WO2008038491A1 - Dispositif de radiographie - Google Patents

Dispositif de radiographie Download PDF

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Publication number
WO2008038491A1
WO2008038491A1 PCT/JP2007/066880 JP2007066880W WO2008038491A1 WO 2008038491 A1 WO2008038491 A1 WO 2008038491A1 JP 2007066880 W JP2007066880 W JP 2007066880W WO 2008038491 A1 WO2008038491 A1 WO 2008038491A1
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WO
WIPO (PCT)
Prior art keywords
radiation
subject
radiation source
distance
magnification
Prior art date
Application number
PCT/JP2007/066880
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English (en)
Japanese (ja)
Inventor
Shintarou Muraoka
Original Assignee
Konica Minolta Medical & Graphic, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Konica Minolta Medical & Graphic, Inc. filed Critical Konica Minolta Medical & Graphic, Inc.
Publication of WO2008038491A1 publication Critical patent/WO2008038491A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/484—Diagnostic techniques involving phase contrast X-ray imaging

Definitions

  • the present invention relates to a radiographic image capturing apparatus, and more particularly, to a radiographic image capturing apparatus capable of capturing a phase contrast image.
  • a radiographic imaging apparatus that uses an action of radiation passing through a substance is widely used for medical diagnostic imaging, non-destructive inspection, and the like.
  • a method has been used in which a subject is fixed on a subject table integrated with a radiographic image detector.
  • this method does not increase the contrast of the image enough to capture the actual size of the subject, and medical imaging is used to interpret the fine structure of a specific part such as a diseased part of the breast. There was a problem that the image was not clear enough for the device.
  • a radiographic image capturing apparatus that captures a phase contrast image has been proposed.
  • a phase contrast image is also called a refraction contrast image.
  • Previously it was obtained by imaging with monochromatic parallel radiation obtained from a radiation source such as SPring-8, or with a microfocus radiation source having a focal spot size of about 10 m). Although it has been said that it can be obtained, it has been found that it can also be obtained with a radiation source (small focal radiation source with a focal size of 30 to 300 (11 m)) used in general medical facilities.
  • Patent Document 1 discloses a technique for obtaining an edge enhancement effect without using synchrotron radiation that requires a large device or an X-ray light source having a small X-ray focal point size until it can be regarded as a point light source.
  • the distance R1 from the X-ray tube as a radiation source to the subject is Rl ⁇ (D-7) / 200 (m). It is shown that an edge-enhanced image can be obtained when the distance R2 between the subject and the X-ray detector is 0.15 (m) or more.
  • the magnification ratio (R1 + R2) / R1.
  • the enlargement ratio is the ratio of the size of the subject in the radiographic image to the actual size of the subject, and is synonymous with the imaging magnification.
  • the enlargement ratio that is, imaging magnification
  • the above-described R1 is fixed. This is done by changing R2.
  • Patent Document 1 JP 2001-91479 A
  • Patent Document 2 Japanese Patent Laid-Open No. 2004-173879
  • FIG. 9 shows a detector holding unit 12 that holds a radiation source 6, a subject H, and a radiation image detector (X-ray detector) when a breast is imaged by phase contrast imaging in a conventional radiographic imaging device.
  • the numbers in the figure indicate the magnification), and schematically shows the positional relationship between the floor and ceiling in the imaging room where phase contrast imaging is performed.
  • the distance R1 between the radiation source 6 and the subject H is fixed, so that the radiation source 6 is positioned vertically upward by the distance R1 of the subject H (Fig. 9 ( a)). That is, the top position of the radiation source 6 is increased according to the subject position (when the subject H is a breast, the height from the floor surface to the subject H).
  • R1 + R2 that is, the distance between the radiation source 6 and the detector holding unit 12 is constant, and according to the enlargement ratio.
  • the applicant of the present application has applied for a radiographic imaging device that adjusts the relative distance between the radiation source 6 and the detector holder 12 with respect to the subject H.
  • An object of the present invention is to prevent the image quality from changing depending on the imaging magnification in the radiographic image capturing apparatus.
  • the object of the present invention can be achieved by the following configurations.
  • Detector holding means for holding a radiation image detector for detecting radiation from the radiation source transmitted through the subject;
  • An object table disposed between the radiation source and the detector holding means and holding the subject
  • Magnification setting means for setting the shooting magnification
  • a radiographic imaging apparatus comprising: a control means for detecting an irradiation amount from the radiation source and controlling the radiation source!
