WO2022064910A1 - 情報処理装置、情報処理方法、及び情報処理プログラム - Google Patents
情報処理装置、情報処理方法、及び情報処理プログラム Download PDFInfo
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Definitions
- This disclosure relates to an information processing device, an information processing method, and an information processing program.
- Contrast imaging is performed to shoot a low-energy image and a high-energy image by radiating radiation of different energies to the subject injected with the contrast agent, and a difference image showing the difference between the high-energy image and the low-energy image is obtained.
- a technique for generating a radiographic image in which a contrast agent is emphasized by generating it.
- International Publication No. 2013/0471993 describes a technique for displaying a difference image obtained by contrast imaging as a moving image.
- the present disclosure has been made in consideration of the above circumstances, and provides an information processing apparatus, an information processing method, and an information processing program capable of observing a time change of the contrast amount with a smaller number of radiographic images. ..
- the information processing apparatus of the first aspect of the present disclosure includes at least one processor, in which the processor irradiates a subject in a state in which a contrast agent is injected with radiation of the first energy and causes a radiographic imaging apparatus to take an image.
- Each of the images is acquired and a plurality of difference images showing the difference between the low energy image and each of the plurality of high energy images are generated.
- the information processing apparatus is the information processing apparatus according to the first aspect, in which the processor continuously displays a plurality of difference images as moving images in the order of shooting time series.
- the processor displays the difference image having the highest contrast in the region of interest among the plurality of difference images. ..
- the information processing apparatus is the information processing apparatus according to any one of the first to third aspects, wherein the processor derives the contrast amount of the region of interest in each of the plurality of difference images. Then, information representing the time change of the amount of contrast in the region of interest is generated and displayed.
- the processor derives the contrast amount of the region outside the region of interest in each of the plurality of difference images, and the region outside the region of interest. Information indicating the change in the amount of contrast with time is generated and displayed.
- the processor receives and accepts the information representing the region of interest or the information representing the region outside the region of interest. Based on the information, the amount of contrast is derived.
- the processors are different from each other and the timing is less than that for taking a high energy image.
- Multiple low-energy images taken by a radiation imaging device are acquired as low-energy images, and the difference between each of the plurality of high-energy images and the low-energy image satisfying a predetermined condition among the plurality of low-energy images.
- the information processing apparatus of the eighth aspect of the present disclosure is the information processing apparatus of the seventh aspect, and the predetermined condition is that the timing of shooting is closest to the high energy image.
- the shooting interval between a plurality of low energy images is determined according to the subject.
- the ratio of the number of a plurality of low-energy images to the number of a plurality of high-energy images is set to the subject. It is determined accordingly.
- the information processing apparatus is the information processing apparatus according to any one of the first to sixth aspects, wherein the processor is a low-energy image and a high-energy image whose shooting timing is closest to each other. A first difference image showing the difference between the two is generated, a second difference image showing the difference between the high energy images is generated, and a plurality of difference images are generated by using the first difference image and the second difference image.
- the information processing apparatus is the information processing apparatus according to any one of the first to eleventh aspects, wherein the subject is a breast and the radiographic imaging apparatus is a mammography apparatus. ..
- the information processing method includes a low-energy image obtained by irradiating a subject in a state in which a contrast agent is injected with radiation of the first energy and having a radiation imaging apparatus capture the image, and a contrast agent.
- the subject in the injected state is irradiated with radiation having a second energy higher than that of the first energy, and each of a plurality of high-energy images taken by a radiation imaging apparatus at different timings is acquired.
- This is a method for a computer to execute a process of generating a plurality of difference images showing differences between a low energy image and a plurality of high energy images.
- the information processing program includes a low-energy image obtained by irradiating a subject in a state in which a contrast agent is injected with radiation of the first energy and having a radiation imaging apparatus capture the image, and a contrast agent.
- the subject in the injected state is irradiated with radiation having a second energy higher than that of the first energy, and each of a plurality of high-energy images taken by a radiation imaging apparatus at different timings is acquired.
- This is for causing a computer to perform a process of generating a plurality of difference images showing differences between a low energy image and each of the plurality of high energy images.
- FIG. 1 shows a configuration diagram showing an example of the overall configuration of the radiographic imaging system 1 of the present embodiment.
- the radiographic imaging system 1 of the present embodiment includes a mammography apparatus 10 and a console 12.
- the mammography apparatus 10 of the present embodiment is an example of the radiographic imaging apparatus of the present disclosure.
- the console 12 of the present embodiment is an example of the information processing apparatus of the present disclosure.
- FIG. 2 shows a side view showing an example of the appearance of the mammography apparatus 10 of the present embodiment. Note that FIG. 2 shows an example of the appearance when the mammography apparatus 10 is viewed from the right side of the subject.
- the mammography apparatus 10 of the present embodiment is an apparatus that takes a subject's breast as a subject, irradiates the breast with radiation R (for example, X-ray), and captures a radiographic image of the breast.
- the mammography apparatus 10 is used not only when the subject is standing up (standing position) but also when the subject is sitting on a chair (including a wheelchair) or the like (sitting state). It may be a device for imaging a breast.
- the mammography apparatus 10 of the present embodiment has a function of performing two types of imaging, so-called contrast imaging in which a contrast medium is injected into the breast of a subject, and general imaging.
