WO2019022247A1 - 放射線画像撮影システム、ファントム、及び評価方法 - Google Patents
放射線画像撮影システム、ファントム、及び評価方法 Download PDFInfo
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Images
Classifications
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- A—HUMAN NECESSITIES
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- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
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- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
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- A61B6/481—Diagnostic techniques involving the use of contrast agents
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- A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
- A61B6/502—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of breast, i.e. mammography
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Definitions
- the present invention relates to a radiation imaging system, a phantom, and an evaluation method.
- a mammography apparatus for imaging a radiation image by irradiating radiation from a radiation source toward a breast of a subject and detecting radiation transmitted through the breast with a radiation detector.
- a mammography apparatus of this type there is a mammography apparatus capable of performing contrast radiographing on a breast in a state where a contrast agent using iodine is administered.
- a mammography apparatus capable of contrast imaging radiation of a first energy is irradiated, a first radiation image is captured by a radiation detector, radiation of a second energy different from the first energy is irradiated, and radiation is performed.
- a mammography apparatus for capturing a second radiation image by a detector When this apparatus is used, a doctor diagnoses a lesion or the like with a third radiation image in which a contrast agent is enhanced, which is generated from the first radiation image and the second radiation image.
- QC Quality Control
- a mammography apparatus is performed by a radiation image obtained by imaging a phantom for evaluation as a subject.
- a phantom for contrast imaging used for evaluating the function of contrast imaging of a mammography apparatus is known.
- a phantom including an insert of a contrast agent is disclosed in JP-A-2008-161690. Have been described.
- phantoms for contrast imaging when evaluating a mammography device, the user such as an engineer may have trouble handling, such as preparation of a phantom containing a contrast agent in a liquid state, and convenience for the user is desired to be improved. It was rare.
- the present disclosure has been made in consideration of the above circumstances, and provides a radiation imaging system, a phantom, and an evaluation method that can improve the convenience of evaluation of the function of contrast imaging by a mammography apparatus.
- a radiation of a first energy is irradiated to a subject, a first radiation image is captured by a radiation detector, and a second energy larger than the first energy is emitted.
- a mammography apparatus for photographing and a mammography apparatus having a solid containing at least one kind of element having a value of the k absorption edge not less than the first energy and not more than the second energy as a pattern for image evaluation simulating a contrast agent And a phantom for evaluation.
- a radiation of a first energy is irradiated to a subject, a first radiation image is captured by a radiation detector, and a second energy larger than the first energy is emitted.
- the thickness of the solid with respect to the incident direction of radiation in the radiation imaging system of the third aspect of the present disclosure is a thickness determined according to the concentration of the contrast agent.
- the phantom of the radiation imaging system according to the fourth aspect of the present disclosure further includes another predetermined pattern for image evaluation.
- the image evaluation pattern in the radiation imaging system includes at least one of an image evaluation pattern for evaluating a contrast to noise ratio and an image evaluation pattern for evaluating a low contrast resolution. There is.
- the image evaluation pattern in the radiation imaging system includes an image evaluation pattern simulating a mass, an image evaluation pattern simulating a microcalcification, and an image evaluation pattern simulating a fiber structure. It contains at least one.
- the first energy in the radiation imaging system of the seventh aspect of the present disclosure is 22 keV or more and less than the value of iodine k-edge, and the second energy is larger than the value of iodine k-edge , 49 keV or less.
- the solid in the radiation imaging system of the eighth aspect of the present disclosure is formed by any of vapor deposition, sputtering, fine particle coating, and machining of elements.
- a radiation imaging system generates a third radiation image in which a contrast agent is enhanced from the first radiation image and the second radiation image, and the mammography apparatus uses the phantom as a subject. And a second radiation image, the apparatus further includes a generation unit that generates a third radiation image in which solid matter is enhanced instead of the contrast agent.
- the radiographic imaging system of the 10th aspect of this indication is further provided with the evaluation part which evaluates a mammography apparatus based on the 3rd radiographic image which a production
- a phantom according to an eleventh aspect of the present disclosure has a solid including at least one element having an k absorption edge value of 22 keV or more and 49 keV or less as an image evaluation pattern simulating a contrast agent using iodine. It is a phantom for evaluation of a mammography apparatus which has.
- a phantom according to a twelfth aspect of the present disclosure is a mammography apparatus having a solid containing at least one element having an atomic number of 45 to 56 as an image evaluation pattern simulating a contrast agent using iodine. It is a phantom for evaluation.
- the evaluation method of the thirteenth aspect of the present disclosure is an evaluation method of a mammography apparatus, which uses iodine as a solid including at least one element whose k absorption edge has a value of 22 keV or more and 49 keV or less.
- An evaluation method of a fourteenth aspect of the present disclosure is an evaluation method of a mammography apparatus, which simulates a solid material containing at least one element having an atomic number of 45 to 56 as a contrast agent using iodine
- the radiation of the first energy is irradiated from the mammography device to the phantom for evaluation of the mammography device, which has as a pattern for image evaluation, and the first radiation image is taken by the radiation detector; Irradiating a radiation of a second large energy and capturing a second radiation image by the radiation detector, and generating a third radiation image in which solid matter is enhanced from the first radiation image and the second radiation image And.