  • the control means variably controls the radiation dose emitted from the radiation source in accordance with the imaging magnification set by the magnification setting means.
  • the focal size D of the radiation source is 30 (m) or more
  • the distance R1 from the radiation source to the subject is Rl ⁇ (D-7) / 200 (m),
  • the radiation that can prevent the image quality from changing according to the imaging magnification by variably controlling the radiation dose emitted from the radiation source according to the imaging magnification set by the magnification setting means.
  • An image capturing device can be provided.
  • FIG. 1 is a diagram showing a configuration example of a breast image photographing apparatus 1 according to the present invention.
  • FIG. 2 is a diagram schematically showing the internal configuration of the imaging device main body 2 of the breast image capturing device 1
  • FIG. 3 is a block diagram showing a functional configuration of breast image capturing apparatus 1.
  • FIG. 4 is a diagram for explaining the principle of phase contrast imaging.
  • FIG. 6 The results of visibility evaluation of each captured image when the distance L (R1 + R2) between the radiation source 6 and the detector holding unit 12 and the magnification rate are changed in the mammography apparatus 1 are shown.
  • (B) shows that Rl + R2 1140, and R when radiographing was performed at each magnification with the same radiation dose as the radiation irradiation stop condition.
  • FIG. 8 is a flowchart showing an irradiation dose control process executed by the control device 16.
  • FIG. 6 is a diagram schematically showing the positional relationship between the radiation source 6, the subject H, the detector holding unit 12, the floor surface, and the ceiling.
  • FIGS. 1 and 2 show a configuration example of the mammography apparatus 1.
  • FIG. 1 is a diagram illustrating an example of an external configuration of the breast imaging apparatus 1
  • FIG. 2 is a diagram schematically illustrating an internal configuration of the imaging apparatus main unit 2 of the breast imaging apparatus 1 illustrated in FIG. .
  • the radiation dose detection unit 13, the operation device 14, the power supply unit 15, the drive device 17 and the drive device 19 are connected to the control device 16 (shown in FIG. 3) of the main body 9! Power Not shown here! /
  • FIG. 3 the control device 16
  • a support base 3 is provided on a main body 9 so as to be movable up and down, and a support shaft 4 provided on the support base 3 is provided on the support base 3.
  • the imaging device main body 2 is supported via the.
  • the support base 3 is moved up and down by being driven by a drive device 17 constituted by a motor or the like.
  • the imaging device main body 2 can be raised and lowered by raising and lowering the support base 3 by the drive device 17, and can be rotated by the drive device 17 about the support shaft 4.
  • a radiation source 6 for radiating radiation is provided on the upper part of the imaging apparatus main body 2.
  • the radiation source 6 is connected to the main body 9 via the support shaft 4 and the support base 3. Is connected to the power supply 15
  • the radiation source 6 is applied with a tube voltage and a tube current by the power supply unit 15.
  • an aperture locus of an aperture device 7 as an irradiation field adjustment device for adjusting the radiation field is provided so as to be freely opened and closed.
  • the radiation source 6 is preferably a rotating anode X-ray tube.
  • X-rays are generated when an electron beam emitted from the cathode collides with the anode.
  • This is incoherent (incoherent) like natural light and is not divergent X-ray but divergent light. If the electron beam continues to hit the place where the anode is fixed, the anode will be damaged by the generation of heat. Therefore, in a normal X-ray tube, the anode is rotated to prevent a decrease in the life of the anode.
  • the electron beam is made to collide with a certain size plane of the anode, and the generated X-rays are emitted toward the subject H from the plane of the certain size anode.
  • This plane is called a focus.
  • the focus size D m) is the length of one side when the focus is square, the length of the short side when the focus is rectangular or polygonal, and the diameter when the focus is circular.
  • a detector holding a force set containing a stimulable phosphor sheet for example, as a radiation image detector (radiation detector) for detecting radiation transmitted through the subject H
  • the part 12 is attached to a position below the subject table 10 and extending substantially perpendicularly from the radiation source 6 so as to face the radiation source 6.
  • the uppermost surface of the radiation image detector held by the detector holding unit 12 coincides with the uppermost surface of the detector holding unit 12.
  • the radiation source 6 and the detector holding unit 12 are attached to the holding member 8, and the holding member 8 allows the distance L between the radiation source 6 and the detector holding unit 12 (R1 to be described later) + R2) is maintained at a certain distance.
  • the holding member 8 can be moved up and down by driving a driving device 19 composed of a motor or the like.
