JP2001149359A - Imaging device, image processing device, image processing system, image processing method and storage medium - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an imaging device capable of providing an index of a transmitted dosage effective for reading a radiation image and radiographing. SOLUTION: The first detecting means AEC of a sensor part 200 detect the dosage of a first area part on an image pickup surface of an imaging means for acquiring a radiation image of a subject. A second detecting means 302 calculates a transmitted dosage quantity of the subject on the basis of a picture element value of a second area part corresponding to the first area part on the radiation image obtained by the image pickup means.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention is used, for example, in a radiographing apparatus for radiographing an object (such as X-rays).
Using a semiconductor sensor, an imaging apparatus, an image processing apparatus, an image processing system, an image processing method, and a processing step for performing the same are effective for an imaging apparatus having a function of detecting a radiation dose transmitted through a subject. The present invention relates to a storage medium readable by a computer.

[0002]

2. Description of the Related Art Conventionally, when a certain kind of phosphor is irradiated with radiation (X-ray, α-ray, β-ray, γ-ray, electron beam, ultraviolet ray, etc.), a part of the radiation energy at this time is reduced. It is accumulated in the phosphor. Further, when the phosphor in which a part of the radiation energy is accumulated is irradiated with excitation light such as visible light, the phosphor shines according to the energy accumulated in the phosphor. It is known to exhibit exhaustion. Phosphors exhibiting such properties are called “accumulative phosphors (stimulable phosphors)”.

Therefore, as a photographing apparatus using the above-mentioned stimulable phosphor, for example, Japanese Patent Application Laid-Open No. 55-12429
And a radiation image information recording / reproducing apparatus described in JP-A-56-11395. In this radiation image information recording / reproducing apparatus (hereinafter, referred to as “radiation imaging apparatus 1”), first, radiation image information (X-ray image information or the like) of a subject such as a human body is temporarily stored in a sheet of stimulable phosphor (hereinafter, “ (Referred to as “accumulative phosphor sheet”). Next, by scanning the stimulable phosphor sheet with excitation light such as laser light,
The stimulable luminescent light is generated in the stimulable phosphor sheet, and the stimulable luminescent light is photoelectrically read to obtain an image signal. Then, the image signal is subjected to image processing such as gradation conversion processing, and the processed image signal is converted into a radiation image of a subject as a visible image by using a recording medium such as a photographic photosensitive material or a CRT.
And the like.

In recent years, an imaging device (hereinafter, referred to as a “radiation imaging device 2”) that uses a semiconductor sensor and acquires a radiation image (X-ray image or the like) of a subject in the same manner as the above-described radiation imaging device 1. ") Has been developed.

The radiation imaging apparatus 1 and the radiation imaging apparatus 2 described above can record images over an extremely wide radiation exposure area as compared with a conventional imaging apparatus (radiography system) using silver halide photography. Advantages. That is, the radiation imaging apparatus 1 and the radiation imaging apparatus 2
Is a method in which radiation (e.g., X-rays) having a very wide dynamic range, transmitted through a subject, is read by a sensor (photoelectric conversion means), converted into an electric signal, and subjected to image processing on the electric signal. By outputting the radiation image as a visible image to a recording medium such as a photographic light-sensitive material or a display device such as a CRT, it is possible to acquire a radiation image that is not affected by a change in radiation exposure amount.

[0006]

However, in the above-described conventional radiation imaging apparatus, image processing according to the part of the subject is automatically performed irrespective of the amount of radiation transmitted through the subject (transmitted dose). However, the following inconveniences have occurred.

First, as a radiation imaging apparatus, there is a film screen system in which a radiation image of a subject acquired in the same manner as the above-described radiation imaging apparatuses 1 and 2 is output on a film. In the screen system, if the transmitted dose is not enough, sufficient darkening cannot be obtained for the film, so it can be judged at a glance that the transmitted dose is insufficient, and if the transmitted dose is too large, the film will be too black. By
It can be seen at a glance that the transmitted dose is too large.

Therefore, for example, when the transmitted dose is not sufficient, image processing such as a gradation conversion process is performed in spite of the insufficient transmitted dose as described above. For this reason, the radiation image obtained as a result is in a state of an image with much quantum noise, and the image in such a state is output to a recording medium such as a photographic photosensitive material or a display device such as a CRT, It will be used for image diagnosis etc. by a doctor.

