JP3051902B2 - Radiation image information reading and displaying device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a radiation image information reading and displaying apparatus for reading and displaying radiation image information stored and recorded on a stimulable phosphor.

[0002]

2. Description of the Related Art Conventionally, X-ray photography has been used to obtain radiographic images. This method allows a fluoroscopic image to be easily obtained in a subject, and has been widely used as an extremely powerful method, particularly in the field of diagnosis in medical treatment. However, this method has a small difference in the X-ray transmittance of each tissue in the human body, a low contrast of an image obtained because the X-rays are scattered in the subject, and a problem that the X-rays are harmful to the human body. However, there are drawbacks such as narrow latitude and severe shooting conditions. To compensate for these shortcomings,
Using an X-ray detector with high sensitivity and wide latitude,
A method of converting a line image into an electric signal and performing image processing to obtain a high-quality image with less influence on a human body has been sought.

As an example of such a radiographic method, radiation transmitted through a subject is absorbed and stored in a certain kind of phosphor, and then this phosphor is excited with a certain kind of energy to accumulate the phosphor. A method has been considered in which the emitted radiation energy is emitted as fluorescent light, and the fluorescent light is detected and imaged.

As a specific method, for example, US Pat.
859,527 and JP-A-55-12144,
A radiation image conversion method using a stimulable phosphor as a phosphor and using electromagnetic radiation selected from visible light and infrared light as excitation energy has been proposed.

In this method, a radiation image conversion panel having a stimulable phosphor layer formed on a support is used. The stimulable phosphor layer of the radiation image conversion panel absorbs radiation transmitted through a subject, and By accumulating radiation energy corresponding to the intensity of the light, and then scanning the stimulable phosphor layer with stimulating excitation light, the accumulated radiation energy is extracted as a light signal, and an image is formed by the intensity of the light. What you get.

[0006] The final image may be reproduced as a hard copy or on a picture tube such as a CRT.

The stimulable phosphor is a radiation (X-ray, α-ray)
Radiation, β-rays, γ-rays, ultraviolet rays, etc.), and when excited with a certain energy such as light or heat, the phosphor emits a photostimulated luminescence in accordance with the radiation energy stored in the phosphor. Refers to phosphor.

[0008] The radiation image conversion panel having a stimulable phosphor-containing layer herein means a plate (panel), drum or flexible film having a stimulable phosphor layer surface. Various forms, such as those to be made, are generically referred to (hereinafter simply referred to as conversion panels).

The above method has a very practical advantage in that an image can be recorded over a very wide radiation exposure area as compared with a conventional radiographic system using silver halide photography. That is, it has been recognized that the amount of radiation exposure in the conversion panel and the intensity or the amount of stimulated emission emitted by the stimulated excitation light after accumulation of the radiation are proportional to a very wide range. Even if the exposure amount fluctuates greatly, the reading gain of the stimulated emission is set to an appropriate value, read by a photoelectric conversion unit, converted into an electric signal, and a recording material such as a photographic light-sensitive material using the electric signal. By outputting a visible image on a display device such as a CRT, it is possible to obtain a radiation image that is not affected by a change in the radiation exposure amount.

According to this method, a radiographic image stored and recorded on the conversion panel is converted into an electric signal, and then subjected to appropriate signal processing. Using the electric signal, a recording material such as a photographic photosensitive material, a CRT, or the like is used. By outputting a visible image on a display device such as the one described above, an extremely great effect that a radiation image with excellent diagnostic suitability can be obtained can be expected.

[0011]

However, in order to eliminate the influence of fluctuations in imaging conditions and the like or to obtain a radiation image with excellent diagnostic adequacy as described above, the recording of the radiation image stored and recorded on the conversion panel is required. It is indispensable to perform appropriate signal processing on the radiation image based on the display of a visible image for observing and interpreting image information such as a state, a part of a subject, and an imaging method such as a simple contrast. For example, after reading a radiation image stored and recorded in the conversion panel and temporarily storing the radiation image in the image storage device, the image information of the radiation image is obtained by arithmetically processing the radiation image signal stored in the image storage device. The radiographic image is extracted, an appropriate image processing condition is obtained based on this information, and signal processing is performed based on the image processing condition, thereby obtaining a radiation image excellent in diagnosis appropriateness.

