Patent Description:
A technology of performing contrast imaging of capturing a low-energy image and a high-energy image by irradiating a subject into which a contrast medium has been injected with radiation having different energies and generating a difference image showing a difference between the high-energy image and the low-energy image to generate a radiation image in which the contrast medium is enhanced is known. As a technology of generating a difference image showing a difference between a low-energy image and a high-energy image, for example, a technology disclosed in <CIT> is known. In the technology disclosed in <CIT>, a technology is described in which, in X-ray computed tomography (CT) apparatus, a projection image, which is the low-energy image, is reconstructed, a projection image, which is the high-energy image, is reconstructed, and a difference image of a reconstructed image is generated. <CIT> discloses multiple energy exposures to implement temporal dual energy subtraction. <CIT> discloses a temporal X-ray acquisition arrangement that determines whether motion has occurred to stop sequence of X-ray imaging in order to avoid unnecessary exposure. <CIT> discloses a contrast enhanced mammography arrangement that detects and compensates motion using registration algorithm. <CIT> discloses to detect movement during tomosynthesis procedure and provides notification to the operator.

By the way, in diagnosing a lesion or the like in a subject, it is desired to observe a temporal change of a contrast medium permeating a region of interest, such as a lesion, specifically, a temporal change of a contrast amount. In a case of observing the temporal change of the contrast amount, since the imaging time is long, a body movement of the subject may occur during the imaging. The technology disclosed in <CIT> may be influenced by the body movement of the subject. For example, in a case in which a body movement amount of the subject is relatively large, the influence of the body movement of the subject may appear in the difference image.

The present disclosure is made in view of the above circumstances, and provides a control apparatus, a control method, and a non-transitory storage medium storing a control program capable of reducing an influence of a body movement of a subject in contrast imaging for observing a temporal change of a contrast amount.

A first aspect of the present disclosure relates to a control apparatus comprising at least one processor, in which the processor acquires a low-energy image captured by a radiography apparatus by emitting radiation having first energy to a subject into which a contrast medium has been injected, sequentially acquires each of a plurality of high-energy images captured by the radiography apparatus at different timings by emitting radiation having second energy higher than the first energy to the subject into which the contrast medium has been injected, sequentially derives a body movement amount of the subject from each of the plurality of high-energy images, performs, in a case in which the derived body movement amount exceeds a threshold value, control of causing the radiography apparatus to re-capture the low-energy image before a next high-energy image is captured, and generates a plurality of difference images showing a difference between the low-energy image and each of the plurality of high-energy images.

A second aspect of the present disclosure relates to the control apparatus according to the first aspect, in which the processor generates a difference image showing a difference from the low-energy image captured at a timing closest to an imaging timing of the high-energy image.

A third aspect of the present disclosure relates to the control apparatus according to the first aspect, in which the processor generates a difference image showing a difference from the re-captured low-energy image from a high-energy image in which the derived body movement amount exceeds the threshold value.

A fourth aspect of the present disclosure relates to the control apparatus according to the first aspect, in which the processor switches the low-energy image to be used for generating the difference image with a timing at which a body movement of the subject has occurred as reference.

A fifth aspect of the present disclosure relates to the control apparatus according to the first aspect, in which the processor generates a first difference image showing a difference from a high-energy image having an imaging timing closest to an imaging timing of the low-energy image, generates a second difference image showing a difference between the high-energy images, and generates the plurality of difference images by using the first difference image and the second difference image.

A sixth aspect of the present disclosure relates to the control apparatus according to any one of the first to fifth aspects, in which the processor generates a difference image for body movement analysis showing a difference between two continuously captured high-energy images among the plurality of high-energy images, and sequentially derives the body movement amount of the subject from the generated difference image for body movement analysis.

A seventh aspect of the present disclosure relates to the control apparatus according to any one of the first to fifth aspects, in which the processor sequentially derives the body movement amount of the subject from each of the plurality of high-energy images with the low-energy image as a reference.

An eighth aspect of the present disclosure relates to the control apparatus according to any one of the first to seventh aspects, in which the processor generates the plurality of difference images after performing registration between the low-energy image and each of the plurality of high-energy images.

A ninth aspect of the present disclosure relates to the control apparatus according to the eighth aspect, in which the processor performs registration between a region of interest in the low-energy image and a region of interest in each of the plurality of high-energy images.

A tenth aspect of the present disclosure relates to the control apparatus according to any one of the first to seventh aspects, in which the processor corrects each of the plurality of high-energy images according to the body movement amount, and generates a plurality of difference images showing a difference between the low-energy image and each of the corrected plurality of high-energy images.

An eleventh aspect of the present disclosure relates to the control apparatus according to any one of the first to tenth aspects, in which the processor gives a notification that a body movement has occurred in a case in which the derived body movement amount exceeds the threshold value.

A twelfth aspect of the present disclosure relates to the control apparatus according to any one of the first to eleventh aspects, in which the processor continuously displays the plurality of difference images as a moving image in a time series order of capturing.

A thirteenth aspect of the present disclosure relates to the control apparatus according to any one of the first to eleventh aspects, in which the processor displays a difference image having a highest contrast of a region of interest among the plurality of difference images.

A fourteenth aspect of the present disclosure relates to the control apparatus according to any one of the first to thirteenth aspects, in which the processor derives a contrast amount of a region of interest in each of the plurality of difference images, and generates information indicating a temporal change of the contrast amount of the region of interest and displays the generated information.

A fifteenth aspect of the present disclosure relates to the control apparatus according to any one of the first to fourteenth aspects, in which the subject is a breast, and the radiography apparatus is a mammography apparatus.

In addition, a sixteenth aspect of the present disclosure relates to a control apparatus comprising at least one processor, in which the processor captures a low-energy image by a radiography apparatus by emitting radiation having first energy to a subject into which a contrast medium has been injected, and then sequentially acquires each of a plurality of high-energy images captured by the radiography apparatus at different timings by emitting radiation having second energy higher than the first energy to the subject into which the contrast medium has been injected, sequentially derives a body movement amount of the subject from each of the plurality of high-energy images, and performs, in a case in which the derived body movement amount exceeds a threshold value, control of causing the radiography apparatus to re-capture the low-energy image before a next high-energy image is captured.

In addition, a seventeenth aspect of the present disclosure relates to a control method executed by a computer, the method comprising acquiring a low-energy image captured by a radiography apparatus by emitting radiation having first energy to a subject into which a contrast medium has been injected, sequentially acquiring each of a plurality of high-energy images captured by the radiography apparatus at different timings by emitting radiation having second energy higher than the first energy to the subject into which the contrast medium has been injected, sequentially deriving a body movement amount of the subj ect from each of the plurality of high-energy images, performing, in a case in which the derived body movement amount exceeds a threshold value, control of causing the radiography apparatus to re-capture the low-energy image before a next high-energy image is captured, and generating a plurality of difference images showing a difference between the low-energy image and each of the plurality of high-energy images.

In addition, in order to achieve the objects, an eighteenth aspect of the present disclosure relates to a non-transitory storage medium storing a control program causing a computer to execute a control processing, the control processing comprising: acquiring a low-energy image captured by a radiography apparatus by emitting radiation having first energy to a subject into which a contrast medium has been injected, sequentially acquiring each of a plurality of high-energy images captured by the radiography apparatus at different timings by emitting radiation having second energy higher than the first energy to the subject into which the contrast medium has been injected, sequentially deriving a body movement amount of the subject from each of the plurality of high-energy images, performing, in a case in which the derived body movement amount exceeds a threshold value, control of causing the radiography apparatus to re-capture the low-energy image before a next high-energy image is captured, and generating a plurality of difference images showing a difference between the low-energy image and each of the plurality of high-energy images.