  • the raising and lowering of the holding member 8 by the driving device 19 keeps the radiation source 6 and the detector holding unit 12 at a certain distance. While going up and down.
  • the distance L between the radiation source 6 and the detector holding unit 12 is preferably set to L ⁇ 0.95 (m) from the viewpoint of visibility when outputting a photographed image as a result of intensive research! (See Figure 6).
  • a radiation image detector for example, a screen (intensifying screen) / film, an FPD (flat panel detector), or the like may be used in addition to the above-described force set containing the photostimulable phosphor sheet. Good.
  • the subject table 10 holding the subject H also with a lower force and A compression plate 11 is provided for pressing and fixing the subject H from above.
  • the subject table 10 is attached to the holder 5 of the photographing apparatus main body 2 and moves up and down in accordance with the raising and lowering of the photographing apparatus main body 2 by the driving device 17.
  • the compression plate 11 is configured to be movable up and down along a support shaft (not shown) provided in the photographing apparatus main body 2.
  • the position of the compression plate 11 is detected by a position detection unit 18 (shown in FIG. 3) and output to the control device 16 of the main body unit 9.
  • a position detection unit 18 shown in FIG. 3
  • the position detector 18 a method using photometry using infrared rays, a method in which a line resistance is provided on the rail of the support shaft that slides the compression plate 11, and a position is determined from the measured resistance value can be adopted.
  • a radiation dose detection unit 13 for detecting the radiation dose irradiated is provided on the surface of the detector holding unit 12 opposite to the surface facing the subject table 10.
  • the radiation dose detection unit 13 is, for example, a sensor composed of a semiconductor or the like.
  • the radiation dose detected by the radiation dose detection unit 13 is output to the control device 16 of the main body unit 9.
  • the main body 9 includes a control device 16 including a CPU (Central Processing Unit), a ROM (Read Only Memory), and a RAM (Random Access Memory).
  • FIG. 3 shows an example of the functional configuration of the breast image capturing apparatus 1.
  • the control device 16 includes a radiation dose detection unit 13 for detecting the irradiated radiation dose, a keyboard touch panel for setting imaging conditions such as an enlargement ratio (imaging magnification) and an imaging direction,
  • An input device 14a having a position adjustment switch (upward adjustment switch for adjusting upward, downward adjustment switch for adjusting downward) for adjusting the position of the subject table 10, and a display device 14b such as a CRT display or a liquid crystal display are provided.
  • a position detection unit 18 for detection and a drive device 19 for raising and lowering the holding member 8 are connected via a bus 20.
  • the ROM of the control device 16 stores a control program for controlling each part of the mammography apparatus 1, and the CPU controls the operation of each part of the mammography apparatus 1 in cooperation with this control program. To control phase contrast.
  • phase contrast imaging a certain distance R2 is provided between the subject H and the radiation image detector 12a, and as shown in FIG. Emphasis) to obtain an image.
  • the radiation from the radiation source 6 is refracted when passing through the subject H, and the radiation density Dr inside the boundary of the subject H becomes sparse, and the outside of the subject H passes through the object.
  • Radiation density Dr increases due to overlapping with radiation that does not.
  • the edge that is the boundary of the subject H is enhanced as an image. This is a phenomenon that arises from the difference in refractive index between subject H and air. This is an edge-enhanced image.
  • the boundary portion of the subject H is expressed as a boundary portion with a substance having a different refractive index with respect to radiation.
  • the starting point is the position of the focal point of the radiation source 6, and the location of the radiation source 6 is clearly shown in the normal commercial radiation source 6.
  • the end point is the center line of the subject H fixed by the subject table 10 that fixes the subject position.
  • the center line of the subject H is a position equidistant from the subject table 10 and the compression plate 11.
  • the starting point is the center line of the subject H
  • the end point is the uppermost surface of the plane that receives the radiation of the radiation image detector, that is, the uppermost surface of the detector holding unit 12.
  • the control device 16 sets the set shooting direction to a shooting direction that requires the rotation of the shooting device main body 2. If it is an imaging direction that requires rotation, for example, MLO (Medio- Lateral Oblique) for imaging the breast from an oblique direction force, the drive unit 17 uses the imaging device main body. 2 Rotate the entire body by a predetermined amount. When the position adjustment switch of the input device 14a is pressed, the control device 16 controls the drive device 17 accordingly to adjust the position of the object table 10.