However, since the image processing conditions obtained by calculating the radiation image signal in this manner are obtained mechanically, it is difficult to cope with all the imaging conditions. In some cases, this is not the case. That is, it may not be possible to obtain a highly diagnostic image after reading the image.

An object of the present invention is to provide a radiation image information reading and displaying apparatus capable of obtaining an image having high diagnostic performance even when improper image processing is performed.

[0014]

The above object of the present invention can be achieved by the following constitutions.

Means for reading a radiation image conversion panel in which a radiation image is stored to obtain original image data;
Display means, means for obtaining a gradation processing condition corresponding to the radiographic image based on a frequency distribution of image data obtained by thinning out the original image data, Processing means for performing gradation processing based on the conditions, correction means for correcting the gradation processing conditions, and causing the display means to display an image based on the original image data in response to reading of the radiation image conversion panel, Almost simultaneously with the end of the reading, the image based on the displayed original image data is changed to an image based on the original image data on which the gradation processing has been performed, and further modified according to the operation of the modifying unit. Control means for changing to an image based on the original image data that has been subjected to the gradation processing based on the gradation processing conditions. Radiation image information reading display device comprising.

[0016]

[0017]

Embodiments of the present invention will be described below in detail with reference to the drawings.

FIG. 3 is a block diagram of a radiographic imaging apparatus according to the present invention, which is shown in the case of a chest radiographic apparatus. Radiation from the radiation source 21 is applied to the radiation conversion panel 23 through the chest region of the subject 22. The radiation conversion panel 23 is mounted on the front surface of the radiation image information recording / reading unit 24. Inside the radiation image information recording / reading unit 24, a light beam unit 41 using a semiconductor laser (this may be a gas laser or a solid-state laser), light The radiation conversion panel 23 includes a light scanner 42 that irradiates the light beam from the beam unit 41 and scans the radiation conversion panel 23, and a photoelectric converter 43 that detects stimulated emission light emitted from the radiation conversion panel 23. The photoelectric converter 43 includes a light collector 43a made of an optical fiber, a filter 43b that allows only light in the stimulated emission wavelength region to pass, and a photomultiplier 43c that converts the light passing through the filter 43b into an electric signal. Next, in the radiation image information recording / reading unit 24, a current-for converting the output current from the photoelectric converter 43 into a voltage signal-
It includes a voltage converter 44, a logarithmic amplifier 45 for logarithmically amplifying the voltage signal of the current-voltage converter 44, and an A / D converter 46 for converting the output of the amplifier 45 into digital data. The A / D converter 46 obtains a three-digit range of stimulated emission light as 10-bit conversion data in order to convert a wide dynamic range image of the radiation conversion panel 23 as faithfully as possible. Further, a control circuit 47 for inputting data from the A / D converter 46 is provided in the radiation image information recording / reading unit 24. The control circuit 47 adjusts the light beam intensity of the light beam unit 41, Gain adjustment of photomultiplier by adjusting power supply voltage of power supply 48, current-voltage converter 4
4 and gain adjustment of A / D converter 46 and A / D converter 46
And dynamically adjust the read gain of the radiation image information.

Next, the control unit 25 is controlled by a computer, and has a central processing unit (hereinafter referred to as a CPU) 5.
0 is connected to the following processing elements by the system bus SB and the image bus VB. The image display means (image monitor) 51 is connected to the CPU 50 via a display control section 51a, and the frame memory 52 as storage means is connected to the CPU 50 via a frame memory control section 52a. The information input means 53 includes a keyboard 53a and an LCD display means 53b, and is connected to the CPU 50 via an interface 53c. The reading synchronizing means 54 includes a reading control unit 54a connected to the CPU 50 and an X-ray adapter 54b connected to the reading control unit 54a. You. 56, an I / O interface for an external device (not shown);
Is a magnetic disk device 58 (or an external optical disk device,
A magnetic disk controller 59 for the magnetic tape device) is a memory. Note that the CPU 50 can also be connected to an external terminal.

The operation of such a device is described below.

The identification information of the subject 22 to be X-rayed is
It is input from the keyboard 53a of the control unit 25. The identification information includes an ID number, a name, a date of birth, a sex, an imaging part, an imaging date and the like. However, the shooting date and time may be automatically inserted by a calendar clock built in the CPU 50, or if the ID information is managed by an external device, the ID information may be sent from it and only the collation may be performed. It may be. Alternatively, only the collation may be performed by receiving the input from the external terminal.
Further, the identification information input here may be only information relating to the patient to be imaged at that time, or a series of information may be input in advance, and the imaging may be sequentially performed later. The identification information is input, and the subject 22 is set at the photographing position to perform photographing.

