WO2021075723A1 - Appareil et procédé d'imagerie par tomographie à rayons x multi-énergies - Google Patents

Appareil et procédé d'imagerie par tomographie à rayons x multi-énergies Download PDF

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Publication number
WO2021075723A1
WO2021075723A1 PCT/KR2020/012027 KR2020012027W WO2021075723A1 WO 2021075723 A1 WO2021075723 A1 WO 2021075723A1 KR 2020012027 W KR2020012027 W KR 2020012027W WO 2021075723 A1 WO2021075723 A1 WO 2021075723A1
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ray
energy
image
rays
subject
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PCT/KR2020/012027
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English (en)
Korean (ko)
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최영욱
김기현
최영진
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한국전기연구원
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    • 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
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • 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
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4035—Arrangements for generating radiation specially adapted for radiation diagnosis the source being combined with a filter or grating
    • 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
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • 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
    • A61B6/52—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
    • 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
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • A61B6/5282—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to scatter

Definitions

  • the present invention relates to an X-ray tomography imaging apparatus and method, and more particularly, to a multi-energy X-ray tomography imaging apparatus and method capable of photographing a tomography image of a subject by using multi-energy X-rays.
  • cancer can be said to be one of the most important causes of death for modern people.
  • Koreans the incidence of cancer is rapidly increasing as food and lifestyle patterns are rapidly westernized.
  • the incidence rate of cancer varies according to sex.
  • breast cancer is one of the highest incidence cancers.
  • the incidence rate is increasing so rapidly that the increase rate of breast cancer reaches 20 times the global average, which can be said to be more serious.
  • cancer can be treated greatly depending on the degree of progression after the onset of cancer, a diagnostic technique for early diagnosis is very important.
  • mammography of a two-dimensional plain image currently used it is difficult to accurately determine the occurrence of cancer, such as when the contrast of the image is low or when it is difficult to distinguish cancer cell tissues due to obstruction of muscle or adipose tissue. It is difficult to accurately determine whether there is an outbreak through image reading, as the rate of this filming reaches 36.6%.
  • the breast tissue is dense, so it is more difficult to determine the cancer cell tissue.
  • the contrast of the image may be improved, but it is still difficult to accurately determine the lesion (see 2D in Fig. 2), and the subject is X There is a problem that various side effects may occur when a contrast agent or the like is injected to improve the ray absorption characteristics.
  • DBT digital breast tomography
  • Fig. 1(b) 9 to 15 2D images are captured while rotating at a certain angular interval, and then processed to perform a series of tomography images. Is synthesized (see 3D in FIG. 2). Accordingly, in digital breast tomography (DBT), a tomography image having a higher resolution can be generated, thereby increasing the accuracy of the examination, but the amount of X-ray irradiation may increase according to multiple images, and the double energy X above. Compared to the line image, the contrast may be lowered, and further, expensive equipment is required, which increases the inspection cost and increases the time required for the inspection.
  • an X-ray tomography imaging apparatus and method capable of generating a high-resolution tomography image with a low X-ray irradiation amount while improving image contrast is required.
  • an appropriate alternative to this has not yet been presented.
  • the present invention was invented to solve the problems of the prior art as described above, and provides an X-ray tomography imaging apparatus and method capable of generating a high-resolution tomography image with a low X-ray dose while improving image contrast. It is aimed at.
  • an optical signal is generated.
  • An X-ray tomography imaging apparatus for solving the problem of passing through the first optical signal passing through the path (P1) and the second path (P2) longer than the first path (P1)
  • An X-ray source for sequentially irradiating X-rays of a plurality of different energy levels to a subject while moving along a predetermined first path
  • An X-ray detector configured to generate an X-ray image by detecting X-rays irradiated from the X-ray source and passing through the subject
  • a tomography image generator for generating a tomography image of the subject by using a plurality of X-ray images generated by the X-ray detector
  • a control unit for controlling the X-ray source, the X-ray detector, and the tomography image generator.