At this time, if the doctor or the like has information on the relative or absolute transmitted dose, the doctor can interpret the output image based on prior knowledge such as an image with much noise or an image with little noise. For this reason, a relative or absolute transmitted dose index is required not only by doctors but also by radiological technicians who perform radiography. This is because it is necessary to re-capture the image if the amount of transmitted light is significantly insufficient.

Therefore, in response to the above-mentioned demands of doctors and radiologists, a radiation imaging apparatus (CR: Computed Radii) using an imaging plate (IP).
(Ography system) corresponds as follows.

[0011] As a CR system, EDR (Expo) is a function for finishing an image having an optimum density and contrast.
Sure Data Recognizer)
In the EDR, an “S value” is provided as a relative index of the transmitted dose (called an index indicating “reading sensitivity” in the case of a CR system).

More specifically, S, which is an index representing the reading sensitivity,
The value is the median value of the reader output (“51” for 10 bits).
1 ”) is defined as a relationship with a value Sk representing the amount of emitted light of the IP. The value Sk representing the amount of emitted light is a tube voltage of 80.
The light emission amount when 0.5 mR is irradiated at kVp is “2”.
Is a scale expressed in logarithm. The relationship between the S value and the Sk value is represented by the equation S = 4 · 10 ^(4-Sk) . Therefore, when the radiation (X-ray) irradiation amount becomes relatively large, the S value becomes large,
The Sk value decreases accordingly. This means that a sufficient signal can be taken out even if the reading sensitivity is low because the amount of emitted light from the IP is large.

Further, the CR system includes "Semi A
The “Semi Auto” mode is a reading condition determination method based on a concept similar to the so-called photo timer method.A predetermined area on the IP from the pre-read image data is used. And the reading conditions are determined so that the value corresponding to the amount of emitted light is a digital value set in advance for each photographing menu. The average density of the predetermined area is always a constant optimum density, but the latitude is a fixed value set for each shooting menu.

However, due to the difference between the photometry area used when the radiologist takes a radiograph of the subject and the area where the “S value” is actually calculated, the
It is pointed out that the “S value” varies, differs from the actual feeling, and the like. For this reason, conventionally, doctors, radiologists, and the like have not been able to obtain an effective transmitted dose index for image reading and imaging.

The present invention has been made in order to eliminate the above-mentioned drawbacks, and it is an image pickup apparatus, an image processing apparatus, and an image processing apparatus capable of providing an index of a transmitted dose effective for radiographic image interpretation, radiography, and the like. It is an object of the present invention to provide a computer-readable storage medium storing a system, an image processing method, and processing steps for executing the system.

[0016]

For such a purpose,
A first invention is an imaging unit that captures a radiation image of the subject by capturing radiation transmitted through the subject, a detection unit that detects a radiation dose incident on the imaging unit for the radiation dose control, Calculating means for calculating a radiation transmission amount of the subject from the radiation image obtained by the imaging means, wherein the detection means detects a radiation amount in a first region on an imaging surface of the imaging means; The calculating means calculates the radiation transmission amount of the subject based on a pixel value of a second area corresponding to the first area on the radiation image.

According to a second aspect, in the first aspect,
The detection means detects the radiation dose of the plurality of first area parts, and the calculation means based on pixel values of a plurality of second area parts corresponding to the plurality of first area parts,
The radiation transmission amount of the subject is calculated.

According to a third aspect, in the second aspect,
The detecting means selects a target area portion of the radiation dose detection from the plurality of first area parts based on the part information of the subject, and the calculating means selects the area part by the detecting means. And selecting a target area portion for calculating the radiation transmission amount from the plurality of second area portions based on the selection.

According to a fourth aspect, in the third aspect,
It is characterized by comprising a setting means for setting the part information of the subject.

According to a fifth aspect of the present invention, in the first aspect,
The calculation means calculates a radiation transmission amount of the subject from a logarithmic conversion value of the pixel value.

According to a sixth aspect, in the first aspect,
The calculation means calculates a radiation transmission amount of the subject from an average value of the pixel values.