According to the present disclosure, it is possible to reduce the influence of the body movement of the subject in the contrast imaging for observing the temporal change of the contrast amount.

In the following, an embodiment of the present invention will be described in detail with reference to the drawings. It should be noted that the present embodiment does not limit the present invention.

First, an example of an overall configuration of a radiography system according to the present embodiment will be described. <FIG> shows a configuration diagram showing an example of an overall configuration of a radiography system <NUM> according to the present embodiment. As shown in <FIG>, the radiography system <NUM> according to the present embodiment comprises a mammography apparatus <NUM> and a console <NUM>. The mammography apparatus <NUM> according to the present embodiment is an example of a radiography apparatus according to the present disclosure. In addition, the console <NUM> according to the present embodiment is an example of a control apparatus according to the present disclosure.

First, the mammography apparatus <NUM> according to the present embodiment will be described. <FIG> shows a side view showing an example of an appearance of the mammography apparatus <NUM> according to the present embodiment. It should be noted that <FIG> shows the example of the appearance of the mammography apparatus <NUM> as viewed from a right side of an examinee.

The mammography apparatus <NUM> according to the present embodiment is an apparatus that uses a breast of the examinee as a subject and captures a radiation image of the breast by irradiating the breast with radiation R (for example, X-rays). It should be noted that the mammography apparatus <NUM> may be an apparatus that images the breast of the examinee in a state in which the examinee is sitting on a chair (including a wheelchair) or the like (sitting state) in addition to a state in which the examinee is standing (standing state).

In addition, the mammography apparatus <NUM> according to the present embodiment has a function of performing two types of imaging of so-called contrast imaging in which the imaging is performed in a state in which a contrast medium has been injected into the breast of the examinee and general imaging. It should be noted that, in the present embodiment, the imaging to be performed in a state in which the contrast medium has been injected into the breast of the examinee refers to the "contrast imaging", and the imaging that is not the contrast imaging refers to the "general imaging".

In the mammography apparatus <NUM>, in a case of performing the contrast imaging, the radiation image is captured by emitting the radiation having the first energy from the radiation source 37R to the breast in a state in which the contrast medium has been injected. In addition, in the mammography apparatus <NUM>, the radiation image is captured by emitting the radiation having the second energy higher than the first energy from the radiation source 37R to the breast in a state in which the contrast medium has been injected. It should be noted that, in the present embodiment, the radiation image captured by emitting the radiation R having the first energy is referred to as a "low-energy image", and the radiation image captured by emitting the radiation R having the second energy is referred to as a "high-energy image". In addition, in a case in which the images captured by the mammography apparatus <NUM> are collectively referred to without distinction between types, such as the low-energy image and the high-energy image, the images are simply referred to as the "radiation image".

As shown in <FIG>, the mammography apparatus <NUM> according to the present embodiment comprises a control unit <NUM>, a storage unit <NUM>, and an interface (I/F) unit <NUM> inside the imaging table <NUM>. The control unit <NUM> controls an overall operation of the mammography apparatus <NUM> under the control of the console <NUM>. The control unit <NUM> comprises a central processing unit (CPU), a read only memory (ROM), and a random access memory (RAM) (all not shown). The ROM stores, in advance, various programs, including an imaging processing program for performing control related to radiation image capturing, which is executed by the CPU. The RAM transitorily stores various data.

The storage unit <NUM> stores the image data of the radiation image captured by the radiation detector <NUM> or various types of other information. Specific examples of the storage unit <NUM> include a hard disk drive (HDD) and a solid state drive (SSD). The I/F unit <NUM> performs communication of various types of information with the console <NUM> by wireless communication or wired communication. The image data of the radiation image captured by the radiation detector <NUM> in the mammography apparatus <NUM> is transmitted to the console <NUM> via the I/F unit <NUM> by wireless communication or wired communication.

In addition, an operation unit <NUM> is provided as a plurality of switches on an imaging table <NUM> of the mammography apparatus <NUM>, for example. It should be noted that the operation unit <NUM> may be provided as a touch panel type switch, or may be provided as a foot switch operated by a user, such as a doctor or an engineer with a foot.

The radiation detector <NUM> detects the radiation R that has passed through the breast which is the subject. In addition, as shown in <FIG>, the radiation detector <NUM> is disposed inside the imaging table <NUM>. In the mammography apparatus <NUM> according to the present embodiment, the user positions the breast of the examinee on an imaging surface 30A of the imaging table <NUM> in a case of performing the imaging.

The radiation detector <NUM> detects the radiation R transmitted through the breast of the examinee and the imaging table <NUM>, generates a radiation image based on the detected radiation R, and outputs image data representing the generated radiation image. A type of the radiation detector <NUM> according to the present embodiment is not particularly limited. For example, a radiation detector of an indirect conversion method that converts the radiation R into light and converts the converted light into a charge may be used, and a radiation detector of a direct conversion method that directly converts the radiation R into a charge may be used.

A radiation emitting unit <NUM> comprises the radiation source 37R. As shown in <FIG>, the radiation emitting unit <NUM> is provided in an arm part <NUM> together with the imaging table <NUM> and the compression unit <NUM>. As shown in <FIG>, a face guard <NUM> is attachable and detachable at a position near the examinee on the arm part <NUM> below the radiation emitting unit <NUM>. The face guard <NUM> is a protective member for protecting the examinee from the radiation R emitted from the radiation source 37R.

It should be noted that, as shown in <FIG>, the mammography apparatus <NUM> according to the present embodiment comprises the arm part <NUM>, a base <NUM>, and a shaft part <NUM>. The arm part <NUM> is held by the base <NUM> to be movable in a vertical direction (Z-axis direction). The shaft part <NUM> connects the arm part <NUM> to the base <NUM>. In addition, the arm part <NUM> is rotatable relative to the base <NUM> with the shaft part <NUM> as a rotation axis.

The arm part <NUM>, the imaging table <NUM>, and the compression unit <NUM> can be separately rotated relative to the base <NUM> with the shaft part <NUM> as a rotation axis. In the present embodiment, the base <NUM>, the arm part <NUM>, the imaging table <NUM>, and the compression unit <NUM> are each provided with an engaging part (not shown), and each of the arm part <NUM>, the imaging table <NUM>, and the compression unit <NUM> is connected to the base <NUM> by switching a state of the engaging part. One or two of the arm part <NUM>, the imaging table <NUM>, or the compression unit <NUM>, which are connected to the shaft part <NUM>, are integrally rotated around the shaft part <NUM>.

The compression unit <NUM> is provided with a compression plate driving unit (not shown) that moves the compression plate <NUM> in the vertical direction (Z-axis direction). The compression plate <NUM> according to the present embodiment has a function of compressing the breast of the examinee. A support part <NUM> of the compression plate <NUM> is attachably and detachably attached to the compression plate driving unit, is moved in the vertical direction (Z-axis direction) by the compression plate driving unit, and compresses the breast of the examinee with the imaging table <NUM>.

On the other hand, the console <NUM> according to the present embodiment has a function of controlling the mammography apparatus <NUM> by using an imaging order and various types of information acquired from a radiology information system (RIS) <NUM> via a wireless communication local area network (LAN) and the like, and an instruction performed by the user by an operation unit <NUM> and the like.