  • the X-ray source sequentially irradiates X-rays of the plurality of energy levels to the subject at a plurality of positions including a first position and a second position of the first path, and at the first position, the X-rays of the first energy Is irradiated to the subject, and at the second position adjacent to the first position, an X-ray having a second energy higher than the first energy may be irradiated to the subject.
  • the tomography image generator uses a first-first image generated using an X-ray of the first energy at the first position, and uses a first-first position corresponding to the second energy at the first position. 2 You can create an image.
  • a first image corresponding to the second energy at the first position by using a 2-1 image generated using X-rays of the second energy at the second position 2 You can create an image.
  • the tomography image generator may generate a 1-3th image with improved contrast with respect to the first location by using the 1-1th image and the 1-2nd image.
  • the tomography image generator may generate the 1-2 image using a U-network, a Cycle-GAN, or another neural network.
  • the tomography image generator may generate a tomography image of the subject by using a plurality of contrast enhancement images corresponding to the plurality of positions.
  • a filter unit for selectively filtering one of the first energy X-rays and the second energy X-rays may be provided.
  • the filter unit when the first energy X-ray is irradiated, the filter unit may be removed from the X-ray irradiation path, and when the second energy X-ray is irradiated, a driving unit may be provided to move the filter unit to the X-ray irradiation path.
  • a grid for reducing scattering of the X-rays may be provided on the X-ray detector.
  • X-rays of different energy levels are sequentially irradiated to the subject to generate X-ray images of different energy levels, but the energy level that is not irradiated at each location X-ray tomography imaging capable of generating a high-resolution tomography image with a low X-ray dose while improving the contrast of the image by using it to generate a tomography image of the subject after calculating the X-ray image of The device can be implemented.
  • 1 is a 2D and 3D image diagnosis apparatus for breast cancer diagnosis according to the prior art.
  • 2 is a conceptual diagram of 2D and 3D images according to the prior art.
  • FIG. 3 is a block diagram of an X-ray tomography imaging apparatus according to an embodiment of the present invention.
  • FIG. 4 is a diagram illustrating an operating principle of an X-ray tomography imaging apparatus according to an embodiment of the present invention.
  • FIG. 5 is an exemplary view of an X-ray tomography imaging apparatus according to an embodiment of the present invention.
  • FIG. 6 is an X-ray spectrum by a filter unit of an X-ray tomography imaging apparatus according to an embodiment of the present invention.
  • FIG. 7A and 7B are exemplary views of a filter unit and a driving unit of an X-ray tomography imaging apparatus according to an exemplary embodiment of the present invention.
  • first and second may be used to describe various components, but the components are not limited by the terms, and the terms are used to distinguish one component from other components. Is only used.
  • FIG. 3 a block diagram of an X-ray tomography imaging apparatus 100 according to an embodiment of the present invention is shown.
  • the X-ray tomography imaging apparatus 100 transmits X-rays of different energy levels to the subject 200 while moving along a predetermined first path.
  • X-ray tomography imaging apparatus 100 while moving along a predetermined first path, X-rays of different energy levels are sequentially irradiated to the subject 200 while An X-ray image of different energy levels is generated, but an X-ray image of an energy level that is not irradiated at each location is also calculated, and then a tomography image of the subject 200 is generated by using it. It is possible to generate a high-resolution tomography image with a low X-ray dose while improving the contrast.
  • the X-ray tomography imaging apparatus 100 is divided by components and examined in detail.
  • the X-ray source 110 sequentially irradiates X-rays of different energy levels to the subject 200 while moving along a predetermined first path.
  • the X-ray source 110 sequentially irradiates the X-rays of the plurality of energy levels to the subject 200 at a plurality of positions including a first position and a second position of the first path, and the first position
  • X-rays of a first energy may be irradiated to the subject
  • X-rays of a second energy higher than the first energy may be irradiated to the subject 200 at the second position adjacent to the first position.
  • the X-ray source 110 rotates along an arc centered on the subject 200 and transmits low-energy and high-energy (for example, 27KV and 43KV) X-rays at 15 degree intervals.
  • the subject 200 may be irradiated.
  • the X-ray source 110 rotates along an arc centered on the subject 200 and transmits a low energy X-ray of 27 KV at the first position (Fig. 4 (a1)) to the subject ( 200), and a high energy X-ray of 43 KV is irradiated to the subject 200 at a second position ((a2) of FIG. 4) moved by 15 degrees from the first position.
  • the present invention is not necessarily limited thereto, and X-rays of three different energy levels are sequentially irradiated, or four or more energy levels Various embodiments are possible, such as sequentially irradiating X-rays of.