According to a seventh aspect of the present invention, there is provided an image processing apparatus for performing arbitrary image processing on a radiographic image obtained by radiographically imaging a subject. An imaging means having the function of (1) is provided.

According to an eighth aspect based on the seventh aspect,
An output unit for outputting a radiation image obtained by the imaging unit and a radiation transmission amount of the subject is provided.

According to a ninth aspect, in the eighth aspect,
The output means has at least one of a display output function and a print output function on a film, and outputs the radiation transmission amount to an arbitrary portion on the radiation image.

A tenth invention is an image processing system in which a plurality of devices are communicably connected, wherein at least one of the plurality of devices is one of the first to sixth embodiments. It has a function of an imaging device or a function of the image processing device according to any one of claims 7 to 9.

An eleventh invention is an image processing method for calculating the amount of radiation transmitted through the subject when the subject is subjected to radiography to obtain a radiation image of the subject. An imaging step of capturing radiation with an imaging sensor to obtain a two-dimensional radiation image of the subject, and a radiation dose detection step of detecting a radiation dose incident on the imaging sensor with a photosensor for the radiation dose control, An area detection step of detecting which area on the imaging surface of the imaging sensor the detection area of the photosensor is located at, and a pixel value in an arbitrary area of the imaging sensor detected by the area detection step A radiation transmission amount calculating step of calculating the radiation transmission amount of the subject based on

In a twelfth aspect based on the eleventh aspect, a setting step of setting the method of photographing the subject and at least one of a plurality of detection areas on the photosensor based on the setting in the setting step. The method includes a step of selecting one detection area, and the step of detecting a radiation amount includes a step of detecting a radiation amount incident on the imaging sensor in a detection area on the photosensor selected by the selection step. It is characterized by.

In a thirteenth aspect based on the eleventh aspect, the radiation dose detecting step includes the step of detecting a radiation dose incident on the image sensor in an arbitrary detection area among a plurality of detection areas on the photosensor. The method includes the step of detecting.

In a fourteenth aspect based on the eleventh aspect, the radiation transmission amount calculating step is based on a logarithmic conversion value of a pixel value in an arbitrary area of the image sensor detected by the area detecting step. Calculating a radiation transmission amount of the subject.

In a fifteenth aspect based on the eleventh aspect, the step of calculating the amount of transmitted radiation is based on an average value of pixel values in an arbitrary area of the image sensor detected by the area detecting step. Calculating a radiation transmission amount of the subject.

According to a sixteenth aspect, the function of the image pickup apparatus according to any one of claims 1 to 6, the function of the image processing apparatus according to any one of claims 7 to 9, or the image according to claim 10 is provided. A processing program for implementing the functions of the processing system
It is a storage medium that is readable by a computer.

A seventeenth aspect of the present invention is a storage medium in which the processing steps of the image processing method according to any one of claims 11 to 15 are readable by a computer.

[0033]

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

The present invention is applied to, for example, an image processing system 100 as shown in FIG. The image processing system 100 performs image processing such as gradation conversion processing on an X-ray image of a subject captured and acquired with radiation (here, “X-ray”), and performs X-ray processing after the processing. The line image can be printed out or displayed. In particular, the image processing system 100 is configured to output information on the transmitted dose of X-rays to an arbitrary portion of an output area of an X-ray image (an X-ray image area on a film or a screen). There is a feature in the configuration for acquiring dose information.

Therefore, first, the image processing system 100
The sensor unit 200 acquires and outputs an X-ray image (digital image data) of a subject as shown in FIG.
An image pre-processing unit 301 for performing pre-processing on the X-ray image from the sensor unit 200; a transmitted dose calculating unit 302 for acquiring X-ray transmitted dose information from the pre-processed X-ray image; QA (Quality As)
a QA processing unit 303 for performing a (surance) process, an image display unit 304 for displaying the transmitted dose information obtained by the transmitted dose calculation unit 302 and the X-ray image after the QA processing obtained by the QA processing unit 303, An operation unit 305 for instructing various operations; an image output unit 306 for outputting transmitted dose information obtained by the transmitted dose calculation unit 302 and an X-ray image after QA processing obtained by the QA processing unit 303; , Image output unit 3
The output X-ray image 06 is transferred to a printer 309, an image storage device 310, and an image display device 311 on a network 308.
And a network interface (I / F) 307 for supplying to any arbitrary device.