- FIG. 1 the block diagram showing an example of the whole structure of the radiographic imaging system 1 of this embodiment is shown.
- the radiation imaging system 1 of the present embodiment is operated by a user such as a doctor or a radiographer based on an instruction (imaging order) input from an external system (for example, RIS: Radiology Information System) via the console 6. It has a function to take a radiation image by RIS: Radiology Information System
- the radiation imaging system 1 of the present embodiment includes a console 6, a mammography apparatus 10, and a phantom 50.
- FIG. 2 is a block diagram showing an example of the configuration of the console 6 and the mammography apparatus 10 of the present embodiment.
- the console 6 of the present embodiment has a function of controlling the mammography apparatus 10 using a photographing order, various information, and the like acquired from an external system or the like via a wireless communication LAN (Local Area Network) or the like.
- a wireless communication LAN Local Area Network
- the console 6 of this embodiment is a server computer as an example. As shown in FIG. 2, the console 6 includes a control unit 70, a storage unit 72, an I / F (Interface) unit 74, a display unit drive unit 76, a display unit 78, an operation input detection unit 80, and an operation unit 82. ing.
- the control unit 70, the storage unit 72, the I / F unit 74, the display unit drive unit 76, and the operation input detection unit 80 are connected so as to be able to exchange various information with one another via a bus 83 such as a system bus or control bus. ing.
- the control unit 70 of the present embodiment controls the overall operation of the console 6.
- the control unit 70 of the present embodiment includes a central processing unit (CPU) 70A, a read only memory (ROM) 70B, and a random access memory (RAM) 70C.
- the ROM 70B stores, in advance, various programs including an image evaluation processing program, which will be described later, which are executed by the CPU 70A.
- the RAM 70C temporarily stores various data.
- the storage unit 72 stores image data of radiation images captured by the mammography apparatus 10, various other information, and the like. Further, the storage unit 72 of the present embodiment stores an evaluation result of the mammography apparatus 10 whose details will be described later. Specific examples of the storage unit 72 include a hard disk drive (HDD) and a solid state drive (SSD).
- the I / F unit 74 communicates various information with an external system such as the mammography apparatus 10 or RIS by wireless communication or wire communication.
- the display unit 78 displays various information.
- the display drive unit 76 controls the display of various information on the display unit 78.
- the operation unit 82 is used by the user to input an instruction related to imaging of a radiation image including an irradiation instruction of the radiation R and various information.
- the operation unit 82 is not particularly limited, and examples thereof include various switches, a touch panel, a touch pen, and a mouse.
- the operation unit 82 and the display unit 78 may be integrated to form a touch panel display.
- the operation input detection unit 80 detects an operation state of the operation unit 82.
- the mammography apparatus 10 is an apparatus for taking a breast of a subject as a subject and irradiating the breast with radiation R (X-ray) to capture a radiation image of the breast.
- R X-ray
- the mammography apparatus 10 not only when the subject is standing up (standing position) but also when the subject is sitting on a chair (including a wheelchair) etc. (sitting position) It may be an apparatus for imaging a breast, and may be an apparatus capable of imaging at least a radiation image of a breast of a subject.
- the mammography apparatus 10 performs imaging in a state where a contrast agent is administered to the breast of the subject, ie, performs contrast imaging by energy subtraction imaging as a function to perform contrast imaging.
- CEDM Contrast Enhanced Digital Mammography
- the mammography apparatus 10 of this embodiment includes a radiation detector 11, a radiation irradiation unit 28 having a radiation source 29, a control unit 60, a storage unit 62, an I / F unit 64, and an operation panel 66.
- the radiation detector 11, the radiation irradiating unit 28, the control unit 60, the storage unit 62, the I / F unit 64, and the operation panel 66 can exchange various information with each other via the bus 69 such as a system bus or a control bus. It is connected to the.
- the control unit 60 of the present embodiment controls the overall operation of the mammography apparatus 10.
- the control unit 60 of the present embodiment controls the radiation detector 11 and the radiation irradiating unit 28 when taking a radiation image.
- the control unit 60 of the present embodiment includes a CPU 60A, a ROM 60B, and a RAM 60C.
- the ROM 60B stores, in advance, various programs including a photographing processing program described later which are executed by the CPU 60A.
- the RAM 60C temporarily stores various data.
- the storage unit 62 stores image data of a radiation image captured by the radiation detector 11 and other various information. Examples of the storage unit 62 include an HDD and an SSD.
- the I / F unit 64 communicates various information with the console 6 by wireless communication or wired communication.
- the operation panel 66 is provided, for example, on the photographing table 16 of the mammography apparatus 10 as a plurality of switches. Operation panel 66 may be provided as a touch panel.
- FIG. 3 the block diagram showing an example of the whole structure of the mammography apparatus 10 of this embodiment is shown.
- the side closer to the subject (the chest wall side) when the subject is facing the mammography apparatus 10 in taking a radiation image is the apparatus front side of the mammography apparatus 10 and the side away from the subject is the mammography apparatus It will be described as the rear side of the ten devices.