The console <NUM> according to the present embodiment is, for example, a server computer. As shown in <FIG>, the console <NUM> comprises a control unit <NUM>, a storage unit <NUM>, an I/F unit <NUM>, the operation unit <NUM>, and a display unit <NUM>. The control unit <NUM>, the storage unit <NUM>, the I/F unit <NUM>, the operation unit <NUM>, and the display unit <NUM> are connected to each other via a bus <NUM>, such as a system bus or a control bus, such that various types of information can be exchanged.

The control unit <NUM> according to the present embodiment controls an overall operation of the console <NUM>. The control unit <NUM> comprises a CPU 50A, a ROM 50B, and a RAM 50C. The ROM 50B stores, in advance, various programs including a contrast imaging control processing program 51A and a difference image generation display processing program 51B, which are executed by the CPU 50A and will be described below. The RAM 50C transitorily stores various data. The CPU 50A according to the present embodiment is an example of a processor according to the present disclosure. The contrast imaging control processing program 51A and the difference image generation display processing program 51B according to the present embodiment are examples of a control program according to the present disclosure.

The storage unit <NUM> stores the image data of the radiation image captured by the mammography apparatus <NUM> or various types of other information. Specific examples of the storage unit <NUM> include an HDD and an SSD.

The operation unit <NUM> is used by the user to input the instruction, various types of information, and the like related to the radiation image capturing and the like, including an irradiation instruction of the radiation R. The operation unit <NUM> is not particularly limited, and examples thereof include various switches, a touch panel, a touch pen, and a mouse. The display unit <NUM> displays various types of information. It should be noted that the operation unit <NUM> and the display unit <NUM> may be integrated to form a touch panel display.

The I/F unit <NUM> performs communication of various types of information between the mammography apparatus <NUM> and the RIS <NUM> by wireless communication or wired communication. The console <NUM> according to the present embodiment receives the image data of the radiation image captured by the mammography apparatus <NUM> from the mammography apparatus <NUM> via the I/F unit <NUM> by wireless communication or wired communication.

Further, a functional configuration of the console <NUM> according to the present embodiment will be described with reference to <FIG> and <FIG>. <FIG> shows an example of imaging timings of a low-energy image <NUM> and a high-energy image <NUM> in contrast imaging by the mammography apparatus <NUM> according to the present embodiment. In the example shown in <FIG>, in a case in which the contrast imaging is started, first, a low-energy image <NUM> (see <FIG>, <NUM><NUM>) is captured, and then high-energy images <NUM> (see <FIG>, <NUM><NUM> to <NUM><NUM>) are captured each time the predetermined time elapses. Then, in a case in which a body movement of the breast is detected, the low-energy image <NUM> (see <FIG>, <NUM><NUM>) is re-captured, and then the high-energy image <NUM> (see <FIG>, <NUM><NUM>) is imaged each time a predetermined time elapses. In this way, the low-energy image <NUM> and the high-energy image <NUM> are repeatedly captured until a contrast imaging time ends.

Further, <FIG> shows a functional block diagram of an example of the configuration of the console <NUM> according to the present embodiment. As shown in <FIG>, the console <NUM> comprises an acquisition unit <NUM>, a derivation unit <NUM>, a control unit <NUM>, and a notification unit <NUM>. As an example, in the console <NUM> according to the present embodiment, the CPU 50A of the control unit <NUM> also functions as the acquisition unit <NUM>, the derivation unit <NUM>, the control unit <NUM>, and the notification unit <NUM> by the CPU 50A executing the contrast imaging control processing program 51A stored in the ROM 50B.

The acquisition unit <NUM> has a function of acquiring the low-energy image <NUM> and the high-energy image <NUM> captured by the mammography apparatus <NUM>. Specifically, the acquisition unit <NUM> acquires image data representing the low-energy image <NUM> and image data representing the high-energy image <NUM> captured by the radiation detector <NUM> of the mammography apparatus <NUM> via the I/F unit <NUM> and the I/F unit <NUM>. The acquisition unit <NUM> outputs the acquired low-energy image <NUM> and high-energy image <NUM> to the derivation unit <NUM> and the generation unit <NUM>.

The derivation unit <NUM> has a function of deriving an amount of the body movement of the breast (hereinafter, referred to as "body movement amount") from each of the plurality of high-energy images <NUM>. The body movement of the breast includes a case in which a body tissue, such as a mammary gland structure, in the breast is moved and a case in which the breast is moved as a whole due to the body movement of the examinee. As the breast is thicker, the mammary gland structure tends to be likely to be moved with the temporal change even in a compression state. Therefore, as the breast is thicker, the body movement is likely to occur. In addition, since the breast is softer as a proportion of fat is increased as the composition of the breast, the mammary gland structure tends to be likely to be moved with the temporal change even in the compression state. Therefore, as the proportion of fat in the breast is higher or as the breast is softer, the body movement tends to be likely to occur. In addition, as the subject gets older, it is difficult for the subject to maintain the same posture, so that the subject itself tends to be likely to be moved. Therefore, as the subject gets older, the body movement tends to be likely to occur. The derivation unit <NUM> according to the present embodiment derives the body movement amount of the breast that has occurred in this way. The derivation unit <NUM> outputs the derived body movement amount of the breast to the control unit <NUM> and the generation unit <NUM>.

As shown in <FIG> as an example, the derivation unit <NUM> according to the present embodiment generates a difference image for body movement analysis <NUM> (see <FIG>, <NUM> to <NUM><NUM>) showing a difference between the high-energy images <NUM> (see <FIG>, <NUM><NUM> to <NUM><NUM>) which are continuous in time series, and derives the body movement amount based on the generated difference image for body movement analysis <NUM>.

Specifically, the derivation unit <NUM> generates the difference image for body movement analysis <NUM><NUM> showing the difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM>. More specifically, the derivation unit <NUM> generates the difference image data for body movement analysis representing the difference image for body movement analysis <NUM><NUM> by subtracting the image data of the high-energy image <NUM><NUM> from the image data of the high-energy image <NUM><NUM> for each corresponding pixel. In addition, the derivation unit <NUM> derives the body movement amount of the breast from the generated difference image for body movement analysis <NUM><NUM>. Similarly, the derivation unit <NUM> generates a difference image for body movement analysis <NUM><NUM> showing the difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM>, and derives the body movement amount of the breast from the generated difference image for body movement analysis <NUM><NUM>. The derivation unit <NUM> generates the difference image for body movement analysis <NUM><NUM> showing the difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM>, and derives the body movement amount of the breast from the generated difference image for body movement analysis <NUM><NUM>. The derivation unit <NUM> generates the difference image for body movement analysis <NUM><NUM> showing the difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM>, and derives the body movement amount of the breast from the generated difference image for body movement analysis <NUM><NUM>.

It should be noted that, in the derivation unit <NUM> according to the present embodiment, an index value corresponding to the body movement amount and varying according to the body movement amount is derived as the body movement amount, instead of the actual body movement amount itself of the body movement of the breast. In addition, a method by which the derivation unit <NUM> derives the body movement amount of the breast from the difference image for body movement analysis <NUM> is not limited. For example, the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM> before and after the body movement has occurred tends to have a greater pixel value than the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM> in which the body movement does not occur. Therefore, the derivation unit <NUM> may derive a total value of the pixel values of the difference image for body movement analysis <NUM> as the body movement amount. In addition, for example, in the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM> before and after the body movement has occurred, the body movement appears as a line, and thus the high-frequency component tends to be increased as compared with the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM> in which the body movement does not occur. In addition, the image having the high-frequency component tends to be smaller influenced by the temporal change of the contrast amount than the image of the low-frequency component. Therefore, the derivation unit <NUM> may derive a total value of the pixel values of the image having the high-frequency component in the difference image for body movement analysis <NUM> as the body movement amount.