FIG. 2 shows the sensor section 200. As shown in FIG.
Includes a grid 201, an AEC (phototimer) plate 202, and a sensor plate 203.

The grid 201 is installed on the front surface on which X-rays are incident for preventing X-ray scattered radiation. Behind the grid 201, an AEC for detecting X-rays for controlling the amount of X-ray exposure (output) is provided. The plate 202 is set. The AEC plate 202 has three photometric units 202a and 202 described later.
b, 202c are provided.

[0038] Behind the AEC plate 202, a sensor plate 107 is provided. The sensor plate 203 converts the incident X-rays into a two-dimensional charge distribution, performs A / D conversion by an analog / digital (A / D) conversion function, and then converts the X-rays into the image pre-processing 30 shown in FIG.
Supply to 1.

As the sensor plate 203, in addition to a sensor that directly converts X-rays into an electric charge using a selenium, the visible light is converted into electric charges by once converting it into visible light with a phosphor. Although it is conceivable to use a sensor, the present invention is not limited to this, and a stimulable sensor plate may be used.

FIG. 3 shows the relationship between the X-ray image formed by the sensor unit 200 as described above and the three photometric units 202a, 202b and 202c of the AEC plate 202. Here, as an example of the X-ray image, a chest front image 400 obtained by irradiating an X-ray from the front of the chest is used.

In the chest front image 400, as shown in FIG. 3 above, a through portion (a portion where X-rays are directly applied) 40
With 1 as a background, a chest area exists. The heaviest part (the part important for a doctor's image diagnosis) in the chest region is a right lung part 402 and a left lung part 403.

On the other hand, the AEC plate 202 is provided with three photometric sections 202a, 202b, and 202c, but the important parts in the front chest image 400 are the right lung section 402 and the left lung section 403. , Actually AEC
As photometric units used as functions, two photometric units 20
2a and 202c are selected.

As a method of selecting the photometric unit used as the AEC function, for example, in accordance with an instruction from a user such as a radiologist (an instruction from the operation unit 305), the photometric unit 202 is selected.
a, 202b, and 202c (hereinafter, referred to as “selection method 1”). Alternatively, in accordance with information indicating which part of the target image is an image (such as information from the operation unit 305), the photometric units 202a,
There is a method of selecting a corresponding photometric unit from 202b and 202c (hereinafter, referred to as “selection method 2”). in this case,
In advance, information of a photometry unit to be selected is prepared as table information in association with information of various parts (information indicating whether the image is a chest front image or a chest side image), and from this table information, By acquiring the information of the photometric unit corresponding to the information of the part and the like from the operation unit 305, the photometric unit 20 is obtained.
The corresponding photometric unit is selected from 2a, 202b and 202c.

The photometer 202 selected as described above
When the sum of the X-ray doses incident on a and 202c reaches a predetermined value, an X-ray cutoff signal is transmitted to the X-ray generation unit as shown in FIG. As a result, X-ray generation in the X-ray generation unit is cut off.

The photometric units provided on the AEC plate 202 include three photometric units 202a, 202b, and 202c.
It is not limited to. For example, an AEC plate having two photometric units may be used.

FIG. 4 shows the X formed by the sensor unit 200.
As an example of a line image, a chest side image 500 obtained by irradiating an X-ray from the side of the chest is shown.

In the chest side image 500, FIG.
As shown in the figure, a chest (side surface) region exists with the pass-through portion 501 as a background. The heaviest part of this chest area (important for a doctor's diagnostic imaging)
Is the lung part 502, the three photometric sections 202a and 20 are used as the photometric sections to be used as the AEC function in the AEC plate 202 by the selection method 1 or 2 described above.
2b and 202c are selected. These photometric units 202
a, 202b, and 202c, when the sum of the X-ray doses reaches a predetermined value, as shown in FIG.
The line cutoff signal is transmitted to the X-ray generation unit. As a result, X-ray generation in the X-ray generation unit is cut off.

Hereinafter, the operation of the image processing system 100 including the above-described sensor unit 200 will be described.

First, a signal (digital image data) output from the sensor unit 200 is supplied to an image pre-processing unit 301 and a QA processing unit 303, respectively.