- the left-right direction of a subject when the subject is facing the mammography apparatus 10 is demonstrated as an apparatus left-right direction of the mammography apparatus 10.
- FIG. Further, the head direction of the subject when the subject is facing the mammography apparatus 10 will be described as the upper side and the vertical direction with the foot direction as the lower side.
- the mammography apparatus 10 includes a substantially C-shaped imaging unit 12 provided on the front side of the apparatus, and a base unit 14 that supports the imaging unit 12 from the apparatus rear side.
- the imaging unit 12 includes an imaging table 16 having a planar imaging surface 24 in contact with the subject's breast, a compression plate 20 for compressing the breast by sandwiching the imaging surface 24 of the imaging table 16, and imaging And a holding unit 18 for supporting the platform 16 and the compression plate 20.
- a member that transmits the radiation R is used for the compression plate 20.
- the imaging unit 12 further includes a support 22 that supports the radiation source 29 and a radiation irradiator 28, and the support 22 is separated from the holder 18.
- a radiation source 29 provided with a tube (tungsten as an example in the present embodiment) for irradiating the breast with radiation R in the radiation irradiating section 28 of the mammography apparatus 10 of the present embodiment.
- a Rh (rhodium) filter 42 and a Cu (copper) filter 44 are provided between the radiation source 29 and the imaging table 16 inside the radiation irradiation unit 28.
- FIG. 3 shows the Rh filter 42 and the Cu filter 44 in an integrated manner, each filter is provided as a separate filter.
- the filters provided in the mammography apparatus 10 are not limited to the Rh filter 42 and the Cu filter 44.
- a Mo (molybdenum) filter may be provided instead of or in addition to the Rh filter 42.
- the Al (aluminum) filter has the radiation source 29 continuously moved, and the imaging time at each imaging position (irradiation time of the radiation R) ) Is suitable for tomosynthesis photography that takes short pictures. Therefore, when the mammography apparatus 10 has a function of performing tomosynthesis imaging, an Al filter may be provided, and tomosynthesis imaging may be performed using the Al filter.
- a moving unit (not shown) is provided in the inside of the radiation irradiating unit 28, and when photographing a radiation image, depending on the energy of the radiation R to be irradiated, the Rh filter 42 or the Cu filter 44 is used. Move to a position in the radiation field.
- an axis (not shown) is provided in the imaging unit 12 of the present embodiment, and the imaging unit 12 can rotate with respect to the base unit 14.
- the shaft is fixed to the support 22 and the shaft and the support 22 rotate integrally.
- Gears are respectively provided on the shaft and the holding unit 18 provided in the photographing unit 12, and the holding unit 18 and the shaft are connected and integrally rotated by switching the meshing state and the non-meshing state of the gears.
- the shaft can be switched to a state where it is separated from the holding portion 18 and idles.
- shaft can use not only the said gear but various mechanical elements.
- the holding unit 18 supports the imaging table 16 and the radiation source 29 by separating the imaging surface 24 and the radiation source 29 at predetermined intervals.
- the holding unit 18 also holds the compression plate 20 via the support arm 26.
- the compression unit 20 moves as the holding unit 18 slides the support arm 26, and the compression plate 20 and the imaging surface 24 Interval changes.
- the imaging surface 24 in contact with the breast of the subject is formed of, for example, carbon in terms of radiation permeability and intensity.
- a radiation detector 11 for detecting radiation R that has passed through the breast and the imaging surface 24 is disposed inside the imaging table 16.
- a radiation image is generated based on the radiation R detected by the radiation detector 11.
- the type of radiation detector 11 of the present embodiment is not particularly limited, and may be, for example, an indirect conversion radiation detector that converts radiation R into light and converts the converted light into electric charge, or radiation It may be a direct conversion type radiation detector that converts R directly into charge.
- image data representing a radiation image output from the radiation detector 11 of the mammography apparatus 10 is transmitted to the console 6.
- the mammography apparatus 10 of the present embodiment has a function of performing contrast imaging.
- a contrast agent used for contrast imaging a contrast agent using iodine having a 33 k-absorption edge (hereinafter simply referred to as "contrast agent”) is generally used.
- the mammography apparatus 10 irradiates the radiation R of the first energy lower than the k absorption edge of the contrast agent with the breast to which the contrast agent is administered as a subject, and takes a first radiation image by the radiation detector 11, and A radiation R of a second energy higher than the k absorption edge of the contrast agent is irradiated, and a second radiation image is taken by the radiation detector 11.
- irradiating the radiation R of the first energy means applying a tube voltage of the first energy to irradiate the radiation R from the radiation source 29, similarly, Irradiating the radiation R of the second energy means applying the tube voltage of the second energy and applying the radiation R from the radiation source 29.
- Specific first energy and second energy are determined from the specifications of the mammography apparatus 10, the desired image quality of the radiation image, and the exposure of the subject in addition to the k absorption edge of the contrast agent.
- 22 keV to 49 keV is preferable.
- the first energy is preferably 22 keV or more and less than the value of the k absorption edge of the contrast agent.
- the second energy is preferably larger than the value of the k absorption edge of the contrast agent and not more than 49 keV.
- the first energy is the same as the energy of the radiation R used for normal (general) imaging.