  • the X-ray source 110 may sequentially irradiate X-rays of a plurality of energy levels while moving at equal angular intervals, but the present invention is not necessarily limited thereto, and the subject 200 It is also possible to irradiate X-rays at non-uniform angular intervals depending on the location where the tomography image can be generated more efficiently in consideration of the characteristics of
  • the X-ray source 110 must be capable of generating X-rays of the plurality of energy levels and irradiating the X-rays to the subject 200.
  • the X-ray source 110 may be configured by using various devices capable of generating X-rays of multiple energy levels that can be used to generate an X-ray image and irradiating it to the subject 200.
  • HFG high-frequency X-ray generator
  • the plurality of X-ray generators 310 sequentially irradiate the subject 200 with X-rays of a plurality of energy levels at predetermined angular intervals while moving along a concentric arc.
  • the X-ray detector 320 detects X-rays that are irradiated from the X-ray source 110 and transmitted through the subject 200 to generate an X-ray image.
  • the X-ray source 110 sequentially irradiates X-rays of different energy levels to the subject 200 while moving along a predetermined first path. X-ray images of X-rays of different energy levels are sequentially generated.
  • a low energy X-ray of 27 KV at the first position (Fig. 4 (a1)) is transmitted to the subject ( 200)
  • the X-ray detector 320 generates a low-energy X-ray image for the first location
  • the X-ray source 110 generates 43 KV at the second location ((a2) in FIG. 4).
  • the X-ray detector 320 When high-energy X-rays are irradiated onto the subject 200, the X-ray detector 320 generates a high-energy X-ray image of the second location.
  • the X-ray detector 120 generates a digital image so that the X-ray image can be processed more efficiently.
  • the thus formed X-ray image is transmitted to the tomography image generator 130 and is used to generate a tomography image of the subject 200.
  • the X-ray sensing unit 120 above shows an example in which the low-energy X-ray and the high-energy X-ray are sequentially detected, but the present invention is not necessarily limited thereto, and the X-ray sensing unit 120 is different from each other. It may be configured in various ways, such as sequentially detecting X-rays of three energy levels, or generating an X-ray image by sequentially detecting X-rays of four or more energy levels.
  • the tomography image generation unit 130 generates a tomography image of the subject by using a plurality of X-ray images generated by the X-ray detection unit 120.
  • a 1-2 video can be generated.
  • the X-ray detector 320 While the X-ray source 110 rotates along an arc centered on the subject 200, a low energy X-ray of 27 KV at the first position (Fig. 4 (a1)) is transmitted to the subject ( 200), the X-ray detector 320 generates a 27KV low-energy X-ray image for the first position, and the X-ray source 110 is 43KV at the second position ((a2) in FIG. 4).
  • the high-energy X-ray of is irradiated to the subject 200, the X-ray detector 320 generates a 43KV high-energy X-ray image of the second location.
  • the tomography image generator 130 may generate a high-energy X-ray image of the first location by using the low-energy X-ray image of the first location.
  • the tomography image generator 130 may generate a high-energy X-ray image for the first location by considering a high-energy X-ray image of a second location adjacent to the first location.
  • the second energy corresponding to the second energy at the first position by using the 2-1 image generated by using the X-ray of the second energy at the second position. It is also possible to generate a 1-2 image.
  • the X-ray detector 320 While the X-ray source 110 rotates along an arc centered on the subject 200, a low energy X-ray of 27 KV at the first position (Fig. 4 (a1)) is transmitted to the subject ( 200), the X-ray detector 320 generates a 27KV low-energy X-ray image for the first position, and the X-ray source 110 is 43KV at the second position ((a2) in FIG. 4).
  • the high-energy X-ray of is irradiated to the subject 200
  • the X-ray detector 320 When the high-energy X-ray of is irradiated to the subject 200, the X-ray detector 320 generates a 43KV high-energy X-ray image of the second location.
  • the tomography image generator 130 may generate a high-energy X-ray image of the first location by using the high-energy X-ray image of the second location.
  • the tomography image generator 130 may generate a high energy X-ray image for the first location by considering the low energy X-ray image at the first location.
  • the tomography image generator 130 may generate a high energy 1-2 image for the first location using a U-network, a Cycle-GAN, or another neural network.
  • the neural network circuit such as the U-network and Cycle-GAN can be implemented by applying a conventional technique, a detailed description thereof will be omitted.
  • the neural network circuit receives the low energy 1-1 image generated at the first position and receives the Generates a high energy 1-2 image for the first location or receives a high energy 2-1 image generated at a second location adjacent to the first location and receives a high energy 1-2 image for the first location. It is possible to generate 2 images, and further, it is possible to generate a high-energy image 1-2 for the first location by receiving both the 1-1 image and the 2-1 image.