The image pre-processing unit 301 performs pre-processing such as offset correction processing, LOG conversion processing, and gain correction processing on the digital image data from the sensor unit 200, and converts the digital image data after the processing. , To the transmitted dose calculation unit 302.

The transmitted dose calculation unit 302 includes the image preprocessing unit 3
From the digital image data from 01, the transmitted dose of X-rays is calculated. At this time, the image (2) for calculating the transmitted dose
The area on the (dimensional image matrix) is the AE on the AEC plate 202 as shown in FIGS.
An area corresponding to the photometric unit selected as the C function is determined.

More specifically, for example, when the selection of the photometry unit is performed by the above-described selection method 1, the information input from the operation unit 305 (information of the photometry unit used as the AEC function) at this time is used. , Photometric units 202a, 202
b, the photometry unit selected from 202c is recognized,
An area corresponding to the photometric unit is determined as an area on the image for calculating the transmitted dose.

For example, when the selection of the photometry unit is performed by the above-described selection method 2, the transmitted dose calculation unit 3
02, the information of the photometric unit to be selected from the photometric units 202a, 202b, and 202c is previously associated with the information of the part of the target image (information indicating whether the image is a chest front image or a chest side image). By storing the area information corresponding to each of the photometric units in association with the obtained table information, the photometric units 202a, 202b,
The area information corresponding to the photometric unit selected from the area 202c is acquired, and the area indicated by the area information is determined as the area on the image for calculating the transmitted dose.

Therefore, as described above, the transmitted dose calculation unit 302 sets the AEC
An area corresponding to the photometric unit selected as the function is determined as an area on the image for which the transmitted dose is calculated, and the transmitted dose is calculated from the data (pixel value) of the area. In this case, the transmitted dose does not necessarily need to be an absolute value, and may be an index value having a correlation with the transmitted dose.

For example, the photometric units 202a, 202b, 20
The transmitted dose is calculated based on the average value of the data of the image area corresponding to the photometry unit selected from 2c. When a plurality of photometric units are selected, the transmitted dose is calculated based on the average value of the data in the image area corresponding to the entirety of the plurality of photometric units. The average value itself may be used as an index of the transmitted dose.

On the other hand, the QA processing unit 303 applies the digital image data after pre-processing by the image pre-processing unit 301 to
QA processing such as frequency enhancement processing, dynamic range compression processing, and gradation conversion processing is performed.

The transmitted dose calculated by the transmitted dose calculation unit 302 and the digital image data after QA processing by the QA processing unit 303 are stored in the image display unit 304 and the image output unit 30.
6 respectively.

The image display unit 304 includes the transmitted dose calculation unit 30
The transmitted dose calculated in 2 and the digital image data after QA processing in the QA processing unit 303 are displayed on a screen.
For example, the information on the transmitted dose is displayed at an arbitrary part on the image of the subject by the digital image data.

The display of the transmitted dose information on the image display unit 304 is not limited. For example, a value obtained by LOG-converting the transmitted dose information may be displayed, or the transmitted dose information may be linearly converted. May be displayed.

The image output unit 306 includes the transmitted dose calculation unit 30
2 and the digital image data after QA processing by the QA processing unit 303 is converted into an arbitrary image file, and the image file is converted into a network I /
The data is transmitted to the network 308 via F307.

Here, for example, when the image file output from the image output unit 306 is a file composed of an image part and a header part, the transmitted dose is written as a part of the information of the header part. Alternatively, the transmitted dose is written as bitmap information as part of the information of the image section. The advantage of such a configuration is that even if the printer 309 or the image display device 311 as an output unit on the network 308 does not have a function of developing the information of the header portion as a pattern, the transmitted dose can be reduced. Can be output. That is, the printer 309 can output the transmitted dose together with the image in the image file so that it can be recognized on the film.
1 shows the transmitted dose along with the image in the image file as CRT
Etc. can be output to a display unit in a recognizable manner.

In the output form on the film by the printer 309 and the display output form by the image display device 311, for example, information on the transmitted dose is output to an arbitrary portion on the image of the subject.