- the radiation R of the first energy is irradiated to perform imaging (hereinafter, referred to as “first imaging”)
- the Rh filter 42 is disposed in the irradiation field. Since the k absorption edge of Rh is 23.2 keV, the radiation quality of the radiation R irradiated to the object is a radiation quality in which an energy component of 23.2 keV or more is suppressed.
- the second energy is set to any value in the range of 45 keV to 49 keV.
- the Cu filter 44 is disposed in the irradiation field when the radiation R of the second energy is irradiated to perform imaging (hereinafter, referred to as “second imaging”). Make the radiation quality of the radiation R irradiated to the subject the radiation quality of which the first energy component of the radiation R is suppressed by making the k absorption edge of Cu as low as 9.0 keV but having a suitable thickness Can.
- the first radiation image captured by the first imaging and the second radiation image captured by the second imaging are output to the console 6, and the console 6 generates image data of each of the first and second radiation images.
- the concentration distribution of the contrast agent is calculated from the difference of and the contrast agent is imaged.
- the control unit 70 of the console 6 multiplies the image data of the first radiation image by the predetermined first coefficient to obtain the image data of the second radiation image.
- a difference image in which the human body structure is suppressed and the administered contrast agent is enhanced by subtracting the image data from the image data obtained by multiplying the predetermined second coefficient for each corresponding pixel. Generate image data.
- the method of the control unit 70 generating the difference image is not limited to this, and it is possible to use a known difference image generation method.
- the difference image generated by the mammography apparatus 10 of the present embodiment is an example of the third radiation image of the present disclosure.
- the phantom 50 of the present embodiment is used to evaluate the mammography apparatus 10 by evaluating the image quality of a radiation image based on a desired image quality evaluation item.
- the phantom 50 of the present embodiment is applied to, for example, the method of the International Electrotechnical Commission (IEC) and the method of the European Reference Organization for Quality of the Breast Screening and Diagnostic Services (EUREF).
- the phantom 50 of the present embodiment is added with a function of evaluating the detection ability of the image of the contrast agent.
- FIG. 4 shows a plan view of an example of the phantom 50 according to this embodiment as viewed from the radiation source 29 side.
- the phantom 50 of the present embodiment has an image evaluation pattern 100 and an image evaluation pattern used to evaluate the detectability of an image of a contrast agent (hereinafter simply referred to as “contrast agent detectability”). It has 102.
- the image evaluation pattern 100 and the image evaluation pattern 102 the image quality evaluation item by the phantom 50 of the present embodiment includes the detectability of the contrast agent.
- the image evaluation pattern 100 is also used for evaluation of a contrast to noise ratio (CNR), which is one of the image quality evaluation items.
- CNR contrast to noise ratio
- the image evaluation pattern 102 includes a plurality of disks 103 and is also used for evaluation of low contrast resolution (LCD) which is one of the image quality evaluation items.
- the image evaluation pattern 100 and the image evaluation pattern 102 are used to evaluate the detectability of a contrast agent, and they are formed on a plastic substrate such as PET (Poly Ethylene Terephthalate) or polycarbonate (hereinafter referred to as "plastic substrate"). It is formed as a solid of predetermined size, shape and density, which simulates the contrast agent.
- plastic substrate such as PET (Poly Ethylene Terephthalate) or polycarbonate (hereinafter referred to as "plastic substrate”). It is formed as a solid of predetermined size, shape and density, which simulates the contrast agent.
- solids can be regarded as not changing in accordance with the shape of the container to be stored, and can be regarded as not changing in shape with time.
- the phantom 50 of the present embodiment contrasts a solid substance including at least one element whose k absorption edge is included in the above-described first energy to second energy of the radiation R irradiated from the radiation source 29. It has as pattern 100 for image evaluation which imitated the agent, and pattern 102 for image evaluation.
- the k absorption end is larger than the k absorption end of the Rh filter 42 used for the first imaging for emitting the radiation R of the first energy, and the radiation for the second imaging
- the image evaluation pattern 100 and the image evaluation pattern 102 are formed as a solid that simulates a contrast agent by a material containing at least one element smaller than the peak energy of R.
- Examples of this type of element include elements from Rh having an atomic number of 45 having an k absorption edge of 23.2 keV to Ba (barium) having an atomic number of 56 having an k absorption edge of 37.4 keV.
- Rh having an atomic number of 45 having an k absorption edge of 23.2 keV
- Ba barium
- 56 having an k absorption edge of 37.4 keV.
- a tin foil of Sn having an atomic number of 50 having an k absorption edge of 29.2 keV, and an atomic number of 49 having an atomic number of Sn and a k absorption edge of 27.9 keV ITO (Indium Tin Oxide) film by In (indium) is mentioned.
- the image evaluation pattern 100 and the image evaluation pattern 102 can be formed on a plastic substrate by machining.
- the image evaluation pattern 100 is formed in a rectangular shape having a thickness of 300 ⁇ m and a side of 3 cm.
- the disk 103 is formed in a circular shape having a thickness of 50 ⁇ m and a diameter of 2 mm.
- the image evaluation pattern 100 and the image evaluation pattern 102 can be formed on the plastic substrate by any method such as vapor deposition, sputtering, and fine particle coating.