  • MLO Medium- Lateral Oblique
  • the operator adjusts the position of the compression plate 11 by an operator such as a photography engineer, and the subject H is pressed and fixed by the compression plate 11, and an enlargement factor in phase contrast photographing by the input device 14a as a magnification setting means (this embodiment
  • the controller 16 selects the movement amount of the subject table 10 and the position information from the position detection unit 18.
  • the position of the subject H is specified according to the position of the subject table 10 and the holding device 8 is moved up and down by controlling the driving device 19 according to the positions of the subject table 10 and the compression plate 11 and the set enlargement ratio. Adjust the relative distance between the radiation source 6 and the detector holder 12 relative to.
  • the positions of the radiation source 6 and the detector holding unit 12 having an enlargement ratio set to (R1 + R2) / R1 are calculated so that the radiation source 6 and the detector holding unit 12 are obtained.
  • the holding member 8 is moved up and down.
  • the control device 16 applies a tube voltage and a tube current to the radiation source 6 from the power supply unit 15 to irradiate the subject H with radiation, and detects the radiation dose.
  • Unit 13 Force When the output radiation dose reaches the preset radiation dose, the power source unit 15 stops the radiation irradiation from the radiation source 6.
  • control device 16 controls the driving device 19 to raise and lower the holding member 8, thereby adjusting the relative distance between the radiation source 6 and the detector holding unit 12 with respect to the subject table 10. A stage is realized.
  • FIG. 5 shows a radiation source 6, a subject H, a detector holding unit 12 (numbers in the figure indicate an enlargement ratio), and a phase when a breast image is captured by the breast image capturing apparatus 1 according to the present embodiment.
  • the positional relationship of the floor surface and the ceiling in the imaging room which performs contrast imaging is schematically shown.
  • the distance L of R1 + R2 is constant even if the enlargement ratio changes, so that as the enlargement ratio increases, the floor surface and the detector holding unit 12 Therefore, if the subject position is low, it is not possible to secure the distance and the enlargement ratio that can be taken is not limited.
  • the range of subject positions where phase contrast imaging is possible can be expanded and applied to more patients. (Evaluation of visibility of breast imaging device 1)
  • FIG. 6 shows that R1 + R2, which is the distance L between the radiation source 6 and the detector holder 12, is 1555, 1140, 950, 750 (mm), and an enlarged skewer is provided for each Rl + R2.
  • R1 + R2 which is the distance L between the radiation source 6 and the detector holder 12, is 1555, 1140, 950, 750 (mm), and an enlarged skewer is provided for each Rl + R2.
  • the mammography apparatus 1 used was a prototype manufactured by Konica Minolta MG Co., Ltd., and the radiological image detector used was the company's Regius Plate RP-5PM and Regius Cascette RC-110M.
  • the radiographic image detector after mammography is read with a regius model 190 manufactured by Konica Minolta Co., Ltd. at a reading pixel pitch of 43.75 (111), and the read image is output at a writing pitch of 25 m) with a drypro model 793. did.
  • each pixel of the scanned image and each pixel of the output image are output without any interpolation processing corresponding to 1: 1, and an image with a magnification of 1.75 times has a life size (actual size) and a magnification of 1.
  • a 46x image was output at 0.83x actual size.
  • 1.25x enlargement interpolation processing was performed and output was performed at a writing pitch of 25 (am) using the enlarged interpolation image. And visibility There was no difference.
  • the factor contributing to the "output” item is the distance of R1.
  • a factor contributing to the "uniformity" item is the distance of R1. Generally, if R1 is too small, radiation cannot be irradiated on the entire surface of the radiation image detector, resulting in unevenness and low uniformity.
  • the factor that contributes to “sharpness” and “graininess” is the enlargement ratio. In general, the larger the enlargement ratio, the better the image.
  • the factor that contributes to the "scattered radiation content" is R2, and in general, the larger R2, the more the scattered radiation is removed and a better image is obtained.
  • phase contrast effect edge enhancement effect
  • enlargement ratio and R2 Factors contributing to the “phase contrast effect (edge enhancement effect)” are the enlargement ratio and R2, and the larger the enlargement ratio and R2, the more the phase contrast effect is obtained, and the better the image is.
  • the focal point size D ⁇ 30 (m) of the radiation source, the distance Rl ⁇ (D-7) / 200 (m) from the radiation source to the subject, the radiation Radiation image that can guarantee the phase contrast effect of the captured image by setting the source force to the distance L (m) 0.95 (m) to ⁇ ⁇ 14 (m).