When the photographing button is pressed, the CPU 50 instructs the reading control section 54a to start reading. Read control unit 54
a controls the drive circuit 10 via the X-ray adapter 54b and instructs the radiation source 21 to perform X-ray imaging. Thus, the radiation source 21 emits radiation (X
Line). This radiation passes through the subject 22, energy is accumulated in the stimulable phosphor layer of the radiation conversion panel 23 according to the radiation transmittance distribution of the subject 22, and a latent image of the subject 22 is formed there. Thus, the X-ray imaging is completed.

When the X-ray imaging is completed, the light beam unit 41 generates a light beam whose beam intensity is controlled, the light beam is changed by the light scanner 42, the light path is changed by the reflecting mirror, and the radiation conversion panel 23 is changed. Is guided as excitation scanning light. The radiation conversion panel 23 outputs stimulated emission light proportional to the latent image energy by the excitation scanning light. The photoelectric converter 43 detects the stimulated emission light and outputs a current signal corresponding to the incident light. The output current passes through a current-voltage converter 44, an amplifier 45, and an A / D converter 46, becomes digital image data, is applied to a control circuit 47, and is transferred to the control unit 25.

FIG. 4 is a block diagram showing the configuration of the reading control section 54a in the control section 25. This reading control unit 5
4a is an input switch SW which is switched in synchronization with each other
1. An output switch SW2 and line buffers A and B composed of a RAM having a storage capacity of 2048 pixels.
Here, the line buffers A and B correspond to one line in the main scanning direction of the image data. When the image data of the first line from the radiation image information recording / reading unit 24 is stored in the line buffer A, the input switch SW1 and the output switch SW2 are switched, and the image data of the second line is stored in the line buffer B. . At the same time, the image data of the first line of the line buffer A is output and the image bus VB
Are sequentially stored in the frame memory 52.
The input / output switches SW1 and SW2 are switched for each line, and the roles of the line buffers A / B are changed.

FIG. 5 is a schematic diagram of the configuration of the frame memory 52. This frame memory 52 has 2048 * 256
It is composed of a RAM having a storage capacity of 0 pixels. The image data converted by the radiation image information recording / reading unit 24 and temporarily stored in the line buffers A / B is stored in the frame memory 52 line by line. At the same time, the stored image data is transferred to the display controller 51a or the magnetic disk controller 57 via the image bus VB.

From the frame memory 52 to the display controller 51a
When the image data is transferred, the image data is read out from the frame memory 52 every four pixels in both the main scanning direction and the sub-scanning direction, and is continuously written into the display memory in the display control unit 51a. This is because the display CRT has only a display resolution of 512 pixels * 640 pixels, so that both main and sub pixels are thinned to 1/4. When transferring image data from the frame memory 52 to the magnetic disk control unit 57, the image data is continuously read from the frame memory 52 and written continuously to the FIFO memory in the magnetic disk control unit 57. As described above, the frame memory control unit 52a has the configuration shown in FIG. 1 in order to make the frame memory 52 accessible by thinning or continuous access.

In the figure, basically, the read / write timing of the entire frame memory 52 is generated in the frame memory timing control circuit 61, and the main scanning direction address generator 62 in the X axis direction and the sub scanning in the Y axis direction are generated. The address of the frame memory 52 to be accessed by the direction address generator 63 is specified, and the data is stored in the image bus VB.
Is read or written via the. The main scanning direction address generator 62 is an 11-bit sub-scanning direction address generator 63 corresponding to 2048 pixels.
Has the same configuration except that it is composed of 12 bits corresponding to 2560 pixels.

Here, a case where reading is performed every four pixels will be described. First, the CPU 50 sets the address of the head pixel position in the latch circuits 65 and 66 through the I / F logic 64. Next, the CPU 50 sets +4, which is the increment of the address, in the latch circuits 67 and 68. Then, the CPU 50 sets the read flag and the X-direction addition flag of the command latch in the frame memory timing control circuit 61, and instructs the start of data transfer.