- the image evaluation pattern 100 is formed in a rectangular shape with a thickness of 500 ⁇ m and a side of 3 cm.
- the disk 103 is formed in a circular shape having a thickness of 100 ⁇ m and a diameter of 2 mm.
- the ITO film as the image evaluation pattern 100 and the image evaluation pattern 102 is not required to be transparent unlike the case where it is used as a transparent electrode, so the film forming conditions are relatively loose, and heat treatment is also unnecessary. Therefore, it is easy to increase the thickness of the ITO film, and it is possible to easily form a film on a plastic substrate.
- the thickness of the image evaluation pattern 100 and the image evaluation pattern 102 specifically, the thickness with respect to the incident direction in which the radiation R is incident is determined according to the concentration of the contrast agent to be simulated, and the concentration of the contrast agent is high. The more the thickness with respect to the direction of incidence, the greater the thickness.
- the phantom 50 of the present embodiment has an image evaluation pattern for evaluating other desired image quality evaluation items.
- the phantom 50 is used for an image evaluation pattern 104 used for dynamic range evaluation, an image evaluation pattern 106 used for linearity evaluation, and spatial resolution (SR). It has a pattern 108 for image evaluation.
- the phantom 50 shown in FIG. 4 is not described in detail, but as other desired image quality evaluation items, for example, chest wall defect, system sensitivity invariance, geometric distortion, image unevenness (system artifact), and image The uniformity can also be evaluated, and each image evaluation pattern is included.
- FIG. 5 is a flowchart showing an example of the flow of the entire evaluation operation by the radiation imaging system 1 of the present embodiment.
- step S100 the user arranges the phantom 50 as an object at an arbitrary position on the imaging surface 24 of the imaging table 16 of the mammography apparatus 10. Then, the user places the compression plate 20 on the phantom 50 in the next step S102.
- next step S104 the user instructs the start of radiation image capturing from the operation unit 82 of the console 6.
- An instruction to start imaging (instruction to start imaging) is transmitted to the mammography apparatus 10 via the I / F unit 74. Further, in the radiation imaging system 1 of the present embodiment, the imaging order is also transmitted from the console 6 to the mammography apparatus 10 via the I / F unit 74.
- the mammography apparatus 10 performs the imaging process, an example of which is shown in FIG. 6, and captures a radiation image of the phantom 50.
- the mammography apparatus 10 receives the radiation image imaging start instruction and the imaging order from the console 6, the CPU 60A of the control unit 60 executes the imaging processing program stored in the ROM 60B. The photographing process shown in FIG. 6 is executed.
- step S150 the control unit 60 of the mammography apparatus 10 causes the radiation source 29 to emit the radiation R of the first energy, and in the next step S152, the control unit 60 (1) A first imaging is performed by imaging a radiographic image.
- the Rh filter 42 is disposed in the irradiation field when at least the first imaging is performed in a state where the imaging processing has been started.
- the radiation R of the first energy is irradiated to the phantom 50 by the steps S150 and S152, and the image data representing the first radiation image generated by the radiation detector 11 according to the radiation R transmitted through the phantom 50 is the mammography device 10 Output to the console 6.
- control unit 60 moves the Rh filter 42 and the Cu filter 44 to position the Cu filter 44 in the irradiation field. Further, the control unit 60 changes the tube voltage applied to the radiation source 29 from the tube voltage in the case of irradiating the first energy to the tube voltage in the case of irradiating the second energy.
- the control unit 60 irradiates the radiation R of the second energy from the radiation source 29, and in the next step S158, the control unit 60 causes the radiation detector 11 to capture a second radiation image.
- the main shooting process is ended.
- the radiation R of the second energy is irradiated to the phantom 50 by the steps S156 and S158, and the image data representing the second radiation image generated by the radiation detector 11 according to the radiation R transmitted through the phantom 50 is the mammography device 10 Output to the console 6.
- various radiation images such as the first radiation image and the second radiation image are collectively referred to, they are simply referred to as “radiation images”.
- the console 6 When image data representing a radiation image captured by the imaging process is input from the mammography apparatus 10, the console 6 temporarily stores the image data representing the input radiation image in the storage unit 72.
- step S108 the control unit 70 of the console 6 generates a difference image from the first radiation image and the second radiation image, and displays the difference image on the display unit 78. Display.
- the method of generating a difference image is the same as the generation method of generating a difference image when normal contrast radiography is performed in a case where a breast in a state in which a contrast agent is administered is used as a subject.
- the control unit 70 of the present embodiment is an example of a generation unit of the present disclosure.
- the control unit 70 acquires, from the storage unit 72, image data representing the first radiation image and image data representing the second radiation image. Then, the control unit 70 sets the image data obtained by multiplying the image data representing the first radiation image by a predetermined first coefficient into the image data representing the second radiation image in advance.
- the image data of the difference image is generated by subtracting for each corresponding pixel from the image data obtained by multiplying the coefficients of 2.
- the method of the control unit 70 generating the difference image is not limited to this, and it is possible to use a known difference image generation method.
- the control unit 70 evaluates the generated difference image.