- contrast imaging imaging performed with a contrast medium injected into the breast of the subject
- general imaging imaging other than contrast imaging
- the mammography apparatus 10 of the present embodiment includes a control unit 20, a storage unit 22, and an I / F (Interface) unit 24 inside the photographing table 30.
- the control unit 20 controls the overall operation of the mammography apparatus 10 according to the control of the console 12.
- the control unit 20 includes a CPU (Central Processing Unit), a ROM (ReadOnlyMemory), and a RAM (RandomAccessMemory), all of which are not shown.
- Various programs including an imaging processing program for controlling the imaging of a radiographic image, which is executed by the CPU, are stored in the ROM in advance.
- the RAM temporarily stores various data.
- the storage unit 22 stores image data of a radiation image taken by the radiation detector 28, various other information, and the like. Specific examples of the storage unit 22 include HDD (Hard Disk Drive) and SSD (Solid State Drive).
- the I / F unit 24 communicates various information with the console 12 by wireless communication or wired communication.
- the image data of the radiation image taken by the radiation detector 28 by the mammography device 10 is transmitted to the console 12 via the I / F unit 24 by wireless communication or wired communication.
- the operation unit 26 is provided as a plurality of switches on, for example, the imaging table 30 of the mammography apparatus 10.
- the operation unit 26 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 a technician with his / her foot.
- the radiation detector 28 detects the radiation R that has passed through the breast, which is the subject. As shown in FIG. 2, the radiation detector 28 is arranged inside the photographing table 30. In the mammography apparatus 10 of the present embodiment, when performing imaging, the breast of the subject is positioned by the user on the imaging surface 30A of the imaging table 30.
- the radiation detector 28 detects the radiation R transmitted through the subject's breast and the imaging table 30, generates a radiation image based on the detected radiation R, and outputs image data representing the generated radiation image.
- the type of the radiation detector 28 of the present embodiment is not particularly limited, and may be, for example, an indirect conversion type radiation detector that converts radiation R into light and converts the converted light into charge, or radiation.
- a radiation detector of a direct conversion method that directly converts R into a charge may be used.
- the radiation irradiation unit 37 includes a radiation source 37R. As shown in FIG. 2, the radiation irradiation unit 37 is provided on the arm unit 32 together with the photographing table 30 and the compression unit 36. As shown in FIG. 2, the face guard 38 is removable at a position close to the subject in the arm portion 32 below the irradiation portion 37. The face guard 38 is a protective member for protecting the subject from the radiation R emitted from the radiation source 37R.
- the mammography apparatus 10 of the present embodiment includes an arm portion 32, a base 34, and a shaft portion 35.
- the arm portion 32 is movably held in the vertical direction (Z-axis direction) by the base 34.
- the shaft portion 35 connects the arm portion 32 to the base 34. Further, the arm portion 32 is rotatable relative to the base 34 with the shaft portion 35 as the rotation axis.
- the arm portion 32, the photographing table 30, and the compression unit 36 can rotate separately with respect to the base 34 with the shaft portion 35 as the rotation axis.
- an engaging portion (not shown) is provided on each of the base 34, the arm portion 32, the photographing table 30, and the compression unit 36, and by switching the state of the engaging portion, the arm portion 32 and the imaging unit are photographed.
- Each of the base 30 and the compression unit 36 is connected to the base 34.
- One or both of the arm portion 32, the photographing table 30, and the compression unit 36 connected to the shaft portion 35 rotate integrally around the shaft portion 35.
- the compression unit 36 is provided with a compression plate drive unit (not shown) that moves the compression plate 40 in the vertical direction (Z-axis direction).
- the compression plate 40 of the present embodiment has a function of compressing the breast of the subject.
- the support portion 46 of the compression plate 40 is detachably attached to the compression plate drive portion, moves in the vertical direction (Z-axis direction) by the compression plate drive portion, and presses the subject's breast with the imaging table 30. do.
- the console 12 of the present embodiment is performed by the user by the operation unit 56 and the like, and the shooting order and various information acquired from the RIS (Radiology Information System) 2 and the like via the wireless communication LAN (Local Area Network) and the like. It has a function of controlling the mammography apparatus 10 by using instructions and the like.
- RIS Radiology Information System
- LAN Local Area Network
- the console 12 of this embodiment is, for example, a server computer. As shown in FIG. 3, the console 12 includes a control unit 50, a storage unit 52, an I / F unit 54, an operation unit 56, and a display unit 58.
- the control unit 50, the storage unit 52, the I / F unit 54, the operation unit 56, and the display unit 58 are connected to each other via a bus 59 such as a system bus or a control bus so that various information can be exchanged.
- the control unit 50 of this embodiment controls the entire operation of the console 12.
- the control unit 50 includes a CPU 50A, a ROM 50B, and a RAM 50C.
- Various programs including the irradiation control processing program 51A and the information processing program 51B, which will be described later, executed by the CPU 50A are stored in the ROM 50B in advance.
- the RAM 50C temporarily stores various data.
- the CPU 50A of the present embodiment is an example of the processor of the present disclosure.
- the information processing program 51B of the present embodiment is an example of the information processing program of the present disclosure.
- the storage unit 52 stores image data of a radiographic image taken by the mammography apparatus 10, various other information, and the like. Specific examples of the storage unit 52 include HDDs and SSDs.
- the operation unit 56 is used for the user to input instructions and various information related to taking a radiation image including an irradiation instruction of radiation R.
- the operation unit 56 is not particularly limited, and examples thereof include various switches, a touch panel, a stylus, and a mouse.