In addition, although the body movement amount of the breast that occurs during the imaging interval between the continuous high-energy images <NUM> is small, in a case in which the body movement is gradually performed over a long period of time, the body movement amount may be increased as a result. For example, in the example shown in <FIG>, the body movement amount of the breast is small in a case in which the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM> are compared, but the body movement amount of the breast may be large in a case in which the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM> are compared. In such a case, it is preferable to adopt a form in which the body movement amount is derived based on the image obtained by adding the generated difference image for body movement analysis <NUM>.

The control unit <NUM> has a function of controlling the contrast imaging. Specifically, the control unit <NUM> has a function of performing control related to the irradiation with the radiation R in the mammography apparatus <NUM> in the contrast imaging. More specifically, in the contrast imaging, the control unit <NUM> has a function of performing control of emitting the radiation R having the first energy from the radiation source 37R and control of emitting the radiation R having the second energy. In other words, the control unit <NUM> has a function of performing control of causing the mammography apparatus <NUM> to capture the low-energy image <NUM> and control of causing the mammography apparatus <NUM> to capture the high-energy image <NUM>.

For example, an iodine contrast medium with a k-absorption edge of <NUM> keV is generally used as the contrast medium for the contrast imaging. In the contrast imaging in this case, the low-energy image <NUM> is captured by emitting the radiation R having the first energy lower than the k-absorption edge of the iodine contrast medium. In addition, the high-energy image <NUM> is captured by emitting the radiation R having the second energy higher than the k-absorption edge of the iodine contrast medium.

A body tissue, such as a mammary gland, and the contrast medium have different absorption characteristics of the radiation. Therefore, in the high-energy image <NUM> captured as described above, the body tissue, such as the mammary gland or fat, is reflected, and the contrast medium is clearly reflected. In addition, in the low-energy image <NUM>, almost no contrast medium is reflected, and the body tissue, such as the mammary gland or fat, is clearly reflected. Therefore, a difference image <NUM> indicating a difference between the low-energy image <NUM> and the high-energy image <NUM> can be made to be an image in which a mammary gland structure is removed and the contrast medium is clearly reflected.

In addition, in the contrast imaging, as shown in <FIG>, changes in a state in which the contrast medium permeates the breast are imaged in time series. For example, the contrast medium tends to more easily permeate in a lesion, such as a tumor, than the mammary gland. Also, as the lesion is more malignant, the contrast medium tends to permeate faster and the contrast medium tends to be washed out faster. Therefore, in the radiography system <NUM> according to the present embodiment, a temporal change or an amount of permeation (contrast amount) of the contrast medium permeating a region of interest, such as the lesion, is observed by using a plurality of difference images <NUM> obtained in time series.

In order to obtain the plurality of difference images <NUM>, in the present embodiment, after the low-energy image <NUM> is captured, the high-energy image <NUM> is captured each time a predetermined time, such as <NUM> second, elapses. As described above, in order to observe the temporal change of the contrast amount of the region of interest, it is necessary to capture the high-energy image <NUM> in which the contrast medium is clearly reflected, according to the temporal change. On the other hand, the low-energy image <NUM> does not need to be captured as frequently as the high-energy image <NUM> because the temporal change of the state of the mammary gland structure, particularly, the temporal change of the imaging time of the contrast imaging is very small. However, in a case in which the body movement of the breast has occurred, an appropriate difference image <NUM> cannot be generated because, for example, the appearance of the mammary gland structure is different between the low-energy image <NUM> before the body movement and the high-energy image <NUM> after the body movement.

Therefore, the control unit <NUM> according to the present embodiment performs control of re-capturing the low-energy image <NUM> in a case in which the body movement amount of the breast derived by the derivation unit <NUM> exceeds a threshold value. For example, as described above, in a case in which the derivation unit <NUM> derives the total value of the pixel values of the difference image for body movement analysis <NUM> or the total value of the pixel values of the image having the high-frequency component in the difference image for body movement analysis <NUM> as the body movement amount, the control unit <NUM> performs control of re-capturing the low-energy image <NUM> in a case in which these pixel values exceed the threshold value. In this case, as the threshold value is, for example, a total value of the pixel values of the difference image for body movement analysis <NUM> between the high-energy images <NUM> before and after the body movement of the breast exceeding an allowable range has occurred, or a total value of the pixel values of the image having the high-frequency component of the difference image for body movement analysis <NUM> may be applied. It should be noted that, in this case, the allowable range of the body movement of the breast can be determined in consideration of, for example, an image quality of the difference image <NUM> showing the difference between the low-energy image <NUM> and the high-energy image <NUM>.

The notification unit <NUM> has a function of notifying the user that the body movement of the breast has occurred in a case in which the control unit <NUM> performs control of re-capturing the low-energy image <NUM>, in other words, in a case in which the body movement amount of the breast exceeds the threshold value. It should be noted that a notification method in which the notification unit <NUM> notifies that the body movement of the breast has occurred is not particularly limited, and for example, display may be performed by any of an audible display or a visible display.

In addition, the console <NUM> according to the present embodiment comprises the generation unit <NUM> and the display control unit <NUM>. As an example, in the console <NUM> according to the present embodiment, the CPU 50A of the control unit <NUM> functions as the generation unit <NUM> and the display control unit <NUM> by the CPU 50A executing the difference image generation display processing program 51B stored in the ROM 50B.

The generation unit <NUM> has a function of generating the plurality of difference images <NUM> showing the difference between the low-energy image <NUM> and each of a plurality of high-energy images <NUM>. As an example, the generation unit <NUM> according to the present embodiment generates the difference image <NUM> between the low-energy image <NUM> and the plurality of high-energy images <NUM> captured in a period from capturing of a current low-energy image <NUM> to capturing of a next low-energy image <NUM>. The generation unit <NUM> generates the difference image <NUM> showing the difference between the re-captured low-energy image <NUM> and the high-energy image <NUM> in which the body movement amount derived by the derivation unit <NUM> exceeds the threshold value.

As an example, in the present embodiment, the difference image <NUM> is generated by deriving the difference between the low-energy image <NUM> and each high-energy image <NUM>. Specifically, as shown in <FIG>, the generation unit <NUM> generates a difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>. Specifically, the generation unit <NUM> generates the difference image data representing the difference image <NUM> in which the mammary gland tissue is removed and the contrast medium is enhanced, by subtracting image data obtained by multiplying the low-energy image <NUM><NUM> by a predetermined coefficient from image data obtained by multiplying the high-energy image <NUM><NUM> by a predetermined coefficient for each corresponding pixel. Similarly, the generation unit <NUM> generates a difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>, generates a difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>, and generates a difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>. In addition, the generation unit <NUM> generates a difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>.