The image file transmitted to the network 308 is stored in the image storage device 3 on the network 308.
10 is also supplied. The image storage device 310 stores an image file from the network 308. The image file stored in the image storage device 310 is stored in the printer 3
09 and the image display device 310. Therefore, if necessary, the printer 30
9 or the image display device 310 can output a stored image file of the image storage device 310.

As described above, according to the present embodiment, the photometer of the photo timer (AEC) used for photographing and the area for measuring the transmitted dose have the same photometry area. Since the transmitted dose (attained dose) of the region of interest for imaging can be accurately detected and output, a doctor, a radiological technologist, or the like can efficiently perform interpretation and imaging.

In addition, the CR as described in the prior art has a configuration in which the position of the photo timer at the time of photographing cannot be specified when photographing with a cassette as a base.
In a photographing device or system using a semiconductor sensor which will become the mainstream in the future, the photometry unit of the sensor and the phototimer is always fixed in terms of arrangement.
This is effective for an imaging device or a system using a semiconductor sensor.

An object of the present invention is to supply a storage medium storing program codes of software for realizing the functions of the host and the terminal of the above-described embodiment to a system or an apparatus, and to provide a computer (a computer) of the system or the apparatus. It is needless to say that the present invention can also be achieved by a CPU or an MPU) reading and executing a program code stored in a storage medium. In this case, the program code itself read from the storage medium implements the functions of the present embodiment, and the storage medium storing the program code constitutes the present invention. ROM, as a storage medium for supplying the program code,
Floppy disk, hard disk, optical disk, magneto-optical disk, CD-ROM, CD-R, magnetic tape,
A non-volatile memory card or the like can be used. By executing the program code read out by the computer, not only the functions of the present embodiment are realized, but also the OS and the like running on the computer perform actual processing based on the instructions of the program code. It goes without saying that a part or all of the above is performed, and the processing realizes the function of the present embodiment. Further, after the program code read from the storage medium is written to a memory provided in an extension function board inserted into the computer or a function extension unit connected to the computer, the function extension is performed based on the instruction of the program code. It goes without saying that a CPU or the like provided in the board or the function expansion unit performs part or all of the actual processing, and the processing realizes the functions of the present embodiment.

[0067]

As described above, according to the present invention, the area for calculating the radiation transmission amount of the subject is set as the area for detecting the amount of incident radiation (X-rays or the like) to an image sensor such as a photo timer (AEC). Since it is configured to be an area corresponding to (photometric area), it is possible to provide a radiation transmitted dose that promotes the feeling of imaging. Further, in a case where the information of the imaging method of the subject (information such as which part is being imaged) is set, the position information of the photometry area corresponding to various imaging methods is stored as table information. Thus, it is possible to easily determine the area for detecting the radiation transmission dose. Therefore, it is possible to provide an index of the transmitted dose that is effective for radiographic image interpretation, radiography, and the like, and it is possible to efficiently perform radiographic image interpretation, radiography, and the like.

[Brief description of the drawings]

FIG. 1 is a block diagram illustrating a configuration of an image processing system to which the present invention has been applied.

FIG. 2 is a diagram for explaining a sensor unit of the image processing system.

FIG. 3 is a diagram for explaining a relationship between an image (chest front image) at the sensor unit and a photo timer arrangement.

FIG. 4 is a diagram for explaining a relationship between an image (a chest side image) at the sensor unit and an arrangement of a photo timer.

[Explanation of symbols]

REFERENCE SIGNS LIST 100 Image processing system 200 Sensor unit 201 Grid 202 AEC plate 202 a, 202 b, 202 c Photometry unit (photo timer) 203 Sensor plate 301 Image pre-processing unit 302 Transmitted dose calculation unit 303 QA processing unit 304 Image display unit 305 Operation unit 306 Image output Unit 307 Network I / F 308 Network 309 Printer 310 Image storage device 311 Image display device

 ──────────────────────────────────────────────────続 き Continued on the front page F-term (reference) 4C092 AB02 AC01 AC16 CC02 CD05 CD07 CF24 CF25 DD04 DD07 4C093 AA01 CA06 EB13 EB17 EB24 FA18 FA26 FD02 FF08 FH06 5C024 AX11 AX16 CX00 GX02 GX09 HX21 HX23 HX60 A09 FCA HA12

Claims (17)