- the display unit 58 displays various information.
- the operation unit 56 and the display unit 58 may be integrated into a touch panel display.
- the I / F unit 54 communicates various information with the mammography device 10 and the RIS2 by wireless communication or wired communication.
- the console 12 of the present embodiment receives the image data of the radiographic image taken by the mammography apparatus 10 from the mammography apparatus 10 by wireless communication or wired communication via the I / F unit 54.
- FIG. 4 shows a functional block diagram of an example of the configuration of the console 12 of the present embodiment.
- the console 12 includes a control unit 60.
- the CPU 50A of the control unit 50 functions as the control unit 60 by executing the irradiation control processing program 51A stored in the ROM 50B.
- the control unit 60 has a function of controlling the irradiation of radiation R in the mammography apparatus 10 in contrast imaging.
- a radiation image is taken by irradiating the breast in which the contrast medium is injected with radiation of the first energy from the radiation source 37R. Further, the breast in which the contrast medium is injected is irradiated with radiation of a second energy higher than the first energy from the radiation source 37R, and a radiation image is taken.
- the radiation image taken by irradiating the radiation R of the first energy is referred to as a "low energy image”
- the radiation image taken by irradiating the radiation R of the second energy is "". High energy image ".
- the images taken by the mammography apparatus 10 are generically referred to without distinguishing between the types of low-energy images and high-energy images, they are simply referred to as "radiation images”.
- an iodine contrast medium having a k-absorption end of 32 keV is generally used as a contrast medium used for contrast imaging.
- a low-energy image is captured by irradiating the radiation R with a first energy lower than the k-edge of the iodine contrast medium.
- a high-energy image is taken by irradiating the radiation R with a second energy higher than the k-edge of the iodine contrast medium.
- control unit 60 of the present embodiment controls to irradiate the radiation R of the first energy from the radiation source 37R and to irradiate the radiation R of the second energy in the contrast imaging.
- control unit 60 controls the mammography apparatus 10 to capture a low-energy image and controls to capture a high-energy image.
- the contrast medium is clearly shown in the high-energy image taken as described above.
- the low-energy image hardly shows the contrast medium, and the body tissue such as the mammary gland is clearly shown. Therefore, the difference image showing the difference between the low energy image and the high energy image can be an image in which the mammary gland structure is removed and the contrast medium is clearly shown.
- contrast imaging changes in the state of penetration of the contrast medium in the breast are captured in chronological order. For example, lesions such as tumors tend to be more easily penetrated by the contrast medium than the mammary gland, and the more malignant the lesion, the faster the contrast medium penetrates and the faster the contrast medium is washed out. Therefore, in the radiographic imaging system 1 of the present embodiment, the time change of the contrast medium penetrating into the region of interest such as a lesion and the amount of permeation (contrast medium amount) can be observed by using a plurality of difference images obtained in time series. Will be.
- one of a high-energy image and a low-energy image is taken every time a predetermined time such as 1 second elapses in order to obtain a plurality of difference images.
- a predetermined time such as 1 second elapses
- the time change of the state of the mammary gland structure, particularly the time change within the imaging time of contrast imaging is very small, so that the low energy image does not need to be taken as frequently as the high energy image, for example. It may be taken only once. Since the state of the mammary gland structure may change depending on the body movement of the subject, low-energy images may be taken multiple times.
- the number of times a low-energy image is taken in one contrast-enhanced image is set to be less than the number of times a high-energy image is taken.
- the timing for capturing a low-energy image is determined according to the breast as the subject.
- the timing for taking a low-energy image is predetermined according to the thickness of the breast, the composition of the breast, and the age of the subject. Specifically, the thicker the breast, the easier it is for the mammary gland structure to move over time, even in a compressed state.
- the imaging interval between low-energy images when the breast thickness is equal to or greater than the threshold value is shorter than the imaging interval between low-energy images when the breast thickness is less than the threshold value.
- the imaging interval between low-energy images when the proportion of fat in the breast is equal to or greater than the threshold ratio is shortened as compared with the imaging interval between low-energy images when the proportion of fat is less than the threshold ratio.
- the control unit 60 of the present embodiment specifies the timing of taking a low-energy image according to at least one of the thickness of the breast, the composition of the breast, and the age of the subject. Further, the control unit 60 of the present embodiment irradiates the radiation source 37R with the radiation of the first energy or the second energy based on the imaging timing of the specified low-energy image and the predetermined time for imaging. Control to make it.
- FIG. 5 shows an example of the imaging timing of the low-energy image and the high-energy image in the contrast imaging by the mammography apparatus 10 of the present embodiment.
- a low-energy image 70L (see FIGS. 5, 70L 1 ) is first taken, and then a high-energy image 70H (FIGS. 5, 70H 1 to 1) is taken every time a predetermined time elapses. See 70H4 ).
- the shooting timing of the specified low-energy image is reached, the low-energy image 70L (see FIGS. 5 and 70L 2 ) is shot again, and then the high-energy image 70H (see FIGS. 5 and 70H 5 ) is taken every time a predetermined time elapses. ).
- the low-energy image 70L and the high-energy image 70H are repeatedly photographed until the contrast imaging time is completed.
- the console 12 of the present embodiment includes an acquisition unit 62, a generation unit 64, and a display control unit 66.