It should be noted that a method by which the generation unit <NUM> generates the difference image <NUM> is not limited to the method described above. For example, the difference image <NUM> may be generated by adding the difference between the high-energy images <NUM> to the difference between the low-energy image <NUM> and the high-energy image <NUM>. Specifically, as shown in <FIG>, as described above, the generation unit <NUM> generates the difference image <NUM><NUM> between the low-energy image <NUM><NUM> and the high-energy image <NUM><NUM>. In addition, the generation unit <NUM> generates the difference image <NUM><NUM> by adding an image showing a difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM> to the difference image <NUM><NUM>, generates the difference image <NUM><NUM> by adding an image showing a difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM> to the difference image <NUM><NUM>, and generates the difference image <NUM><NUM> by adding an image showing a difference between the high-energy image <NUM><NUM> and the high-energy image <NUM><NUM> to the difference image <NUM><NUM>.

It should be noted that the generation unit <NUM> according to the present embodiment performs registration between the low-energy image <NUM> and the high-energy image <NUM> before generating the difference image <NUM> showing the difference between the low-energy image <NUM> and the high-energy image <NUM>. For example, in a case in which the body movement of the breast has occurred even in a case in which the body movement amount is equal to or smaller than the threshold value, a position of a skin line or a position of a region of interest in the low-energy image <NUM> and a position of a skin line or a position of a region of interest in the high-energy image <NUM> are deviated. That is, the high-energy image <NUM> may be deviated according to the body movement amount of the breast. Therefore, it is preferable that the generation unit <NUM> generates the difference image <NUM> after correcting the deviation by performing registration between the low-energy image <NUM> and the high-energy image <NUM>. For example, it is preferable that the high-energy image <NUM> is corrected according to the body movement amount, and the difference image <NUM> showing the difference between the corrected high-energy image <NUM> and the low-energy image <NUM> is generated.

A specific method of performing registration between the low-energy image <NUM> and the high-energy image <NUM> by the generation unit <NUM> is not particularly limited, and the method need only be a method of associating portions (parts) that are considered to be anatomically the same and transforming the image into a state in which the corresponding portions overlap. For example, as in a known technology disclosed in <CIT>, registration may be performed by moving a breast image showing the breast in parallel in a state in which the centroids of the mammary glands match and aligning the positions of the centroids. In addition, for example, as in a known technology disclosed in <CIT>, linear registration may be performed by using an affine transformation or the like. In addition, for example, registration between the positions of the centroids of the breast region may be performed as in a known technology disclosed in <CIT>.

It should be noted that, as registration performed by the generation unit <NUM>, it is more preferable to perform registration between the position of the region of interest in the low-energy image <NUM> and the position of the region of interest in the high-energy image <NUM>. Therefore, the generation unit <NUM> according to the present embodiment performs registration between the position of the region of interest in the low-energy image <NUM> and the position of the region of interest in the high-energy image <NUM>. As an example, the generation unit <NUM> according to the present embodiment specifies the region of interest by applying computer aided diagnosis (CAD) to each of the low-energy image <NUM> and the high-energy image <NUM>. It should be noted that the method of specifying the region of interest is not limited to the present form, for example, the region of interest may be specified from each of the low-energy image <NUM> and the high-energy image <NUM> by displaying the low-energy image <NUM> and the high-energy image <NUM> on the display unit <NUM> and receiving the information about the region of interest designated by the user for each of the low-energy image <NUM> and the high-energy image <NUM>. It should be noted that the position or the shape of the region of interest that shifts to the radiation image may be changed before and after the body movement of the breast has occurred. Therefore, it is preferable to specify the region of interest for each of the captured low-energy image <NUM> and high-energy image <NUM>, in other words, for each of the captured radiation images. It should be noted that, in a case in which the user specifies the region of interest from the radiation image displayed on the display unit <NUM>, it is relatively difficult for the user to designate the region of interest for each of the captured radiation images. In this case, the user may designate the region of interest for the radiation images before and after the body movement of the breast has occurred.

The display control unit <NUM> has a function of causing the display unit <NUM> to continuously display the difference images <NUM> generated by the generation unit <NUM> as a moving image in a time series order. In the present embodiment, the "moving image" means that still images are displayed one after another at high speed and recognized as the moving image. Therefore, the so-called "frame advance" is also included in the moving image depending on a degree of "high speed" in the display.

In addition, the display control unit <NUM> according to the present embodiment has a function of deriving each of information indicating the temporal change of the contrast amount of the region of interest in the difference image <NUM> and information indicating the temporal change of the contrast amount of an outside of the region of interest and displaying the derived information on the display unit <NUM>. It should be noted that a method by which the display control unit <NUM> specifies the region of interest from the difference image is not particularly limited. For example, in a case in which the generation unit <NUM> specifies the region of interest, the display control unit <NUM> may specify the region of interest from the difference image <NUM> based on the position of the region of interest specified by the generation unit <NUM>. In addition, for example, the region of interest may be specified from the difference image <NUM> by receiving information about the region of interest input by the user. Specifically, at least one image of the difference image <NUM>, the low-energy image <NUM>, or the high-energy image <NUM> may be displayed on the display unit <NUM>, and a region designated by the user operating the operation unit <NUM> on the display image may be received as the information about the region of interest. In addition, for example, the display control unit <NUM> may specify the region of interest by applying the CAD to the difference image <NUM>. It should be noted that a method by which the display control unit <NUM> specifies the outside of the region of interest from the difference image <NUM> is not particularly limited. For example, a region excluding the region of interest from the region representing the breast in the difference image <NUM> may be specified as the outside of the region of interest. In addition, for example, a mammary gland region other than the region of interest may be specified as the outside of the region of interest.

In addition, the display control unit <NUM> according to the present embodiment has a function of displaying, on the display unit <NUM>, information indicating a timing at which the body movement of the breast has occurred, more specifically, a timing at which the body movement amount of the breast derived by the derivation unit <NUM> exceeds the threshold value.

Next, an action of the console <NUM> in the contrast imaging by the radiography system <NUM> according to the present embodiment will be described with reference to the drawings.

<FIG> shows a flowchart showing an example of a flow of the contrast imaging by the radiography system <NUM> according to the present embodiment. In a case in which the contrast imaging is performed, first, the user injects the contrast medium into the breast, which is the subject, as shown in step S10 of <FIG>. Next, as shown in step S12, the user positions the breast of the examinee on the imaging table <NUM> of the mammography apparatus <NUM> and compresses the breast with the compression plate <NUM>.

Next, in step S14, the contrast imaging control processing shown in <FIG> as an example is performed by the console <NUM> in order to perform the contrast imaging by the mammography apparatus <NUM>. In the present embodiment, as described above, the control unit <NUM> of the console <NUM> performs control related to the irradiation with the radiation R in the mammography apparatus <NUM>. In the console <NUM> according to the present embodiment, as an example, the CPU 50A of the control unit <NUM> executes the contrast imaging control processing program 51A stored in the ROM 50B, thereby executing the contrast imaging control processing shown in <FIG> as an example. <FIG> shows a flowchart showing an example of a flow of the contrast imaging control processing executed in the console <NUM> according to the present embodiment.

In step S100 of <FIG>, the control unit <NUM> determines whether or not the irradiation instruction of the radiation R is received. A negative determination is made in the determination in step S100 until the irradiation instruction is received. On the other hand, in a case in which the irradiation instruction is received, a positive determination is made in the determination in step S100, and the processing proceeds to step S102.

