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WO2012143971A1 - Appareil d'imagerie radiographique - Google Patents

Appareil d'imagerie radiographique Download PDF

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Publication number
WO2012143971A1
WO2012143971A1 PCT/JP2011/002288 JP2011002288W WO2012143971A1 WO 2012143971 A1 WO2012143971 A1 WO 2012143971A1 JP 2011002288 W JP2011002288 W JP 2011002288W WO 2012143971 A1 WO2012143971 A1 WO 2012143971A1
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WO
WIPO (PCT)
Prior art keywords
image
original
original image
imaging apparatus
composite image
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Ceased
Application number
PCT/JP2011/002288
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English (en)
Japanese (ja)
Inventor
澤田　弘
ミッシェル ダージス
貴則 吉田
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Shimadzu Corp
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Shimadzu Corp
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Priority to PCT/JP2011/002288 priority Critical patent/WO2012143971A1/fr
Publication of WO2012143971A1 publication Critical patent/WO2012143971A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • A61B6/12—Arrangements for detecting or locating foreign bodies
    • 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
    • A61B6/504—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 blood vessels, e.g. by angiography
    • 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
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
    • A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT

Definitions

  • the present invention relates to a radiographic apparatus that acquires an image by irradiating a subject with radiation, and more particularly to a radiographic apparatus for surgery in which a stent is introduced.
  • Patent Document 1 a radiation imaging apparatus is provided that acquires an image by irradiating a subject with radiation. A specific configuration of such a radiation imaging apparatus will be described. In the following description, it is particularly assumed that the stenosis of the blood vessel is healed.
  • a guide wire is first introduced into the blood vessel of the subject.
  • the guide wire is provided with a plurality of stent markers indicating a part of the guide wire.
  • the stent marker is made of a metal that hardly transmits radiation.
  • the guide wire is introduced with the subject set on the radiation imaging apparatus.
  • the radiographic apparatus continuously performs radiography of the subject over time, and the operator can visually recognize the radiographic image captured at this time as a moving image (live image). Since the stent marker has the property of absorbing radiation, it is clearly reflected in the live image. The surgeon can know whether the stent marker has been introduced into the stenosis of the blood vessel by checking the moving image.
  • a previously placed stent marker is present at the treatment site.
  • the surgeon can know the positional relationship between the stent introduced last time and the stent marker of the stent introduced this time by checking the moving image.
  • a composite image in which the positional relationship between the stenosis portion of the blood vessel and the stent marker is clarified is generated by superimposing the radiographic images (frames) forming the live image. Yes.
  • the blood vessels of the subject are reflected more clearly than each frame.
  • the conventional configuration has the following problems. That is, according to the conventional configuration, there is a problem that it is not possible to sufficiently follow the temporal change in the positional relationship between the stent marker and the stenosis portion of the blood vessel. In order to generate a composite image, it is necessary to superimpose a plurality of frames. At this time, the frames are overlapped so as to overlap each other.
  • Such a configuration causes a problem when performing surgery on blood vessels close to the heart. That is, as shown in FIG. 7, the image shown in each frame moves with the pulsation because the blood vessel is close to the heart. Therefore, if the frames are simply overlapped, the positions of the stenosis of the blood vessel and the stent marker do not match between the frames, and the stenosis does not form an image in the composite image.
  • the frames are overlapped, and the position of the stenosis of the blood vessel and the stent marker reflected in each frame is not shifted on the image.
  • Each person must superimpose each frame while confirming.
  • the present invention has been made in view of such circumstances, and an object of the present invention is to provide radiation imaging capable of generating in real time a composite image in which a fluoroscopic image of a subject is reflected by superimposing moving image frames. To provide an apparatus.
  • a radiation imaging apparatus includes a radiation source that emits radiation, a detection unit that detects radiation, an image generation unit that generates an original image based on a detection signal output from the detection unit, A position specifying means for specifying the position of the object reflected in each, a positioning means for performing alignment of the original image based on the position of the object based on the position data of the object output by the position specifying means, and a position
  • the image processing apparatus includes a composite image generation unit that generates a composite image by superimposing the combined original images.