In response to this command, the frame memory timing control circuit 61 first sets the head pixel position data of the latch circuits 65 and 66 to the latch circuits 71 and 72 through the multiplexers 69 and 70, and sets these latch data. Switching is performed by the multiplexer 73, and a frame memory address is generated through the buffer 74. When the head pixel data based on the frame memory address is read, the frame memory timing control circuit 61 switches the multiplexer 69 to the adder / subtractor 75 side. The adder / subtractor 75 performs addition / subtraction of the latch data of the latch circuits 67 and 71, and outputs the latch circuit 7 for each timing signal from the frame memory timing control circuit 61.
The pixel position data obtained by adding the increment of the latch circuit 67 to the current value of 1 is set in the latch circuit 71. With this control, the frame memory timing control circuit 61 performs +4 increment control of the main scanning direction address generator 62 every time one pixel data is transferred. When the transfer of one line is completed, the sub-scanning direction address generator 63 is controlled by the main scanning direction address generator 6 every time the transfer of one line is completed.
The +4 increment control is performed in the same manner as in the operation 2. Also, the frame memory timing control circuit 61 reads the RARAM from the DARM frame memory 52 every time one pixel is read.
S and CAS signals are provided, and the refresh operation is also controlled. With the above-described control, it is possible to obtain image data obtained by thinning out a captured image to 1/4. Changing the thinning rate is performed by changing the set values of the latch circuits 67 and 68. For example, the latch circuit 6
7 and the latch circuit 68 are set to +1 for continuous access. When the set value to the latch circuit 67 is -1 and the set value to the latch circuit 68 is +1, the left-right inverted pair image is read. Can be.

The image data read from the frame memory 52 is transferred via the I / F logic 77 and the image bus VB. The CPU 50 manages the transfer of the image data line by line. When the transfer to the magnetic disk control unit 57 becomes necessary, the address at that time is stored at the end of the transfer of the line, and the magnetic disk control unit 57
The transfer is performed by setting the address of the frame memory to be transferred to, the increment value, and the command. Then, the addresses, increments, commands, and the like stored at the end of the transfer are reset, and the transfer to the display control unit 51a is restarted. This is due to the overhead in setting the latches and registers.
Although the effective speed is reduced, the frequency is extremely low as compared with the image transfer, and apparently enables parallel operation.

During the reading operation, the control circuit 47 of the radiation image information recording / reading unit 24 sends the data to the frame memory 52.
Transfer from the frame memory 52 to the display control unit 51a or to the magnetic disk control unit 57 is performed in parallel as described above, but almost simultaneously with the completion of reading, display on the image display unit 51 and data storage in the magnetic disk device 58 Is made.

After the reading is completed, the CPU 50 sets the head address in the latch circuits 65 and 66, sets +32 in the latch circuits 67 and 68, and transfers the data to the buffer memory in the magnetic disk control unit 57. Do. The number of pixels at this time is 64 * 64 pixels, for a total of 4096 pixels. This is a form in which pixel thinning is performed to 1/32 in both main and sub scanning, and the image is trimmed into a square.
Using this image data, the CPU 50 obtains the cumulative frequency distribution of the image, obtains the image processing conditions that are the optimal display characteristics of the image, and changes the contents of the display look-up table in the display control unit 51a. Thus, 1/3 in both main and sub scanning.
The present inventor has found that although the number of pixels is reduced to 2 (the number of pixels is 1/1024), the feature values such as the maximum value, minimum value, and median value of the image and the cumulative frequency distribution hardly change from the original image data. It has been found that the use of this phenomenon greatly simplifies the operation so that even a 16-bit Microsoft processor can make a determination with almost no time delay in obtaining the optimum display characteristics of an image. 6 to 13 exemplify the cumulative frequency distribution and the frequency distribution characteristics at each thinning rate.
As can be seen from this example, even when compared with the cumulative frequency distribution of the original image data (FIG. 6), the cumulative frequency distribution thinned out for every 32 pixels (FIG. 11) has almost the same shape. There is no problem in estimating the image state. Further, even if an image having a thinning rate higher than that is used (FIGS. 12 and 13), the estimation is not so disturbed, which is effective both in hardware and processing time.

In the case of FIGS. 9 and 10, even if a 16-bit CPU is used, the processing time is not so long, and processing that is comparable to estimation using original image data is performed. It is possible and effective.