- an evaluation value CNR for evaluating the contrast to noise ratio using the image evaluation pattern 100 can be obtained by the following equation (1).
- the average pixel value of the image for the image evaluation pattern 100 (100A) is m AL
- the standard deviation is ⁇ AL
- the average pixel value of the image for the image evaluation pattern 100 (100B) is m BG and standard deviation are taken as ⁇ BG .
- control unit 70 derives the evaluation value CNR by the above equation (1) based on the image data of the difference image.
- an LCD score for evaluating low contrast resolution using the image evaluation pattern 102 is derived from a dot pattern (LCD pattern) formed on the difference image by the disk 103.
- a white and black LCD pattern is formed by the disc 103 of the image evaluation pattern 102.
- the control unit 70 digitizes the LCD score by deriving a cross-correlation function of the difference image with the LCD pattern, using the ideal LCD pattern when no noise is generated.
- the CPU 70A executes the image evaluation processing program stored in the ROM 70B of the control unit 70 to derive the evaluation value CNR and the LCD score.
- the control unit 70A functions as an example of the evaluation unit of the present disclosure.
- evaluation of the detectability of the contrast agent by the pattern for image evaluation 100 and the pattern for image evaluation 102 in the radiation image capturing system 1 of the present embodiment is evaluated by the visual recognition result (visibility) of the user viewing the difference image.
- Information representing an evaluation based on the result of visual recognition is input by the user to the console 6 of the present embodiment.
- step S112 the control unit 70 causes the display unit 78 to display the evaluation result of the difference image in step S110. Further, the console 6 of the present embodiment stores the evaluation result in the storage unit 72. In the radiographic imaging system 1 of the present embodiment, the evaluation operation is completed by completing step S112.
- the configuration and the operation are the same except that the phantom 50 provided in the radiation imaging system 1 is different from the phantom 50 (see FIG. 4) of the first embodiment, so the detailed description will be omitted.
- the phantom 50 in the form is described.
- the phantom 50 according to the first embodiment has the function of evaluating the detectability of the image of the contrast agent.
- the phantom 50 of the present embodiment has a function of visually evaluating the detectability of the image of the contrast agent.
- FIG. 7 the top view which looked at an example of the phantom 50 of this embodiment from the radiation source 29 side is shown.
- the phantom 50 of the present embodiment has an image evaluation pattern 200, an image evaluation pattern 202, and an image evaluation pattern 204 which are used to evaluate the detectability of a contrast agent.
- the image quality evaluation items by the phantom 50 of the present embodiment include the ability to detect a contrast agent.
- the image evaluation pattern 200 is also used to evaluate the detectability of a fiber, which is one of the image quality evaluation items. Therefore, the image evaluation pattern 200 includes a plurality of test objects having different sizes simulating a fiber structure.
- the image evaluation pattern 200 in order to use for evaluation of the detectability of a contrast agent, is, for example, a solid having a shape simulating a fiber structure of a desired size by molding a resin into which barium sulfate powder is kneaded.
- the amount of barium sulfate (content of barium sulfate) to be kneaded into the resin is determined according to the concentration of the contrast agent to be simulated, and the higher the concentration of the contrast agent, the higher the content of barium sulfate.
- the image evaluation pattern 202 is also used to evaluate the detectability of microcalcification (calc) which is one of the image quality evaluation items. Therefore, the image evaluation pattern 202 includes a plurality of test objects of different sizes simulating microcalcification.
- the image evaluation pattern 202 in order to use for evaluation of the detection ability of a contrast agent, is, for example, a solid having a shape simulating microcalcification of a desired size by molding a resin into which barium sulfate powder is kneaded. It is created by molding into an object.
- the image evaluation pattern 204 is also used to evaluate the detectability of a mass, which is one of the image quality evaluation items. Therefore, the image evaluation pattern 204 includes a plurality of test objects of different sizes simulating a mass.
- the image evaluation pattern 204 is formed by sintering barium sulfate powder into a solid having a shape simulating a tumor of a desired size and sintering it for use in evaluating the detection ability of a contrast agent. Created by
- the image evaluation pattern 200, the image evaluation pattern 202, and the image evaluation pattern 204 are embedded in a wax that simulates a compressed breast.
- the flow of the entire evaluation operation of the mammography apparatus 10 using the phantom 50 of the present embodiment is the same as the flow of the entire evaluation operation (see FIG. 5) of the first embodiment. It goes without saying that the evaluation of the differential image in step S110 in the flow of the entire evaluation operation is performed according to the image evaluation pattern 200, the image evaluation pattern 202, and the image evaluation pattern 204.
- the evaluation of the detectability of the contrast agent in the case of using the phantom 50 of the present embodiment is evaluated by the visual recognition result (visibility) of the user viewing the difference image.
- the evaluation of the detection ability of the fiber structure, the mass, and the microcalcification is also evaluated by the visual recognition result (visibility) of the user viewing the difference image.
- each of the image evaluation pattern 200, the image evaluation pattern 202, and the image evaluation pattern 204 is used to evaluate the detectability of a contrast agent.
- the evaluation pattern may be in any form as long as it is used to evaluate the detectability of a contrast agent.