- the CPU 50A of the control unit 50 executes the information processing program 51B stored in the ROM 50B, so that the CPU 50A functions as the acquisition unit 62, the generation unit 64, and the display control unit 66. do.
- the acquisition unit 62 has a function of acquiring a low-energy image and a high-energy image taken by the mammography apparatus 10. Specifically, image data representing a low-energy image taken by the radiation detector 28 of the mammography apparatus 10 and image data representing a high-energy image are acquired via the I / F unit 24 and the I / F unit 54. .. The acquisition unit 62 outputs the acquired low-energy image and high-energy image to the generation unit 64.
- the generation unit 64 has a function of generating a plurality of difference images showing the differences between the low energy image and each of the plurality of high energy images.
- the generation unit 64 of the present embodiment generates a difference image between a low-energy image and a plurality of high-energy images taken between the time when the low-energy image is taken and the time when the next low-energy image is taken. do.
- a difference image is generated by deriving a difference between a low energy image and each high energy image.
- the generation unit 64 generates a difference image 721 between the low energy image 70L 1 and the high energy image 70H 1 .
- the generation unit 64 corresponds to the image data obtained by multiplying the low-energy image 70L 1 by a predetermined coefficient from the image data obtained by multiplying the high-energy image 70H 1 by a predetermined coefficient.
- the generation unit 64 generates a difference image 722 between the low energy image 70L 1 and the high energy image 70H 2 , and generates a difference image 723 between the low energy image 70L 1 and the high energy image 70H 3 .
- a difference image 724 between the low energy image 70L 1 and the high energy image 70H 4 is generated.
- the generation unit 64 generates a difference image 725 between the low energy image 70L 2 and the high energy image 70H 5 .
- a difference image may be generated by adding the difference between the high energy images to the difference between the low energy image and the high energy image.
- the generation unit 64 generates a difference image 721 between the low energy image 70L 1 and the high energy image 70H 1 as described above.
- the generation unit 64 generates the difference image 722 by adding the image showing the difference between the high energy image 70H 2 and the high energy image 70H 1 to the difference image 721, and generates the high energy image 70H 3 and the high energy.
- a difference image 723 is generated by adding an image showing the difference from the image 70H 2 to the difference image 722, and an image showing the difference between the high - energy image 70H 4 and the high-energy image 70H 3 is converted into the difference image 723 .
- the difference image 724 is generated by adding.
- the display control unit 66 has a function of displaying the difference images generated by the generation unit 64 on the display unit 58 as continuous moving images in chronological order.
- "moving image” means displaying still images one after another at high speed and making them recognized as moving images. Therefore, depending on the degree of "high speed” in the display, so-called “frame advance” is also included in the moving image.
- the display control unit 66 of the present embodiment derives each of the information representing the time change of the contrast amount in the region of interest in the difference image and the information representing the time change of the contrast amount outside the region of interest to the display unit 58. It has a function to display.
- the method by which the display control unit 66 identifies the region of interest from the difference image is not particularly limited.
- the region of interest may be specified from the difference image by accepting information about the region of interest input by the user.
- the display unit 58 is displayed with at least one of a difference image, a low energy image, and a high energy image, and the user operates the operation unit 56 with respect to the displayed image.
- the area may be accepted as information about the area of interest.
- the display control unit 66 may specify the region of interest by applying CAD (Computer Aided Diagnosis) to the difference image.
- CAD Computer Aided Diagnosis
- the method by which the display control unit 66 identifies the outside of the region of interest from the difference image is not particularly limited.
- a region excluding the region of interest from the region representing the breast of the difference image may be specified as outside the region of interest.
- a mammary gland region other than the region of interest may be specified as outside the region of interest.
- FIG. 7 shows a flowchart showing an example of the flow of contrast imaging by the radiation imaging system 1 of the present embodiment.
- the user injects a contrast medium into the breast as a subject.
- the user positions the subject's breast on the imaging table 30 of the mammography apparatus 10, and presses the breast with the compression plate 40.
- the mammography apparatus 10 takes a radiographic image, specifically, a low-energy image and a high-energy image.
- the control unit 60 of the console 12 controls the irradiation of the radiation R in the mammography apparatus 10.
- the console 12 of the present embodiment executes the irradiation control process shown in FIG. 8 by the CPU 50A of the control unit 50 executing the irradiation control process program 51A stored in the ROM 50B.
- FIG. 8 shows a flowchart showing an example of the flow of the irradiation control process executed in the console 12 of the present embodiment.
- the control unit 60 derives the shooting timing of the low energy image.
- the timing for taking a low-energy image is predetermined according to the thickness of the breast, the composition of the breast, and the age of the subject. Therefore, the control unit 60 acquires breast information representing at least one of breast thickness, breast composition, and subject age.
- the method by which the control unit 60 acquires breast information is not limited. For example, it may be obtained from RIS2 or the like. Further, for example, the breast information input by the user may be acquired by the operation unit 56.
- the control unit 60 may acquire breast information as an analysis result of analyzing the mammary gland mass or the like from the radiographic image taken by general radiography. ..
- the control unit 60 derives the timing for capturing the low-energy image by acquiring the information regarding the timing for capturing the low-energy image previously associated with the breast information acquired in this way.
- step S102 the control unit 60 determines whether or not the irradiation instruction of the radiation R has been received.
- the determination in step S102 is a negative determination until the irradiation instruction is received.
- the determination in step S102 becomes an affirmative determination, and the process proceeds to step S104.