It should be noted that, in an X-ray image, the information of the peripheral portion of the image has little influence on the whole, and even if the upper and lower portions are extracted as an image extraction region, the characteristics are hardly impaired. In such a case, reading control is performed only in the central portion, and when the read image is considerably smaller than 2048 * 2560 pixels, reading is performed within the range of the image area by reducing the thinning rate to 31, 30,. For example, it is possible to easily adjust the reading area and the thinning rate by changing the latch data.

As an example, main scan 2048 pixels, sub scan 2
When reading an image of 464 pixels, the upper and lower parts are each 2
Extraction data of 64 * 64 pixels can be obtained by thinning out an image of 2048 * 2048 pixels, which is omitted for every 08 lines, by 1/32. This is because the extraction is completed 200 lines or more before the reading is completed, then the cumulative frequency distribution is calculated, the maximum value, the minimum value, the median value, etc. are calculated, and the optimal characteristics for the image as the image processing conditions are obtained. Creating the look-up table data to have the data can also end all the operations before the reading is completed. This means that the display control unit 51
Changing the display look-up table in “a” means that CRT images can be observed with optimum display characteristics almost simultaneously with the end of reading.

FIG. 2 shows a block diagram of the display controller 51a. The image data passing through the image bus VB is sequentially written to the display memory 81 through the data buffer 80. This display memory 81 stores 10-bit data of 512 * 64.
It has a storage capacity of 0 pixels. The data stored in the display memory 81 is sequentially transferred to a display look-up table 82 for converting 10-bit (1024-level) data to 8-bit data, converted and compressed into 8-bit data, and this data is subjected to D / A conversion. The data is converted into analog data by a device 83, further amplified by an amplifier 84, converted into a CRT video signal, and provided to a CRT display. The display control of the display memory 81 is performed by a memory control circuit 85, and the entire display control such as data transfer control and generation of a synchronization signal is performed by a display control circuit 86. Commands for these controls are given from CPU 50 through system bus SB and I / F logic 87.

The display control having such a configuration will be described below.

Under the control of rewriting the display look-up table 82 by the CPU 50, the display changes at that time. Therefore, the CPU 50 erases the image that has been displayed by giving an erasure command to the display control circuit 86 at the start of photographing. This can be completed in one frame display time by using a dual port RAM as the display memory 81 and writing black data from the read port side. Here, when erasing the display memory 81, linear table data is written into the display lookup table 82 as image processing conditions. This enables the entire area of the image data to be observed on the display during reading, so that it is possible to capture a shift in the photographing position and an approximate feeling of the image data. For example, the radiation image information recording / reading unit 24 quantizes a 3-digit range of X-ray dose to 10 bits to obtain digital image data. However, the effective range is actually about 1.5 digits, and the image data is 10 bits. (0-1
023) to be able to observe on the CRT which of the levels exists. From this observation, it is possible to confirm whether or not the image is located near the white or black level due to a setting error of the photographing condition, and it is possible to immediately determine whether or not re-imaging is required.

By processing the extracted image data, the display image on the CRT is changed to an image having an appropriate gradation almost at the same time when the reading is completed, and is made an image having good diagnostic performance. At this time,
When the irradiation field and the imaging conditions of the imaging are largely different from those in the normal case, there is a case where an image which is not sufficiently satisfied by the preset gradation characteristic may be obtained. In this case, it can be dealt with by changing the gradation by scanning the gradation control function key of the keyboard 53a. That is, since the density of the X-ray image and the gamma value, which is its inclination, are important, the two parameters are changed by the display look-up table 82 so that the image displayed on the CRT as described above is changed. Change and adjust digitally. With such a configuration, it is possible to determine whether the image processing condition is appropriate or inappropriate by looking at the displayed image, and furthermore, the displayed image is not an inappropriate and sufficiently satisfied image. Even in this case, the image processing conditions can be corrected immediately, and the corrected image can be confirmed on the screen.

As described above, it is possible to confirm an image immediately after photographing and to observe an image having a desired gradation.

When observing an image in detail, it is possible to enlarge and pan the image by using the enlargement of the keyboard 53a and the panning function key. The image can be enlarged by reducing the thinning rate and transferring the image from the frame memory to the display memory 81.
1, and the panning is realized by shifting the read start address of the display memory 81 by an amount to move the image and transferring only the image newly appearing on the CRT. To enable this control, the display memory 81 is configured to be endless in both the main scanning direction and the sub-scanning direction.