  • the composite image according to the present invention is generated by superposing the aligned original images. As a result, even if the position of the subject in the original image is different, the image of the subject is surely formed in the composite image.
  • the alignment is performed by specifying the position of the object that is reflected in each of the original images. If alignment is performed based on the image reflected in the original image as described above, the subject image is clearly reflected in the generated composite image, which is suitable for diagnosis.
  • a composite image can be generated in real time, so that the operator can observe changes in the subject image over time with a clear image. Become.
  • the above-described radiation imaging apparatus includes a moving image generation unit that generates a moving image using the original image generated one after another as a frame.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention.
  • a moving image using the original image as a frame in addition to the composite image is generated, the convenience of the surgeon's diagnosis is further improved.
  • the composite image is not always clear. This is because the position specifying means may not be able to accurately specify the position of the object in the original image. In such a case, if the surgeon can refer to the moving image with the original image as a frame, the operator can visually recognize the moving image that clearly shows the image of the subject as compared with the synthesized image.
  • the alignment of the original image performed by the position specifying unit is realized by translation and rotation of the original image.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. That is, if the alignment of the original image performed by the position specifying means is realized by translation and rotation of the original image, the object is placed at the same position regardless of the change in the position of the object in each original image. A composite image can be generated by superimposing with certainty.
  • trimming means for trimming a region surrounding the object in the composite image is provided.
  • the radiographic apparatus described above further includes trimming means for trimming a region surrounding the object from the original image to generate a trimmed image based on the position data of the object specified by the position specifying means. It is more desirable that the image generating means acts on the trimmed image.
  • the object whose position is specified by the position specifying means is more preferably a guide wire stent marker reflected in the original image.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention.
  • the stent marker is devised so as to be clearly reflected in the original image. Therefore, if the position specifying means operates based on the stent marker, the original images can be more reliably aligned.
  • the position specifying unit, the positioning unit, and the composite image generating unit may repeatedly execute position specification, registration, and composite image generation each time an original image is acquired. More desirable.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. If a composite image is generated each time an original image is acquired, the composite image will be updated in real time, so that the operator can observe changes in the subject image over time with a clear image. It becomes like this.
  • the above-described radiation imaging apparatus includes a display unit that displays a composite image in real time together with a moving image.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention. If the composite image is displayed together with the moving image in real time, the surgeon can perform an operation while reliably comparing the moving image and the composite image.
  • the above-described configuration shows a specific configuration of the radiation imaging apparatus of the present invention.
  • the configuration of the present invention is suitable for vascular stenosis treatment. This is because when the blood vessel in which the stenosis occurs is close to the heart, the position of the subject image in the original image varies with the pulsation. According to the present invention, after aligning an image reflected in the original image as a reference, they are superimposed to generate a composite image, so that even in such a case, a clear composite image is generated. it can.
  • the composite image according to the present invention is generated by superimposing the aligned original images. As a result, even if the position of the subject in the original image is different, the image of the subject is surely formed in the composite image.
  • the alignment is performed by specifying the position of the object that is reflected in each of the original images. If alignment is performed based on the image reflected in the original image as described above, the subject image is clearly reflected in the generated composite image, which is suitable for diagnosis.
  • a composite image can be generated in real time, so that the operator can observe the temporal change of the subject image with a clear image.
  • FIG. 1 is a functional block diagram illustrating a configuration of an X-ray imaging apparatus according to Embodiment 1.
  • FIG. 3 is a flowchart for explaining the operation of the X-ray imaging apparatus according to Embodiment 1;
  • FIG. 3 is a schematic diagram for explaining the operation of the X-ray imaging apparatus according to Embodiment 1.
  • FIG. 3 is a schematic diagram for explaining the operation of the X-ray imaging apparatus according to Embodiment 1.
  • FIG. 3 is a schematic diagram for explaining the operation of the X-ray imaging apparatus according to Embodiment 1.
  • FIG. 3 is a schematic diagram for explaining the operation of the X-ray imaging apparatus according to Embodiment 1. It is a schematic diagram explaining the problem of the X-ray imaging apparatus in a conventional structure.
  • X-rays in the examples correspond to the radiation of the present invention.