- step S104 the control unit 60 outputs an instruction for irradiating the radiation R of the first energy to the mammography apparatus 10.
- the control unit 20 irradiates the breast with the radiation R of the first energy from the radiation source 37R based on the instruction input from the console 12, and the radiation detector 28 captures a low energy image.
- step S106 the control unit 60 determines whether or not the predetermined time has elapsed.
- the determination in step S106 is a negative determination until the predetermined time elapses.
- the determination in step S106 becomes an affirmative determination, and the process proceeds to step S108.
- step S108 the control unit 60 determines whether or not it is the timing to irradiate the radiation R of the first energy. Until the shooting timing of the low-energy image derived in step S100, the determination in step S108 becomes a negative determination, and the process proceeds to step S110.
- step S110 the control unit 60 outputs an instruction for irradiating the radiation R of the second energy to the mammography apparatus 10, and then proceeds to step S114.
- the control unit 20 irradiates the breast with the radiation R of the second energy from the radiation source 37R based on the instruction input from the console 12, and the radiation detector 28 captures a high energy image.
- step S108 when the shooting timing of the low energy image is reached in step S108, a positive determination is made and the process proceeds to step S112.
- step S112 the control unit 60 outputs an instruction for irradiating the radiation R of the first energy to the mammography apparatus 10 in the same manner as in step S104, and then proceeds to step S114.
- the mammography apparatus 10 captures a low energy image.
- step S114 the control unit 60 determines whether or not to end the main irradiation control process. Until the predetermined end condition is satisfied, the determination in step S114 becomes a negative determination, the process returns to step S106, and the processes of steps S106 to S112 are repeated. On the other hand, when the end condition is satisfied, the determination in step S114 becomes an affirmative determination, and the main irradiation control process is terminated.
- the termination conditions are not limited.
- the end conditions include, for example, when the elapsed time from injecting the contrast medium into the breast has elapsed a predetermined time, when the elapsed time from the start of irradiation of radiation R has elapsed, and when the predetermined time has elapsed, the radiographic image. It may be a condition that the shooting is terminated when the number of shootings reaches a predetermined number of times or when an instruction to end the shooting is received from the user.
- control unit 60 may end the main irradiation control process when the result of analyzing the captured radiographic image satisfies the end condition.
- the termination condition in this case is, for example, the case where the contrast amount does not change. Specifically, it may be a condition that the process ends when the difference between the high-energy images is equal to or less than the threshold value, and when the difference between the pixel values in the region of interest in the high-energy image is equal to or less than the threshold value.
- step S16 the difference image generation display process shown in FIG. 9 is performed by the console 12.
- the console 12 of the present embodiment executes the difference image generation display process shown in FIG. 9 by the CPU 50A of the control unit 50 executing the information processing program 51B stored in the ROM 50B.
- FIG. 9 shows a flowchart showing an example of the flow of the difference image generation display processing executed in the console 12 of the present embodiment.
- step S200 the acquisition unit 62 acquires a low-energy image and a high-energy image taken by contrast imaging from the mammography apparatus 10 as described above.
- the timing at which the acquisition unit 62 acquires the low-energy image and the high-energy image is not limited. For example, each time a low-energy image and a high-energy image are taken, a low-energy image and a high-energy image may be acquired from the mammography apparatus 10. Further, for example, after all the low-energy images and high-energy images have been taken, the low-energy images and high-energy images stored in the storage unit 22 of the mammography apparatus 10 may be acquired. Further, the order of acquiring low-energy images and high-energy images is not limited.
- the generation unit 64 generates a plurality of difference images from the low-energy image and the high-energy image acquired in the above step S200, as described above.
- the display control unit 66 identifies the region of interest from the difference image as described above.
- the display control unit 66 derives information representing the time change of the contrast amount, as described above. Specifically, the display control unit 66 derives information representing the time change of the contrast amount of the region of interest specified in step S204 in the difference image generated in step S202. Further, the display control unit 66 derives information representing a time change of the contrast amount outside the region of interest specified in step S204 in the difference image generated in step S202.
- the display control unit 66 does not have to derive the contrast amount itself. For example, the luminance value of a pixel in a difference image changes according to the amount of contrast. Therefore, the information representing the time change of the brightness value of the difference image may be used as the information representing the time change of the contrast amount.
- FIG. 10 shows an example of information 80 representing a change in the amount of contrast with time.
- the horizontal axis represents the passage of time since the contrast medium was injected.
- the vertical axis represents the amount of contrast.
- the contrast amount in this case does not have to be the contrast amount itself, but may be the brightness value of the pixel.
- an example of the time change of the contrast amount when the region of interest is a tumor, so-called breast cancer is shown by a solid line.
- an example of the time change of the mammary gland region as outside the region of interest is shown by a dotted line. As shown in FIG.
- the contrast medium in the case of a tumor, the contrast medium penetrates rapidly and the contrast medium is washed out quickly. Therefore, by observing the time change of the contrast amount in the region of interest, it can be used as an index for diagnosing whether the region of interest is a tumor or malignant.
- the contrast medium is dyed, it is necessary to compare the time change of the contrast amount in the area outside the area of interest, for example, the area of the breast gland presumed to be normal, with the time change of the contrast amount in the area of interest. This makes it possible to clarify the rate at which the contrast medium penetrates and the rate at which the contrast medium is washed out.