- the pattern 202 for image evaluation is used to evaluate the detectability of microcalcification and the detectability of a contrast agent
- the pattern 200 for image evaluation and the pattern 204 for image evaluation each have a detectability of fiber structure and a detectability of a mass. It may be used only for the evaluation of
- the radiation R of the first energy is irradiated to the subject, the first radiation image is captured by the radiation detector 11, and the first energy is generated.
- a mammography apparatus 10 is provided which takes one radiation image and a second radiation image.
- the radiation imaging system 1 includes, as an image evaluation pattern simulating a contrast agent, a solid including at least one element having an k absorption edge value equal to or greater than the first energy and equal to or less than the second energy.
- a phantom 50 for evaluation of the mammography apparatus 10 is provided.
- the radiation imaging system 1 simulates the contrast agent as a pattern for image evaluation that simulates a solid containing at least one element having an atomic number of 45 to 56
- the phantom 50 for evaluation of the mammography apparatus 10 which it has is provided.
- the phantoms 50 of the above-described embodiments each have a solid containing an element based on the k absorption edge of iodine as an image evaluation pattern simulating a contrast agent.
- the prepared liquid contrast agent is injected at a desired position in the phantom After that, a radiation image may be taken with the phantom as a subject, and the contrast agent injected after that may be discarded.
- the amount of contrast agent injected into the phantom may vary.
- the user may feel bothersome because it has a plurality of procedures that require time and effort.
- the image evaluation pattern simulating the contrast agent is a solid, and since it can be built in the phantom, the mammography apparatus 10 The convenience of the evaluation of the function of contrast imaging by
- the phantom 50 of this embodiment can add the evaluation of the function of contrast imaging to the pattern for image evaluation used for evaluating the image quality evaluation item different from the evaluation of the function of contrast imaging, it is possible to use only one phantom 50. A plurality of image quality evaluation items can be evaluated.
- the elements included in the solid which is a pattern for image evaluation simulating the contrast agent contained in the phantom 50 and the manufacturing method are not limited to the above embodiments, and may be used in various situations without departing from the scope of the present invention. Needless to say, it can be changed accordingly.
- a sheet 300 obtained by molding a resin obtained by kneading barium sulfate powder may be disposed on the phantom 302 (the radiation source 29 side).
- FIG. 8 shows a side view seen from the direction intersecting the incident direction of the radiation R.
- the thickness of the sheet 300 in the incident direction of the radiation R is a plurality of thicknesses (thicknesses L1, L2, and L3) according to the concentration of the contrast agent.
- various processors other than the CPU may execute the imaging process and the image quality evaluation process executed by the CPU executing the software (program) in each of the above embodiments.
- a processor in this case, in order to execute specific processing such as PLD (Programmable Logic Device) or ASIC (Application Specific Integrated Circuit) whose circuit configuration can be changed after manufacturing an FPGA (field-programmable gate array) or the like.
- a dedicated electric circuit or the like which is a processor having a circuit configuration specially designed is exemplified.
- imaging processing and image quality evaluation processing may be performed by one of these various processors, or a combination of two or more processors of the same or different types (for example, a plurality of FPGAs, and a CPU and an FPGA) And so on).
- the hardware-like structure of these various processors is, more specifically, an electric circuit in which circuit elements such as semiconductor elements are combined.
- various programs stored in the control unit 60 of the mammography apparatus 10 and the control unit 70 of the console 6 are stored (installed in advance) in the ROM (60B, 70B) of the control unit 60 and the control unit 70 in advance.
- the recording processing program and the image display processing program are recorded in a recording medium such as a compact disk read only memory (CD-ROM), a digital versatile disk read only memory (DVD-ROM), and a universal serial bus (USB) memory. May be provided by
- the photographing processing program and the image evaluation processing program may be downloaded from an external device via a network.
- the configurations and operations of the radiation imaging system 1, the console 6, the mammography apparatus 10, the phantom 50 and the like described in the above embodiments are merely examples, and may be changed according to the circumstances without departing from the scope of the present invention. Needless to say, it can be changed. It goes without saying that the above embodiments may be combined as appropriate.