  • the distance R2 ⁇ 0.15 (m) to the subject force detector holding means, the scattered radiation from the subject H that deteriorates the sharpness of the radiographic image is obtained. Since removal and edge enhancement can be easily recognized, it is possible to provide a radiographic image capturing apparatus that can guarantee the phase contrast effect of a captured image.
  • the average mammary gland dose is substantially inversely proportional to the square of the distance R1 between the radiation source 6 and the subject H as shown in FIGS. 6 and 7 (b). Therefore, if the magnification was 1.46 times and 2.63 times under the same radiation irradiation stop conditions as when the magnification rate was 1.75 times, the average mammary gland dose was 0.7 times and 2 times, respectively. Tripled. In other words, when taking an image at an enlargement ratio of 1.46 times under the same radiation irradiation stop conditions as when the enlargement ratio is 1.75 times, a sufficient average mammary dose cannot be obtained, and the image quality deteriorates.
  • control device 16 variably controls the radiation to be irradiated according to the enlargement ratio.
  • the control device 16 performs the irradiation radiation dose control process shown in FIG. 8, and controls the irradiation dose to be irradiated.
  • the irradiation radiation dose control process is a process realized by a software process in cooperation with the CPU of the control device 16 and a program stored in the ROM, and a control unit is realized by executing the process. Note that the start of this processing is when various settings and adjustments have been completed and the camera is in a shooting standby state. Various settings from the input device 14a, including the enlargement ratio, subject table 10, compression plate, etc. 11. Adjustment of the position of the radiation source 6 and detector holder 12 has been completed.
  • step S I when an instruction for photographing is given from the input device 14a (step S I; YES), the power supply unit
  • step S2 The tube voltage and tube current are applied to the radiation source 6 by 15 and radiation irradiation is started (step S2).
  • step S3 the set enlargement factor is determined, and if it is determined that it is 1.75 times the set value (step S3; YES), the radiation is output until the output value from the radiation dose detector 13 reaches V0. If irradiation is continued and it is determined that the output value SV0 from the radiation dose detector 13 has reached or exceeded (step S4; YES), radiation irradiation from the radiation source 6 is stopped (step S8), and this process Ends.
  • step S3 If it is determined in step S3 that the set enlargement ratio is not 1.75 times (step S3). (Step S3; NO), it is determined whether or not the set magnification is 2.63 times. 2. If it is determined that it is 63 times (Step S5; YES), the radiation dose detection unit 13 Irradiation is continued until the output value of 0.44 XV0 reaches 0.44 XV0, and if it is determined that the output value from the radiation dose detector 13 has reached 0.44 XV0 or more (step S4; YES), the radiation source Radiation from 6 is stopped (step S8), and this process ends.
  • step S5 determines that the set enlargement ratio is not 2.63 times (step S5; NO)
  • step S5 determines that the set enlargement ratio is not 2.63 times.
  • step S7 determines that the output value from the radiation dose detector 13 has reached 1.44 XV0 or higher.
  • the radiation irradiation stop condition can be controlled according to the distance of R1. It can.
  • the radiation irradiation stop condition (radiation dose) that gives the optimum image quality at the reference magnification rate X0 is V0
  • the radiation dose Vn that is the radiation irradiation stop condition for other magnification factors Xn is
  • Vn V0 X ⁇ (R1 when the magnification is Xn) / (R1 when the magnification is X0)
  • the radiation irradiation stop condition may be the same as the magnification factor of 1.75.
  • the distance of the force Rl + R2 determined to variably control the radiation dose irradiated from the radiation source 6 according to the magnification rate is determined.
  • the relationship between the magnification and the distance of R1 is 1: 1 (proportional relationship), so the radiation dose may be variably controlled by the distance of R1.
  • the amount of radiation from the radiation source is controlled so that the amount of radiation reaching the subject H is constant even when the imaging magnification is changed. It is possible to provide a radiographic imaging device that can prevent the image quality from changing due to the power S.
  • the imaging magnification is smaller! /, The amount of irradiation from the radiation source is increased, so that radiographic imaging that can prevent the image quality from changing depending on the imaging magnification can be prevented.
  • An apparatus can be provided.
  • the image quality can be adjusted according to the imaging magnification by variably controlling the radiation dose emitted from the radiation source in accordance with the imaging magnification set by the magnification setting means. It is possible to provide a radiographic image capturing apparatus that can prevent the change of the temperature.