  • the tomography image generator 130 may generate a 1-3 image with improved contrast with respect to the first location by using the 1-1 image and the 1-2 image. do.
  • the tomography image generation unit 130 may generate a tomography image of the subject 200 by using a plurality of contrast enhancement images corresponding to the plurality of positions.
  • the X-ray source 110 irradiates only one X-ray of a plurality of energy levels to the subject 200 at each location. Since the X-ray image is generated and the X-ray image for the remaining energy level is generated by inputting the previously generated X-ray image to a neural network circuit, etc., the amount of X-ray irradiation to the subject 200 is greatly reduced while at each location. By calculating X-ray images of a plurality of energy levels at, it is possible to generate an X-ray image with improved contrast.
  • the X-ray source 110 is moved to the subject 200 using a plurality of contrast-improving X-ray images.
  • a tomography image of the image it is possible to generate a high-resolution tomography image with a low X-ray dose while improving the contrast of the image.Through this, it is possible to generate a sufficiently high-quality tomography image even if the subject is not administered a contrast agent.
  • side effects caused by contrast agents can also be minimized.
  • FIG. 5 shows an exemplary view of an X-ray tomography imaging apparatus 100 according to an embodiment of the present invention.
  • the X-ray source 110 is mounted on the structure 150 and moves according to the rotation of the structure 150, while the subject 200 ) Can be used to irradiate X-rays.
  • the structure 150 serves to fix the X-ray detector 120 at a predetermined position.
  • the present invention is not necessarily limited thereto, and the structure 150 may be implemented in various structures capable of fixing or driving the X-ray source 110 and the X-ray detector 120.
  • the controller 140 controls the X-ray source 110, the X-ray detector 120, and the tomography image generator 130 to operate properly.
  • the X-ray source 110 is controlled to irradiate the subject 200 with X-rays of multiple energy levels while moving the X-ray source 110 along a predetermined first path, and accordingly, an X-ray detector 120 detects the transmitted X-rays, generates an X-ray image at each location, and transmits it to the tomography image generation unit 130, and the tomography image generation unit 130 generates the plurality of X-ray images. Is controlled to generate a tomography image of the subject 200.
  • the X-ray tomography imaging apparatus 100 is provided with a filter unit 151 that selectively filters one of X-rays of multiple energy levels generated by the X-ray source 110 Can be.
  • the filter unit 151 when the X-ray source 110 sequentially irradiates an X-ray of a first energy and an X-ray of a second energy higher than the first energy to the subject 200, the filter unit 151 is One of them may be selectively filtered to irradiate the subject 200.
  • the filter unit 151 does not filter low energy X-rays of 27 KV (27 KV in Fig. 6), and when high energy X-rays of 43 KV are irradiated, the filter unit 151 has a thickness of 3 mm.
  • the amount of 43KV X-ray irradiation can be adjusted (43KV_43KV+Al 3mm in FIG. 6).
  • the filter unit 151 removes the filter unit 151 from the irradiation path of the X-ray when the first energy is irradiated with X-rays, and when the second energy is irradiated with the X-ray, the filter unit 151 ) May be provided with a driving unit 152 that moves to the X-ray irradiation path.
  • the structure 150 drives or removes the filter unit 151 and the filter unit 151 made of an aluminum plate or the like through the X-ray irradiation path.
  • the driving unit 152 for this may be configured using a motor or the like.
  • the driving unit 152 has a lever structure, etc., so that the driving distance of the filter unit 151 is greater than the driving distance of a driving motor, etc., so that the filter unit 151 ), it is also possible to increase the driving distance or to improve the driving speed of the filter unit 151 more quickly.
  • the X-ray tomography imaging apparatus 100 it is possible to optimize image quality such as contrast of an X-ray image generated by adjusting the spectrum of the high-energy and low-energy X-rays.
  • a grid may be provided on the X-ray detector 120 to reduce scattering of the X-rays.
  • the grid is preferably adjusted to the ratio of the depth and the interval to minimize the scattering of X-rays, for a more specific example, the depth and the ratio of the grid is produced in the range of 5:1 to 8:1 X Line scattering can be minimized.
  • the X-ray tomography imaging apparatus 100 while moving along a predetermined first path, X-rays of different energy levels are sequentially irradiated to the subject, and the plurality of energy levels are different from each other. An X-ray image of is generated, but an X-ray image of an energy level that is not irradiated at each location is also calculated, and then a tomography image of the subject is generated, thereby improving the contrast of the image and reducing the X-ray image. High-resolution tomography images can be generated with the amount of radiation.