[Claims] An imaging unit configured to capture a radiation image of the subject by capturing radiation transmitted through the subject; a detection unit configured to detect a radiation amount incident on the imaging unit for controlling the radiation amount; Calculating means for calculating a radiation transmission amount of the subject from the radiation image obtained by the imaging means, wherein the detection means detects a radiation amount in a first region on an imaging surface of the imaging means, An imaging apparatus according to claim 1, wherein said calculating means calculates a radiation transmission amount of said subject based on a pixel value of a second region corresponding to said first region on said radiation image. 2. The method according to claim 1, wherein the detecting unit detects a radiation dose of the plurality of first region portions, and the calculating unit determines a pixel of the plurality of second region portions corresponding to the plurality of first region portions. The imaging apparatus according to claim 1, wherein the radiation transmission amount of the subject is calculated based on the value. 3. The detecting means selects a target area portion of the radiation dose detection from the plurality of first area parts based on the part information of the subject. 3. The imaging apparatus according to claim 2, wherein a target area portion for calculating the radiation transmission amount is selected from the plurality of second area portions based on the selection of the area portion by the means. 4. The imaging apparatus according to claim 3, further comprising a setting unit configured to set the part information of the subject. 5. The imaging apparatus according to claim 1, wherein said calculating means calculates a radiation transmission amount of said subject from a logarithmically converted value of said pixel value. 6. The imaging apparatus according to claim 1, wherein said calculating means calculates a radiation transmission amount of said subject from an average value of said pixel values. 7. An image processing apparatus that performs arbitrary image processing on a radiation image obtained by imaging a subject with radiation, and has a function of the imaging apparatus according to any one of claims 1 to 6. An image processing apparatus comprising an imaging unit. 8. The image processing apparatus according to claim 7, further comprising an output unit that outputs a radiation image obtained by the imaging unit and a radiation transmission amount of the subject. 9. The output means has at least one of a display output function and a print output function on a film, and outputs the radiation transmission amount to an arbitrary portion on the radiation image. The image processing apparatus according to claim 8, wherein 10. An image processing system in which a plurality of devices are communicably connected, wherein at least one of the plurality of devices is a function of the imaging apparatus according to any one of claims 1 to 6. Or claim 7
An image processing system having the function of the image processing apparatus according to any one of claims 9 to 9. 11. An image processing method for calculating the amount of radiation transmitted through a subject when the subject is radiographed to obtain a radiation image of the subject, wherein the imaging sensor detects radiation transmitted through the subject. An imaging step of acquiring a two-dimensional radiation image of the subject by capturing the radiation amount; a radiation amount detecting step of detecting a radiation amount incident on the image sensor by a photosensor for the radiation amount control; The detection area of, the area detection step of detecting which area on the imaging surface of the imaging sensor is located, based on a pixel value in an arbitrary area of the imaging sensor detected by the area detection step, A radiation transmission amount calculating step of calculating the radiation transmission amount of the subject. 12. A setting step of setting a method of photographing the subject, and a selecting step of selecting at least one detection area from a plurality of detection areas on the photosensor based on the setting in the setting step. 12. The image processing method according to claim 11, wherein the radiation dose detecting step includes a step of detecting a radiation dose incident on the imaging sensor in a detection area on the photosensor selected by the selection step. Method. 13. The radiation dose detecting step includes a step of detecting a radiation dose incident on the image sensor in an arbitrary detection region among a plurality of detection regions on the photosensor. Item 12. The image processing method according to Item 11. 14. The radiation transmission amount calculating step is a step of calculating a radiation transmission amount of the subject based on a logarithmic conversion value of a pixel value in an arbitrary region of the image sensor detected in the region detecting step. The image processing method according to claim 11, further comprising: 15. The radiation transmission amount calculating step includes a step of calculating a radiation transmission amount of the subject based on an average value of pixel values in an arbitrary region of the image sensor detected by the region detecting step. The image processing method according to claim 11, further comprising: 16. The function of the image pickup apparatus according to any one of claims 1 to 6, the function of the image processing apparatus according to any one of claims 7 to 9, or the function of the image processing system according to claim 10. A computer-readable storage medium storing a processing program for executing the program. 17. A storage medium, wherein the processing steps of the image processing method according to claim 11 are stored in a computer-readable manner.