- the display control unit 66 controls the display unit 58 to display the plurality of difference images generated in the step S202 and the information 80 representing the time change of the contrast amount derived in the step S206.
- the difference image generation display process is terminated.
- the display control unit 66 performs predetermined image processing such as gradation enhancement processing and frequency enhancement processing on the plurality of difference images generated in step S202 to assist the user in interpreting the images. Control is performed to display a plurality of processed difference images on the display unit 58.
- FIG. 11 shows an example of a state in which the moving image 82 and the information 80 representing the time change of the contrast amount are displayed on the display unit 58.
- the display control unit 66 of the present embodiment causes the display unit 58 to continuously display a plurality of difference images as moving images 82 in the order of shooting time series.
- the position information 83 indicating the position of the region of interest is also displayed on the difference image as the moving image 82.
- the timing of displaying the next difference image may be changed according to the contrast value of the region of interest. For example, when the contrast value of the region of interest is equal to or greater than the threshold value, the timing of displaying the next difference image may be delayed, that is, the display speed of the moving image may be slower than when the contrast value is less than the threshold value. Further, the display speed of the moving image 82 may be adjustable by the user.
- the difference image displayed by the display control unit 66 is not limited to the form of the moving image 82.
- the difference image having the highest contrast in the region of interest may be displayed.
- the difference image having the highest contrast in the region designated by the user on the radiation image 84 or the low energy image may be displayed.
- the display control unit 66 of the present embodiment has taken a radiographic image 84 taken by general radiography, in other words, a state in which a contrast medium has not been injected, with respect to the breast as a subject.
- the radiation image 84 is also displayed on the display unit 58 as a comparative example.
- the moving image 82 and the radiation image 84 are displayed side by side, but either the moving image 82 or the radiation image 84 is displayed and displayed according to the user's instruction. It may be a form of switching images.
- the radiation image displayed on the display unit 58 by the display control unit 66 is not limited to the above-mentioned image.
- at least one of a low energy image and a high energy image may be displayed.
- the images and information displayed on the display unit 58 by the display control unit 66 are not limited to those described above.
- a numerical value indicating the amount of contrast in the region of interest may be displayed. In this case, it may be the contrast amount of the entire region of interest, or it may be any of the average value, the median value, the maximum value, and the like of the contrast amount of the region of interest.
- the difference image generation display process in step S16 shown in FIG. 7 is completed.
- the low-energy image and the plurality of high-energy images taken by the mammography apparatus 10 of the present embodiment, the plurality of difference images generated by the console 12, the moving image 82, and the information 80 indicating the time change of the contrast amount are included in the information 80 and the like. It may be stored in the storage unit 52 of the console 12, PACS (Picture Archiving and Communication Systems), or the like.
- the timing of performing the difference image generation display processing that is, the difference image is displayed.
- the timing of generating and displaying the difference image is not limited to this embodiment.
- the timing of each of the generation of the difference image and the display of the difference image may be performed at a timing according to the user's desire after the contrast imaging.
- the console 12 of each of the above forms includes a CPU 50A as at least one processor.
- the CPU 50A has a low-energy image taken by the mammography apparatus 10 by irradiating the breast in which the contrast agent has been injected with radiation R of the first energy, and the first energy in the breast in which the contrast agent has been injected.
- a radiation R having a second energy higher than that is irradiated, and each of a plurality of high-energy images taken by the mammography apparatus 10 at different timings is acquired.
- the CPU 50A generates a plurality of difference images showing the differences between the low energy image and each of the plurality of high energy images.
- the console 12 of the present embodiment since one low-energy image is applied to a plurality of high-energy images to generate a difference image, the amount of contrast changes over time with a smaller number of radiographic images. Can be observed. Further, the high-energy radiation R easily penetrates fat, and the exposure dose of the subject is reduced as compared with the low-energy radiation R. Therefore, according to the present embodiment, the number of times the low-energy image is taken can be made smaller than the number of times the high-energy image is taken, so that the exposure dose of the subject can be reduced.
- the generation unit 64 generates a difference image between the low energy image and the high energy image taken before the next low energy image is taken.
- the combination of the low-energy image and the high-energy image for generating the difference image is not limited to this form.
- a form may be used in which a difference image from a low-energy image whose shooting timing is closest to the high-energy image is generated.
- the generation unit 64 generates a difference image 72 1 between the high energy image 70H 1 and the low energy image 70L 1 , and generates the high energy image 70H 2 and the low energy image 70L 1 . Generates a difference image 722 with.
- the generation unit 64 generates a difference image 723 between the high energy image 70H 3 and the low energy image 70L 2 , and generates a difference image 742 between the high energy image 70H 4 and the low energy image 70L 2 .
- a difference image 725 between the energy image 70H 5 and the low energy image 70L 2 is generated. In this way, the influence of body movement can be further reduced by generating the difference image by combining the high-energy image with the low-energy image whose shooting timing is closest to the high-energy image.
- the present invention is not limited to this form, and a high-energy image may be taken first.
- the breast is applied as an example of the subject of the present disclosure
- the mammography apparatus 10 is applied as an example of the radiographic imaging apparatus of the present disclosure.
- the subject is not limited to the breast, and the subject is not limited to the breast.
- the radiographic imaging device is not limited to the mammography device.
- the subject may be the chest, the abdomen, or the like, and the radiographic imaging apparatus may be in the form of applying a radiographic imaging apparatus other than the mammography apparatus.