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Abstract

L'invention concerne un dispositif de radiographie capable d'empêcher un changement de qualité d'image provoqué par un agrandissement d'imagerie par la commande de la dose de rayonnement appliquée par une source de rayonnement conformément à l'agrandissement d'imagerie réglé par un moyen de réglage d'agrandissement.
PCT/JP2007/066880 2006-09-28 2007-08-30 Dispositif de radiographie WO2008038491A1 (fr)

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JP2006-264680 2006-09-28

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018061456A1 (fr) * 2016-09-27 2018-04-05 株式会社島津製作所 Dispositif d'imagerie à différence de phase de rayonnement

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000245721A (ja) * 1999-02-25 2000-09-12 Konica Corp 放射線画像撮像装置
JP2001091479A (ja) * 1999-07-16 2001-04-06 Konica Corp Ｘ線画像撮影方法及びその撮影装置
JP2001238871A (ja) * 2000-02-29 2001-09-04 Konica Corp 放射線画像撮影装置

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000245721A (ja) * 1999-02-25 2000-09-12 Konica Corp 放射線画像撮像装置
JP2001091479A (ja) * 1999-07-16 2001-04-06 Konica Corp Ｘ線画像撮影方法及びその撮影装置
JP2001238871A (ja) * 2000-02-29 2001-09-04 Konica Corp 放射線画像撮影装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018061456A1 (fr) * 2016-09-27 2018-04-05 株式会社島津製作所 Dispositif d'imagerie à différence de phase de rayonnement
JPWO2018061456A1 (ja) * 2016-09-27 2019-04-18 株式会社島津製作所 放射線位相差撮影装置

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