Further, when the image is horizontally inverted by the photographing method, the image can be corrected by inverting the image left and right by the function key for left and right inversion. In addition, when there is an input error in the subject name, the date of birth, or the like, correction using the keyboard is possible.

When the above-described checking operation is completed, the process proceeds to the next photographing. At this point, all the data is determined, and the data can be transferred to an external device. Also, after a certain period of time when the operator stops operating without the next shooting,
By automatically determining the data, automatic transfer to an external device can be enabled.

The above-mentioned external device may be a host computer of a higher rank, or a film printer for recording an image, or both. In the case of the host computer, the image data is divided into a plurality of lines in one block, read from the magnetic disk control unit 57, transferred to the buffer memory in the external device interface via the image bus VB, and transferred to the host computer. It is realized by doing. In the case of a film printer, the CPU 50 first sets a look-up table in the interface to make the look-up table similar to the image observed on the CRT. Then, the image is transferred and printed.

The external device is a high-speed processing device whether it is a host computer or a film printer. However, if image data is transferred while reading image data from the magnetic disk device 58, the execution speed is greatly reduced. In some cases, or the transfer is too late. To solve this problem, the execution speed can be improved by additionally providing the frame memory 52 for one screen and switching between reading and transferring. In addition, the management information of the magnetic disk device 58 can be deleted for the image that has been transferred to the external device, so that the magnetic disk device 58 can be prevented from overflowing.

[0046]

As described above, according to the present invention, it is possible to obtain an image having high diagnostic performance after reading an image.
In other words, even when the image processing conditions obtained based on the feature amount of the image data are not appropriate and improper image processing has been performed, the image processing conditions can be corrected, and the corrected image is displayed on the display unit. This has the effect of being able to be confirmed with.

[Brief description of the drawings]

FIG. 1 is a control circuit diagram of a frame memory according to the present invention.

FIG. 2 is a display control circuit diagram according to the present invention.

FIG. 3 is an apparatus configuration diagram of a radiation image information reading and displaying apparatus.

FIG. 4 is a block diagram of timing control in a control unit.

FIG. 5 is a schematic configuration diagram of a frame memory.

FIG. 6 is a measurement diagram showing a histogram for a thinning rate (= 1) of image data.

FIG. 7 is a measurement diagram showing a histogram with respect to a thinning rate (= 2) of image data.

FIG. 8 is a measurement diagram showing a histogram with respect to a thinning rate (= 4) of image data.

FIG. 9 is a measurement diagram showing a histogram with respect to a thinning rate (= 8) of image data.

FIG. 10 is a measurement diagram showing a histogram with respect to a thinning rate (= 16) of image data.

FIG. 11 is a measurement diagram showing a histogram with respect to a thinning rate (= 32) of image data.

FIG. 12 is a measurement diagram showing a histogram with respect to a thinning rate (= 64) of image data.

FIG. 13 is a measurement diagram showing a histogram with respect to a thinning rate (= 128) of image data.

[Explanation of symbols]

 Reference Signs List 21 radiation source 22 subject 23 conversion panel 24 radiation image information recording / reading unit 25 control unit 51a display control unit 52 frame memory 52a frame memory control unit 61 frame memory timing control circuit 62 main scanning direction address generator 63 sub-scanning direction address generator 81 display Memory 82 Display lookup table

──────────────────────────────────────────────────続 き Continuation of front page (51) Int.Cl. ⁷ Identification code FI A61B 6/00 303L H04N 1/04 E 1 / 40Z JP-A-57-131169 (JP, A) JP-A-61-201591 (JP, A) JP-A-62-200871 (JP, A) JP-A-62-42286 (JP, A)

Claims (1)

(57) [Claims] A means for reading a radiation image conversion panel in which a radiation image is stored to obtain original image data; a display means; and a frequency distribution of image data obtained by thinning out the original image data. Means for obtaining a gradation processing condition corresponding to a radiation image; processing means for performing gradation processing on the original image data based on the gradation processing condition; and correction means for correcting the gradation processing condition. An image based on the original image data is displayed on the display unit in response to reading of the radiation image conversion panel, and substantially simultaneously with the end of the reading, the image based on the displayed original image data is subjected to the gradation processing. Is changed to an image based on the original image data subjected to, and further corrected in accordance with the operation of the correction means. Radiation image information reading display device, characterized in that it comprises a control means for changing the image based on the original image data gradation processing is performed on the basis of the gradation processing conditions.