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Abstract

La présente invention concerne un appareil et un procédé d'imagerie par tomographie à rayons X et, plus particulièrement, un appareil et un procédé d'imagerie par tomographie à rayons X multi-énergie capables de capturer une image tomographique d'un sujet à l'aide de rayons X multi-énergie. La présente invention met en œuvre l'appareil pour l'imagerie par tomographie à rayons X, l'appareil comprenant : une source de rayons X qui irradie de façon séquentielle, vers le sujet, des rayons X ayant une pluralité de niveaux d'énergie différents tout en se déplaçant le long d'un premier trajet prédéterminé ; une unité de détection de rayons X qui génère des images de rayons X en détectant les rayons X irradiés à partir de la source de rayons X et transmis à travers le sujet ; une unité de génération d'image tomographique qui génère une image tomographique du sujet à l'aide de la pluralité d'images de rayons X générées par l'unité de détection de rayons X ; et une unité de commande qui commande la source de rayons X, l'unité de détection de rayons X et l'unité de génération d'image tomographique.
PCT/KR2020/012027 2019-10-15 2020-09-07 Appareil et procédé d'imagerie par tomographie à rayons x multi-énergies WO2021075723A1 (fr)

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KR1020190128066A KR20210044638A (ko) 2019-10-15 2019-10-15 다중 에너지 x선 단층영상 촬영 장치 및 방법
KR10-2019-0128066 2019-10-15

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KR20140087206A (ko) * 2012-12-28 2014-07-09 삼성전자주식회사 엑스선 촬영 장치 및 엑스선 영상 처리 방법
KR20150018665A (ko) * 2013-08-08 2015-02-24 삼성전자주식회사 엑스선 영상 장치 및 그 제어 방법
KR101687971B1 (ko) * 2010-07-19 2016-12-21 삼성전자주식회사 유방 촬영 장치 및 그 방법
JP2019058488A (ja) * 2017-09-27 2019-04-18 キヤノンメディカルシステムズ株式会社 Ｘ線ｃｔ装置
KR102023285B1 (ko) * 2018-10-01 2019-09-19 오준호 3차원 영상 재구성 방법

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Publication number Priority date Publication date Assignee Title
KR20160079961A (ko) 2014-12-26 2016-07-07 한국전기연구원 이중 에너지 준위 엑스선원을 이용한 엑스선 투시 촬영 장치

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR101687971B1 (ko) * 2010-07-19 2016-12-21 삼성전자주식회사 유방 촬영 장치 및 그 방법
KR20140087206A (ko) * 2012-12-28 2014-07-09 삼성전자주식회사 엑스선 촬영 장치 및 엑스선 영상 처리 방법
KR20150018665A (ko) * 2013-08-08 2015-02-24 삼성전자주식회사 엑스선 영상 장치 및 그 제어 방법
JP2019058488A (ja) * 2017-09-27 2019-04-18 キヤノンメディカルシステムズ株式会社 Ｘ線ｃｔ装置
KR102023285B1 (ko) * 2018-10-01 2019-09-19 오준호 3차원 영상 재구성 방법

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