In step S102, the control unit <NUM> outputs the instruction to perform the irradiation with the radiation R having the first energy to the mammography apparatus <NUM>. In the mammography apparatus <NUM>, the control unit <NUM> emits the radiation R having the first energy from the radiation source 37R toward the breast based on the instruction input from the console <NUM>, and the low-energy image <NUM> is captured by the radiation detector <NUM>.

In next step S104, the acquisition unit <NUM> acquires the low-energy image <NUM> from the mammography apparatus <NUM>, as described above.

In next step S106, the control unit <NUM> determines whether or not a predetermined time has elapsed. A negative determination is made in the determination in step S106 until the predetermined time elapses. On the other hand, in a case in which the predetermined time has elapsed, a positive determination is made in the determination in step S106, and the processing proceeds to step S108.

In step S108, the control unit <NUM> outputs the instruction to perform the irradiation with the radiation R having the second energy to the mammography apparatus <NUM>. In the mammography apparatus <NUM>, the control unit <NUM> emits the radiation R having the second energy from the radiation source 37R toward the breast based on the instruction input from the console <NUM>, and the high-energy image <NUM> is captured by the radiation detector <NUM>.

In next step S110, the acquisition unit <NUM> acquires the high-energy image <NUM> from the mammography apparatus <NUM>, as described above.

In step S112, the control unit <NUM> determines whether or not to end the present contrast imaging control processing. In a case in which a predetermined end condition is not satisfied, a negative determination is made in the determination in step S112, and the processing proceeds to step S114. The end condition may be, for example, a condition in which the processing ends in a case in which an elapsed time from the injection of the contrast medium into the breast has passed a time that is determined as the imaging time, in a case in which an elapsed time from the start of the irradiation with the radiation R has passed a time that is determined as a cumulative time of the irradiation time in the contrast imaging, in a case in which the number of times of capturing of the radiation image reaches a predetermined number of times, and in a case in which an instruction to end the imaging is received from the user.

In step S114, as described above, the derivation unit <NUM> derives the body movement amount of the breast from the high-energy image <NUM>. In the present embodiment, as described above, the derivation unit <NUM> generates the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM>, and derives the body movement amount of the breast from the difference image for body movement analysis <NUM>.

In next step S116, the control unit <NUM> determines whether or not the predetermined time has elapsed, as in step S106. A negative determination is made in the determination in step S116 until the predetermined time elapses. On the other hand, in a case in which the predetermined time has elapsed, a positive determination is made in the determination in step S116, and the processing proceeds to step S118.

In step S118, the control unit <NUM> determines whether or not the body movement amount of the breast derived in step S114 exceeds the threshold value (body movement amount > threshold value). In a case in which the body movement amount of the breast does not exceed the threshold value, in other words, in a case in which the body movement amount of the breast is equal to or smaller than the threshold value, a negative determination is made the determination in step S118, and the processing proceeds to step S120.

It should be noted that, in a case of the high-energy image <NUM> (see <FIG>, high-energy image <NUM><NUM>) captured first after the start of the contrast imaging, the next high-energy image <NUM> (see <FIG>, high-energy image <NUM><NUM>) has not yet been captured. Therefore, it is not possible to generate the difference image for body movement analysis <NUM> showing the difference between the high-energy images <NUM>. Therefore, after the high-energy image <NUM> is acquired in step S110, in a case in which the processing after S120 has not been performed even once, the processing of step S114 is omitted, and in a case in which a positive determination is made in step S116, the processing of step S118 is omitted, and the processing proceeds to step S120.

In step S120, the control unit <NUM> outputs the instruction to perform the irradiation with the radiation R having the second energy to the mammography apparatus <NUM>, as in step S108. In the mammography apparatus <NUM>, the control unit <NUM> emits the radiation R having the second energy from the radiation source 37R toward the breast based on the instruction input from the console <NUM>, and the high-energy image <NUM> is captured by the radiation detector <NUM>.

In next step S122, the acquisition unit <NUM> acquires the high-energy image <NUM> from the mammography apparatus <NUM>, as described above. In a case in which the processing of step S122 ends, the processing returns to step S112 and repeats the processing of steps S112 to S118 described above.

On the other hand, in step S118, in a case in which the body movement amount of the breast exceeds the threshold value, a positive determination is made, and the processing proceeds to step S124.

In step S124, the control unit <NUM> outputs the instruction to perform the irradiation with the radiation R having the first energy to the mammography apparatus <NUM>, as in step S102. In the mammography apparatus <NUM>, the control unit <NUM> emits the radiation R having the first energy from the radiation source 37R toward the breast to re-capture the low-energy image <NUM> (see <FIG>, low-energy image <NUM><NUM>) by the radiation detector <NUM> based on the instruction input from the console <NUM>.

In next step S126, the acquisition unit <NUM> acquires the re-captured low-energy image <NUM> from the mammography apparatus <NUM>, as described above.

In next step S128, the notification unit <NUM> notifies that the body movement of the breast has occurred. The notification unit <NUM> notifies that the body movement of the breast has occurred, so that the user confirms the state of the examinee, for example. As a result of the confirmation, for example, in a case in which the examinee is moved significantly, the user may give an instruction to stop the contrast imaging to the console <NUM> or the mammography apparatus <NUM>. In a case in which the processing of step S128 ends, the processing returns to step S112 and repeats the processing of steps S112 to S118 described above.

On the other hand, in a case in which the end condition is satisfied in step S112, a positive determination is made in the determination, and the present contrast imaging control processing ends.

In a case in which the contrast imaging control processing shown in <FIG> ends in this way, the contrast imaging ends, and the processing of step S14 shown in <FIG> ends.

In next step S16, the console <NUM> performs difference image generation display processing shown in <FIG>. In the console <NUM> according to the present embodiment, as an example, the CPU 50A of the control unit <NUM> executes the difference image generation display processing program 51B stored in the ROM 50B, thereby executing the difference image generation display processing shown in <FIG> as an example. <FIG> shows a flowchart showing an example of a flow of the difference image generation display processing executed in the console <NUM> according to the present embodiment.

In step S200, the generation unit <NUM> specifies the region of interest from each of the low-energy image <NUM> and the high-energy image <NUM> acquired by the acquisition unit <NUM> from the mammography apparatus <NUM>. Specifically, the generation unit <NUM> according to the present embodiment specifies the region of interest by applying the CAD to each of all the low-energy images <NUM> and the high-energy images <NUM> acquired by the acquisition unit <NUM>.

In next step S202, the generation unit <NUM> performs registration between the low-energy image <NUM> and the high-energy image <NUM>, which are a combination for generating the difference image <NUM>. As an example, as described above, the generation unit <NUM> according to the present embodiment performs registration between the position of the region of interest in the low-energy image <NUM> and the position of the region of interest in the high-energy image <NUM>.

In next step S204, as described above, the generation unit <NUM> generates the plurality of difference images <NUM> from all the low-energy images <NUM> and the high-energy images <NUM> acquired by the acquisition unit <NUM> from the mammography apparatus <NUM>. In next step S204, the display control unit <NUM> specifies the region of interest from the difference image <NUM>, as described above.

In next step S206, as described above, the display control unit <NUM> derives the information indicating the temporal change of the contrast amount. Specifically, the display control unit <NUM> derives the information indicating the temporal change of the contrast amount of the region of interest specified in step S200 in the difference image <NUM> generated in step S204. It should be noted that the display control unit <NUM> may not derive the contrast amount itself. For example, a brightness value of the pixel in the difference image <NUM> is changed according to the contrast amount. Therefore, the information indicating the temporal change of the brightness value of the difference image <NUM> may be used as the information indicating the temporal change of the contrast amount.