- the console 12 is an example of the information processing apparatus of the present disclosure, but an apparatus other than the console 12 may have the function of the information processing apparatus of the present disclosure.
- a part or all of the functions of the control unit 60, the acquisition unit 62, the generation unit 64, and the display control unit 66 may be provided by, for example, a mammography device 10 or an external device other than the console 12.
- the hardware structure of the processing unit that executes various processes such as the control unit 60, the acquisition unit 62, the generation unit 64, and the display control unit 66 is shown below.
- the various processors include a CPU, which is a general-purpose processor that executes software (program) and functions as various processing units, and a circuit after manufacturing an FPGA (Field Programmable Gate Array) or the like.
- Dedicated electricity which is a processor with a circuit configuration specially designed to execute specific processing such as programmable logic device (PLD), ASIC (Application Specific Integrated Circuit), which is a processor whose configuration can be changed. Circuits etc. are included.
- One processing unit may be composed of one of these various processors, or 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). It may be composed of a combination). Further, a plurality of processing units may be configured by one processor.
- one processor is configured by a combination of one or more CPUs and software, as represented by a computer such as a client and a server.
- the processor functions as a plurality of processing units.
- SoC System On Chip
- the various processing units are configured by using one or more of the above-mentioned various processors as a hardware-like structure.
- an electric circuit in which circuit elements such as semiconductor elements are combined can be used.
- each of the irradiation control processing program 51A and the information processing program 51B is used as a recording medium such as a CD-ROM (Compact Disc Read Only Memory), a DVD-ROM (Digital Versatile Disc Read Only Memory), and a USB (Universal Serial Bus) memory. It may be provided in recorded form. Further, each of the irradiation control processing program 51A and the information processing program 51B may be downloaded from an external device via a network.
- a recording medium such as a CD-ROM (Compact Disc Read Only Memory), a DVD-ROM (Digital Versatile Disc Read Only Memory), and a USB (Universal Serial Bus) memory. It may be provided in recorded form.
- each of the irradiation control processing program 51A and the information processing program 51B may be downloaded from an external device via a network.
- Radiation imaging system 2 RIS 10 Mammography device 12 Console 20, 50 Control unit 22, 52 Storage unit 24, 54 I / F unit 26, 56 Operation unit 28 Radiation detector 30 Imaging table, 30A Imaging surface 32 Arm section 34 Base 35 Shaft section 36 Compression unit 37 Radiation irradiation part, 37R Radiation source 38 Face guard 40 Compression plate 46 Support part 50A CPU, 50B ROM, 50C RAM 51A Radiation control processing program, 51B Information processing program 58 Display unit 59 Bus 60 Control unit 62 Acquisition unit 64 Generation unit 66 Display control unit 70L 1 , 70L 2 Low energy image 70H 1 to 70H 5 High energy image 72 1 to 72 5 Difference Image 80 Information showing the time change of the amount of contrast 82 Movie 83 Position information 84 Radiation image R Radiation
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Abstract
Description
図7には、本実施形の放射線画像撮影システム1による造影撮影の流れの一例を表したフローチャートが示されている。造影撮影を行う場合、まず、図7のステップS10に示すようにユーザは、被写体となる乳房に造影剤を注入する。次にステップS12に示すようにユーザは、マンモグラフィ装置10の撮影台30に被検者の乳房をポジショニングし、圧迫板40により乳房を圧迫する。