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Abstract
Description
6 コンソール
10 マンモグラフィ装置
11 放射線検出器
12 撮影部
14 基台部
16 撮影台
18 保持部
20 圧迫板
22 支持部
24 撮影面
26 支持アーム
28 放射線照射部
29 放射線源
42 Rhフィルタ
44 Cuフィルタ
50、302 ファントム
60、70 制御部
60A、70A CPU
60B、70B ROM
60C、70C RAM
62、72 記憶部
64、74 I/F部
66 操作パネル
69、83 バス
76 表示部駆動部
78 表示部
80 操作入力検出部
82 操作部
100、100A、100B、102、104、106、108、200、202、204 画像評価用パターン
103 ディスク
300 シート
R 放射線
Claims (14)
- 第1のエネルギーの放射線を被写体に照射させて放射線検出器により第1放射線画像を撮影し、かつ前記第1のエネルギーより大きい第2のエネルギーの放射線を前記被写体に照射させて前記放射線検出器により第2放射線画像を撮影するマンモグラフィ装置であって、ヨウ素を用いた造影剤が投与された状態の***を前記被写体として前記第1放射線画像及び前記第2放射線画像を撮影するマンモグラフィ装置と、
k吸収端の値が前記第1のエネルギー以上、かつ前記第2のエネルギー以下である元素を少なくとも1種類含む固形物を、前記造影剤を模擬した画像評価用パターンとして有する前記マンモグラフィ装置の評価用のファントムと、
を備えた放射線画像撮影システム。 - 第1のエネルギーの放射線を被写体に照射させて放射線検出器により第1放射線画像を撮影し、かつ前記第1のエネルギーより大きい第2のエネルギーの放射線を前記被写体に照射させて前記放射線検出器により第2放射線画像を撮影するマンモグラフィ装置であって、ヨウ素を用いた造影剤が投与された状態の***を前記被写体として前記第1放射線画像及び前記第2放射線画像を撮影するマンモグラフィ装置と、
原子番号が45から56までの間の元素を少なくとも1種類含む固形物を、前記造影剤を模擬した画像評価用パターンとして有する前記マンモグラフィ装置の評価用のファントムと、
を備えた放射線画像撮影システム。 - 前記固形物の前記放射線の入射方向に対する厚みは、前記造影剤の濃度に応じて定められた厚みである、
請求項1または請求項2に記載の放射線画像撮影システム。 - 前記ファントムは、予め定められた他の画像評価用パターンをさらに有する、
請求項1から請求項3のいずれか1項に記載の放射線画像撮影システム。 - 前記画像評価用パターンは、コントラスト対ノイズ比を評価する画像評価用パターン、及び低コントラスト分解能を評価するための画像評価用パターンの少なくとも一方を含む、
請求項1から請求項4のいずれか1項に記載の放射線画像撮影システム。 - 前記画像評価用パターンは、腫瘤を模擬した画像評価用パターン、微小石灰化を模擬した画像評価用パターン、及び線維構造を模擬した画像評価用パターンの少なくとも1つを含む、
請求項1から請求項4のいずれか1項に記載の放射線画像撮影システム。 - 前記第1のエネルギーは、22keV以上、かつヨウ素のk吸収端の値未満であり、前記第2のエネルギーは、ヨウ素のk吸収端の値よりも大きく、49keV以下である、
請求項1から請求項6のいずれか1項記載の放射線画像撮影システム。 - 前記固形物は、前記元素を蒸着、スパッタリング、微粒子塗布、及び機械加工のいずれかにより成形されている、
請求項1から請求項7のいずれか1項に記載の放射線画像撮影システム。 - 前記第1放射線画像及び前記第2放射線画像から前記造影剤が強調された第3放射線画像を生成し、前記マンモグラフィ装置が前記ファントムを被写体とした前記第1放射線画像及び前記第2放射線画像を撮影した場合、前記造影剤に替わり前記固形物が強調された前記第3放射線画像を生成する生成部をさらに備えた、
請求項1から請求項8のいずれか1項に記載の放射線画像撮影システム。 - 前記ファントムを被写体とした場合に前記生成部が生成した前記第3放射線画像に基づいて、前記マンモグラフィ装置の評価を行う評価部をさらに備えた、
請求項9に記載の放射線画像撮影システム。 - k吸収端の値が、22keV以上、かつ49keV以下である元素を少なくとも1種類含む固形物を、ヨウ素を用いた造影剤を模擬した画像評価用パターンとして有する、
マンモグラフィ装置の評価用のファントム。 - 原子番号が45から56までの間の元素を少なくとも1種類含む固形物を、ヨウ素を用いた造影剤を模擬した画像評価用パターンとして有する、
マンモグラフィ装置の評価用のファントム。 - マンモグラフィ装置の評価方法であって、
k吸収端の値が、22keV以上、かつ49keV以下である元素を少なくとも1種類含む固形物を、ヨウ素を用いた造影剤を模擬した画像評価用パターンとして有する、マンモグラフィ装置の評価用のファントムに、前記マンモグラフィ装置から第1のエネルギーの放射線を照射させて放射線検出器により第1放射線画像を撮影する工程と、
前記ファントムに前記第1のエネルギーよりも大きい第2のエネルギーの放射線を照射させて前記放射線検出器により第2放射線画像を撮影する工程と、
前記第1放射線画像及び前記第2放射線画像から前記固形物が強調された第3放射線画像を生成する工程と、
を備えたマンモグラフィ装置の評価方法。 - マンモグラフィ装置の評価方法であって、
原子番号が45から56までの間の元素を少なくとも1種類含む固形物を、ヨウ素を用いた造影剤を模擬した画像評価用パターンとして有する、前記マンモグラフィ装置の評価用のファントムに、前記マンモグラフィ装置から第1のエネルギーの放射線を照射させて放射線検出器により第1放射線画像を撮影する工程と、
前記ファントムに前記第1のエネルギーよりも大きい第2のエネルギーの放射線を照射させて前記放射線検出器により第2放射線画像を撮影する工程と、
前記第1放射線画像及び前記第2放射線画像から前記固形物が強調された第3放射線画像を生成する工程と、
を備えたマンモグラフィ装置の評価方法。
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US11272896B2 (en) | 2022-03-15 |
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US20200155104A1 (en) | 2020-05-21 |
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