<FIG> shows an example of information <NUM> indicating the temporal change of the contrast amount. In the information shown in <FIG>, the horizontal axis represents the elapsed time since the contrast medium has been injected. In addition, the vertical axis represents the contrast amount. It should be noted that, as described above, the contrast amount in this case may not be the contrast amount itself, but may be the brightness value of the pixel. In the information shown in <FIG>, a solid line shows an example of the temporal change of the contrast amount in a case in which the region of interest is a tumor, that is, a breast cancer. In addition, an example of the temporal change in the mammary gland region as the outside of the region of interest is shown by a dotted line. As shown in <FIG>, in a case of the tumor, the contrast medium rapidly permeates and the contrast medium is washed out faster. Therefore, by observing the temporal change of the contrast amount of the region of interest, it can be used as an index for diagnosing whether or not the region of interest is the tumor and whether or not the region of interest is malignant. In addition, although there are individual differences in how the contrast medium is dyed, by comparing the temporal change of the contrast amount of the region outside the region of interest, for example, the mammary gland region assumed to be normal with the temporal change of the contrast amount of the region of interest, the speed at which the contrast medium permeates and the speed at which the contrast medium is washed out can be made clearer.

In next step S208, the display control unit <NUM> performs control of displaying, on the display unit <NUM>, the plurality of difference images <NUM> generated in step S204 and the information <NUM> indicating the temporal change of the contrast amount derived in step S206, and then the present difference image generation display processing ends. It should be noted that the display control unit <NUM> performs control of performing predetermined image processing of assisting the user in interpreting the image, such as gradation enhancement processing or frequency enhancement processing, on the plurality of difference images <NUM> generated in step S204 and displaying the plurality of difference images <NUM> which have been subjected to the image processing on the display unit <NUM>.

<FIG> shows an example of a state in which a moving image <NUM> and the information <NUM> indicating the temporal change of the contrast amount are displayed on the display unit <NUM>. In the example shown in <FIG>, information <NUM> indicating the timing at which the body movement of the breast has occurred is added to the information <NUM> indicating the temporal change of the contrast amount. In a case in which the low-energy image <NUM> is re-captured as described above, due to the influence of the body movement of the breast and the like, the positions of the skin line, the mammary gland structure, the region of interest, and the like may be deviated between the difference image <NUM> using the low-energy image <NUM> before the re-capturing and the difference image <NUM> using the low-energy image <NUM> after the re-capturing. Therefore, it is preferable that the user can recognize the timing at which the body movement of the breast has occurred, in other words, the timing at which the low-energy image <NUM> is captured. Therefore, as shown in <FIG>, the display control unit <NUM> according to the present embodiment displays, on the display unit <NUM>, the information <NUM> indicating the timing at which the body movement of the breast has occurred.

It should be noted that the form in which the display control unit <NUM> displays, on the display unit <NUM>, the information <NUM> indicating the timing at which the body movement of the breast has occurred is not limited to the form shown in <FIG>. For example, as shown in <FIG>, the information <NUM> indicating the timing at which the body movement of the breast has occurred may be displayed as a form in which an order in which the low-energy images <NUM> and the high-energy images <NUM> are captured is represented along with the elapsed time. As shown in <FIG>, in a case in which the information <NUM> indicating the timing at which the body movement of the breast has occurred is displayed, the user can recognize a timing at which the low-energy image <NUM> is re-captured as the timing at which the body movement of the breast has occurred.

In addition, a form may be adopted in which the information <NUM> indicating the timing at which the body movement of the breast has occurred is displayed by a marker or the like in the moving image <NUM> described below. Specifically, the marker or the like may be displayed as the information <NUM> indicating the timing at which the body movement of the breast has occurred, on the difference image <NUM> using the high-energy image <NUM> in which the body movement amount of the breast exceeds the threshold value among the plurality of difference images <NUM> constituting the moving image <NUM>.

In addition, as described above, the display control unit <NUM> according to the present embodiment continuously displays, on the display unit <NUM>, the plurality of difference images <NUM> as the moving image <NUM> in the time series order of capturing. In the example shown in <FIG>, positional information <NUM> indicating a position of the region of interest is also displayed on the difference image <NUM> as the moving image <NUM>.

It should be noted that, in a case in which the moving image <NUM> is displayed, a timing for displaying the next difference image <NUM> may be changed according to a contrast value of the region of interest. For example, in a case in which the contrast value of the region of interest is equal to or greater than a threshold value, the timing for displaying the next difference image <NUM> may be delayed, that is, the display speed of the moving image may be made slower than in a case in which the contrast value is smaller than the threshold value. In addition, the display speed of the moving image <NUM> may be adjustable by the user.

It should be noted that the difference image <NUM> displayed by the display control unit <NUM> is not limited to a form of the moving image <NUM>. For example, a form may be adopted in which, among the plurality of difference images <NUM> generated by the generation unit <NUM>, a difference image <NUM> having a highest contrast of the region of interest is displayed. In addition, for example, a form may be adopted in which, by displaying a radiation image <NUM> described below or the low-energy image <NUM>, the difference image <NUM> having the highest contrast of a region designated by the user on the radiation image <NUM> or the low-energy image <NUM> is displayed.

In addition, as shown in <FIG>, the display control unit <NUM> according to the present embodiment also displays the radiation image <NUM> on the display unit <NUM> as a comparative example in a case in which there is the radiation image <NUM> captured by the general imaging for the breast which is the subject, in other words, the radiation image <NUM> captured in a state in which the contrast medium has not been injected. It should be noted that, in the example shown in <FIG>, the form has been described in which the moving image <NUM> and the radiation image <NUM> are displayed side by side, a form may be adopted in which any one of the moving image <NUM> or the radiation image <NUM> is displayed and the image to be displayed is switched according to the instruction of the user.

It should be noted that the radiation image displayed by the display control unit <NUM> on the display unit <NUM> is not limited to the image described above. For example, a form may be adopted in which, in addition to the difference image <NUM>, at least one of the low-energy image <NUM> or the high-energy image <NUM> is displayed.

In addition, the image and the information displayed by the display control unit <NUM> on the display unit <NUM> are not limited to the image and the information described above. For example, a numerical value indicating the contrast amount of the region of interest may be displayed. In this case, the contrast amount may be the contrast amount of the entire region of interest, or may be any of an average value, a median value, or a maximum value of the contrast amount of the region of interest.

In this way, in a case in which the difference image generation display processing shown in <FIG> ends, the difference image generation display processing in step S16 shown in <FIG> ends. As a result, the series of processing related to the contrast imaging in the radiography system <NUM> according to the present embodiment ends. It should be noted that a form may be adopted in which the low-energy image <NUM> and the plurality of high-energy images <NUM>, which are captured by the mammography apparatus <NUM> according to the present embodiment, the plurality of difference images <NUM>, the moving image <NUM>, and the information <NUM> indicating the temporal change of the contrast amount, which are generated by the console <NUM>, and the like are stored in the storage unit <NUM> of the console <NUM>, picture archiving and communication systems (PACS), or the like.

In addition, in each form described above, the form has been described in which the difference image generation display processing is continuously performed after the contrast imaging control processing which is the processing of S <NUM> in <FIG> ends, in other words, after the contrast imaging ends, but the timing for performing the difference image generation display processing, that is, the timing for generating the difference image <NUM> or displaying the difference image <NUM> is not limited to the present form. For example, a form may be adopted in which the timing of each of the generation of the difference image <NUM> and the display of the difference image <NUM> is a timing according to the user's desire after the contrast imaging.

