embodiment, Figure 3 is a block diagram showing the configuration of the video processor, etc., and Figure 4 is the rotary filter. A front view showing the configuration, Fig. 5 is a characteristic diagram showing the transmission characteristics of the rotating filter, Fig. 6 is a characteristic diagram showing changes in blood absorbance due to changes in oxygen saturation of hemoglobin, and Fig. 7 is a real-time processing unit. FIG. 8 is a flow diagram showing the overall processing of the blood flow analysis system; FIG. 9 is an explanatory diagram showing the selection menu for setting processing conditions;
Fig. 10 is an explanatory diagram showing how only the image portion is cut out, Fig. 11 is a flow diagram of the focusing process for determining the amount of hemoglobin, Fig. 12 is a flow diagram of the @ line processing for determining the oxygen saturation level, and Fig. 13 is an explanatory diagram showing that the scale is displayed near the image output to the CRT, Fig. 14 is an explanatory diagram showing the area specification menu, and Fig. 15 is an explanatory diagram showing the area specification menu.
Specified I: A flowchart of the process for calculating the amount of hemoglobin or oxygen saturation for a region, FIG. 16 is an explanatory diagram showing how the region is designated, and FIG. It is a figure showing a absorption spectrum. 1... Endoscope @ 2... Electronic endoscope 3...
・Light source device 4... Signal processing circuit 5... Video processor 6... Real time processing unit 7.9.11... Monitor (CRT) 8... Image file device 10... Combi coater 1
2...Blood flow analysis system

Claims (1)

[Claims] an endoscope equipped with an imaging means, a signal processing means for obtaining images in a plurality of narrow band wavelength regions, an image file means for recording the images obtained by the signal processing means and data to be searched; An endoscope apparatus comprising: region specifying means for specifying a region of interest; and arithmetic processing means for calculating blood flow or oxygen saturation for the specified region of interest.