2020年9月28日出願の日本国特許出願2020-162694号の開示は、その全体が参照により本明細書に取り込まれる。
本明細書に記載された全ての文献、特許出願、及び技術規格は、個々の文献、特許出願、及び技術規格が参照により取り込まれることが具体的かつ個々に記された場合と同程度に、本明細書中に参照により取り込まれる。
2 RIS
10 マンモグラフィ装置
12 コンソール
20、50 制御部
22、52 記憶部
24、54 I/F部
26、56 操作部
28 放射線検出器
30 撮影台、30A 撮影面
32 アーム部
34 基台
35 軸部
36 圧迫ユニット
37 放射線照射部、37R 放射線源
38 フェイスガード
40 圧迫板
46 支持部
50A CPU、50B ROM、50C RAM
51A 照射制御処理プログラム、51B 情報処理プログラム
58 表示部
59 バス
60 制御部
62 取得部
64 生成部
66 表示制御部
70L1、70L2 低エネルギー画像
70H1~70H5 高エネルギー画像
721~725 差分画像
80 造影量の時間変化を表す情報
82 動画
83 位置情報
84 放射線画像
R 放射線
Claims (14)
- 少なくとも1つのプロセッサを備え、
前記プロセッサは、
造影剤が注入された状態の被写体に第1のエネルギーの放射線を照射させて放射線画像撮影装置に撮影させた低エネルギー画像と、前記造影剤が注入された状態の被写体に第1のエネルギーよりも高い第2のエネルギーの放射線を照射させて、互いに異なるタイミングで前記放射線画像撮影装置に撮影させた複数の高エネルギー画像の各々とを取得し、
前記低エネルギー画像と前記複数の高エネルギー画像の各々との差分を示す複数の差分画像を生成する
情報処理装置。 - 前記プロセッサは、
前記複数の差分画像を撮影の時系列順に連続して動画として表示させる
請求項1に記載の情報処理装置。 - 前記プロセッサは、
前記複数の差分画像のうち、関心領域のコントラストが最も高い差分画像を表示させる
請求項1または請求項2に記載の情報処理装置。 - 前記プロセッサは、
前記複数の差分画像の各々における関心領域の造影量を導出し、
前記関心領域における造影量の時間変化を表す情報を生成して表示させる
請求項1から請求項3のいずれか1項に記載の情報処理装置。 - 前記プロセッサは、
前記複数の差分画像の各々における前記関心領域外の領域の造影量を導出し、
前記関心領域外の領域の造影量の時間変化を表す情報を生成して表示させる
請求項4に記載の情報処理装置。 - 前記プロセッサは、
前記関心領域を表す情報または前記関心領域外の領域を表す情報を受け付け、
受け付けた前記情報に基づいて、前記造影量を導出する
請求項4または請求項5に記載の情報処理装置。 - 前記プロセッサは、
互いに異なり、かつ高エネルギー画像の撮影よりも少ないタイミングで前記放射線画像撮影装置に撮影させた複数の低エネルギー画像を前記低エネルギー画像として取得し、
前記複数の高エネルギー画像の各々と、前記複数の低エネルギー画像のうち予め定められた条件を満たす低エネルギー画像との差分を示す差分画像を生成する
請求項1から請求項6のいずれか1項に記載の情報処理装置。 - 前記予め定められた条件は、高エネルギー画像に撮影のタイミングが最も近いとの条件である
請求項7に記載の情報処理装置。 - 前記複数の低エネルギー画像同士の撮影間隔は
前記被写体に応じて定められる
請求項7または請求項8に記載の情報処理装置。 - 前記複数の低エネルギー画像の数と、前記複数の高エネルギー画像の数の比率は、
前記被写体に応じて定められる
請求項7または請求項8に記載の情報処理装置。 - 前記プロセッサは、
前記低エネルギー画像と撮影のタイミングが最も近い高エネルギー画像との差分を示す第1差分画像を生成し、
高エネルギー画像同士の差分を示す第2差分画像を生成し、
前記第1差分画像と前記第2差分画像とを用いて前記複数の差分画像を生成する
請求項1から請求項6のいずれか1項に記載の情報処理装置。 - 前記被写体は、乳房であり、
前記放射線画像撮影装置は、マンモグラフィ装置である
請求項1から請求項11のいずれか1項に記載の情報処理装置。 - 造影剤が注入された状態の被写体に第1のエネルギーの放射線を照射させて放射線画像撮影装置に撮影させた低エネルギー画像と、前記造影剤が注入された状態の被写体に第1のエネルギーよりも高い第2のエネルギーの放射線を照射させて、互いに異なるタイミングで前記放射線画像撮影装置に撮影させた複数の高エネルギー画像の各々とを取得し、
前記低エネルギー画像と前記複数の高エネルギー画像の各々との差分を示す複数の差分画像を生成する
処理をコンピュータが実行する情報処理方法。 - 造影剤が注入された状態の被写体に第1のエネルギーの放射線を照射させて放射線画像撮影装置に撮影させた低エネルギー画像と、前記造影剤が注入された状態の被写体に第1のエネルギーよりも高い第2のエネルギーの放射線を照射させて、互いに異なるタイミングで前記放射線画像撮影装置に撮影させた複数の高エネルギー画像の各々とを取得し、
前記低エネルギー画像と前記複数の高エネルギー画像の各々との差分を示す複数の差分画像を生成する
処理をコンピュータに実行させるための情報処理プログラム。
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US20060025680A1 (en) * | 2004-07-29 | 2006-02-02 | Fanny Jeune-Iomme | Method and apparatus for contrast enhanced medical imaging |
JP2012501750A (ja) * | 2008-09-04 | 2012-01-26 | ホロジック,インコーポレイテッド | 統合型マルチモード・マンモグラフィ/トモシンセシスx線システム及び方法 |
US20120134464A1 (en) * | 2010-10-04 | 2012-05-31 | Mathias Hoernig | Method to show a concentration of a contrast agent in a predetermined volume segment by means of tomosynthesis, and corresponding tomosynthesis apparatus |
WO2013047193A1 (ja) | 2011-09-28 | 2013-04-04 | 富士フイルム株式会社 | 放射線画像撮影システム |
JP2016533803A (ja) * | 2013-10-24 | 2016-11-04 | アンドリュー ピー. スミス, | X線誘導胸部生検をナビゲートするためのシステムおよび方法 |
JP2020162694A (ja) | 2019-03-28 | 2020-10-08 | 日本電産サンキョー株式会社 | 開閉部材駆動装置 |
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JP2012501750A (ja) * | 2008-09-04 | 2012-01-26 | ホロジック,インコーポレイテッド | 統合型マルチモード・マンモグラフィ/トモシンセシスx線システム及び方法 |
US20120134464A1 (en) * | 2010-10-04 | 2012-05-31 | Mathias Hoernig | Method to show a concentration of a contrast agent in a predetermined volume segment by means of tomosynthesis, and corresponding tomosynthesis apparatus |
WO2013047193A1 (ja) | 2011-09-28 | 2013-04-04 | 富士フイルム株式会社 | 放射線画像撮影システム |
JP2016533803A (ja) * | 2013-10-24 | 2016-11-04 | アンドリュー ピー. スミス, | X線誘導胸部生検をナビゲートするためのシステムおよび方法 |
JP2020162694A (ja) | 2019-03-28 | 2020-10-08 | 日本電産サンキョー株式会社 | 開閉部材駆動装置 |
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