As described above, the console <NUM> of each form described above comprises the CPU 50A as at least one processor. The CPU 50A acquires the low-energy image <NUM> captured by the mammography apparatus <NUM> by emitting the radiation R having the first energy to the breast into which the contrast medium has been injected. In addition, the CPU 50A sequentially acquires each of the plurality of high-energy images <NUM> captured by the mammography apparatus <NUM> at different timings by emitting the radiation R having the second energy higher than the first energy to the breast into which the contrast medium has been injected. In addition, the CPU 50A sequentially derives the body movement amount of the breast from each of the plurality of high-energy images <NUM>, and performs, in a case in which the derived body movement amount exceeds the threshold value, control of causing the mammography apparatus <NUM> to re-capture the low-energy image <NUM> before the next high-energy image <NUM> is captured. In addition, the CPU 50A generates the plurality of difference images <NUM> showing the difference between the low-energy image <NUM> and each of the plurality of high-energy images <NUM>.

As described above, with the console <NUM> according to the present embodiment, in a case in which the body movement amount exceeds the threshold value, the mammography apparatus <NUM> re-captures the low-energy image <NUM>, so that the influence of the body movement of the subject in the contrast imaging can be reduced. In addition, the radiation R having high energy is easily transmitted through fat, and an exposure dose of the subject is reduced as compared with the radiation R having low energy. Therefore, according to the present embodiment, the number of times of capturing of the low-energy image <NUM> can be made smaller than the number of times of capturing of the high-energy image <NUM>, so that the exposure dose of the subject can be reduced.

It should be noted that, in the form described above, as shown in <FIG> and <FIG>, the form has been described in which the generation unit <NUM> generates the difference image <NUM> between the low-energy image <NUM> and the high-energy images <NUM> captured before the next low-energy image <NUM> is captured, but a combination of the low-energy image <NUM> and the high-energy image <NUM> for generating the difference image <NUM> is not limited to the present form.

For example, a form may be adopted in which the difference image with the low-energy image having the imaging timing closest to the high-energy image is generated. Specifically, as shown in <FIG>, the generation unit <NUM> generates the difference image <NUM><NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>, and generates the difference image <NUM><NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>. In addition, the generation unit <NUM> generates the difference image <NUM><NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>, generates the difference image <NUM><NUM> of the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>, and generates the difference image <NUM><NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>. In this way, the influence of the body movement can be reduced by generating the difference image by combining the low-energy image captured at the timing closest to the imaging timing of the high-energy image.

In addition, for example, the low-energy image <NUM> used for generating the difference image <NUM> may be switched with the timing at which the body movement of the breast has occurred as a reference. An example of this case is shown in <FIG>. In the example shown in <FIG>, the generation unit <NUM> generates the difference image <NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>. On the other hand, in the example shown in <FIG> described above, the generation unit <NUM> generates the difference image <NUM><NUM> between the high-energy image <NUM><NUM> and the low-energy image <NUM><NUM>. As described above, for the high-energy image <NUM> captured after the body movement of the breast has occurred, the influence of the body movement can be further reduced by generating the difference image <NUM> showing the difference from the re-captured low-energy image <NUM>.

In addition, in the form described above, the form has been described in which, as described with reference to <FIG>, the derivation unit <NUM> derives the body movement amount based on the difference images for body movement analysis <NUM><NUM> to <NUM><NUM> showing the difference between the high-energy images <NUM><NUM> to <NUM><NUM> which are continuous in time series, but a method by which the derivation unit <NUM> derives the body movement amount of the breast is not limited to the present form.

For example, a form may be adopted in which the derivation unit <NUM> uses the low-energy image <NUM> as a reference and derives the body movement amount of the breast based on the deviation of the high-energy image <NUM> from the reference. Specifically, a form can be adopted in which the derivation unit <NUM> uses a position of a specific structure, such as the region of interest or the mammary gland, in the low-energy image <NUM> as a reference, derives a movement vector of the specific structure in the high-energy image <NUM>, and detects that the body movement of the breast has occurred in a case in which magnitude of the derived movement vector exceeds a threshold value.

In addition, in the form described above, the form has been described in which the breast is applied as an example of the subject according to the present disclosure, and the mammography apparatus <NUM> is applied as an example of the radiography apparatus according to the present disclosure, but the subject is not limited to the breast, and the radiography apparatus is not limited to the mammography apparatus. For example, the subject may be a chest, an abdomen, or the like, and a form may be adopted in which a radiography apparatus other than the mammography apparatus is applied as the radiography apparatus.

In addition, in the form described above, the form has been described in which the console <NUM> is an example of the control apparatus according to the present disclosure, but an apparatus other than the console <NUM> may have the function of the control apparatus according to the present disclosure. In other words, some or all of the functions of the acquisition unit <NUM>, the derivation unit <NUM>, the control unit <NUM>, the notification unit <NUM>, the generation unit <NUM>, and the display control unit <NUM> may be provided in an apparatus other than the console <NUM>, for example, the mammography apparatus <NUM> or an external apparatus.

In addition, in the form described above, various processors shown below can be used as the hardware structure of processing units that execute various pieces of processing, such as the acquisition unit <NUM>, the derivation unit <NUM>, the control unit <NUM>, the notification unit <NUM>, the generation unit <NUM>, and the display control unit <NUM>. As described above, the various processors include, in addition to the CPU which is a general-purpose processor which executes software (program) and functions as various processing units, a programmable logic device (PLD) which is a processor of which a circuit configuration can be changed after manufacture, such as a field programmable gate array (FPGA), and a dedicated electric circuit which is a processor having a circuit configuration which is designed for exclusive use in order to execute specific processing, such as an application specific integrated circuit (ASIC).

One processing unit may be composed of one of the various processors or may be composed of a combination of two or more processors of the same type or different types (for example, a combination of a plurality of FPGAs or a combination of a CPU and an FPGA). In addition, a plurality of processing units may be composed of one processor.

A first example of the configuration in which the plurality of processing units are composed of one processor is a form in which one processor is composed of a combination of one or more CPUs and software and the processor functions as the plurality of processing units, as represented by the computer, such as a client and a server. Second, as represented by a system on chip (SoC) or the like, there is a form of using a processor that realizes the function of the entire system including the plurality of processing units by one integrated circuit (IC) chip. As described above, various processing units are composed of one or more of the various processors as the hardware structure.

Further, more specifically, an electric circuit (circuitry) obtained by combining circuit elements, such as semiconductor elements, can be used as the hardware structure of the various processors.

Claim 1:
A control apparatus (<NUM>) comprising:
at least one processor that is configured to:
capture a low-energy image (<NUM>) by a radiography apparatus (<NUM>) by emitting radiation having first energy to a subject into which a contrast medium has been injected, and then sequentially acquires each of a plurality of high-energy images (<NUM>) captured by the radiography apparatus at different timings by emitting radiation having second energy higher than the first energy to the subject into which the contrast medium has been injected, the control apparatus characterised in that the processor is further configured to:
sequentially derive a body movement amount of the subject from each of the plurality of high-energy images, and
perform, in a case in which the derived body movement amount exceeds a threshold value, control of causing the radiography apparatus (<NUM>) to re-capture the low-energy image before a next high-energy image is captured.