  • FPD is an abbreviation for flat panel detector.
  • the X-ray imaging apparatus 1 of the present invention is intended for the treatment of blood vessel stenosis.
  • the X-ray imaging apparatus 1 includes a top plate 2 on which a subject M is placed, an X-ray tube 3 that irradiates X-rays provided above the top plate 2, and a bottom plate 2. And an FPD 4 for detecting X-rays provided on the side.
  • the FPD 4 is a rectangle having four sides along either the body axis direction A or the body side direction S of the subject M.
  • the X-ray tube 3 irradiates the FPD 4 with a quadrangular pyramid-shaped X-ray beam that spreads radially.
  • the FPD 4 receives the X-ray beam on the entire surface.
  • X-ray detection elements are two-dimensionally arranged in the body axis direction A and the body side direction S.
  • the X-ray tube 3 corresponds to the radiation source of the present invention
  • the FPD 4 corresponds to the radiation detection means of the present invention.
  • the X-ray tube control unit 6 is provided for the purpose of controlling the X-ray tube 3 with a predetermined tube current, tube voltage, and pulse width.
  • the FPD 4 detects X-rays emitted from the X-ray tube 3 and transmitted through the subject M, and generates a detection signal. This detection signal is sent to the image generation unit 11, where an original image P0 in which a projection image of the subject M is reflected is generated.
  • the X-ray tube control unit 6 corresponds to the radiation source control unit of the present invention
  • the image generation unit 11 corresponds to the image generation unit of the present invention.
  • the position specifying unit 12 is provided for the purpose of specifying the position of the stent marker s of the guide wire reflected in each of the original images P0.
  • the trimming unit 13 is provided for the purpose of generating the trimmed image P1 by trimming the portion where the stent marker s is reflected from the original image P0 based on the position data of the stent marker s.
  • the alignment unit 14 is provided for the purpose of aligning each trimmed image P1 based on the position data of the stent marker s based on the position data of the stent marker s.
  • the composite image generation unit 15 is provided for the purpose of generating the composite image P2 by superimposing the aligned trimmed images P1.
  • the position specifying unit 12 corresponds to the position specifying unit of the present invention
  • the trimming unit 13 corresponds to the trimming unit of the present invention
  • the alignment unit 14 corresponds to the alignment unit of the present invention
  • the composite image generation unit 15 corresponds to the composite image generation unit of the present invention.
  • the moving image generating unit 16 generates a moving image with the original image P0 generated one after another as a frame.
  • the moving image generating unit 16 corresponds to the moving image generating means of the present invention.
  • the display unit 25 is provided for the purpose of displaying each image acquired by X-ray imaging.
  • the console 26 is provided for the purpose of inputting an instruction such as an X-ray irradiation start by the operator.
  • the main control unit 27 is provided for the purpose of comprehensively controlling each control unit.
  • the main control unit 27 is constituted by a CPU, and realizes the control units 6 and 7 and the units 11, 12, 13, 14, 15, and 16 by executing various programs. Further, each of the above-described units may be divided and executed by an arithmetic device that takes charge of them.
  • the storage unit 28 stores all parameters relating to control of the X-ray imaging apparatus 1 such as parameters used for image processing and intermediate images generated along with the image processing.
  • the display unit 25 corresponds to display means of the present invention.
  • ⁇ Operation of X-ray imaging apparatus Next, the operation of the X-ray imaging apparatus will be described with reference to FIG.
  • the X-ray imaging apparatus first, the subject M is placed on the X-ray imaging apparatus (placement step S1), and imaging of the X-ray image is started (imaging start step S2). Then, generation of a moving image (live image) is started based on the original image P0 generated by the image generation unit 11 (moving image generation start step S3), and generation of a composite image P2 is started based on the original image P0 (synthesis). Image generation step S4).
  • these steps will be described in order. In the following description, it will be described how the X-ray imaging apparatus according to the present invention is used in a technique for removing stenosis in a blood vessel close to the heart of the subject M.
  • ⁇ Installation Step S1, Shooting Start Step S2> First, the subject M is placed on the top 2 and a guide wire is inserted into the blood vessel of the subject M.
  • a guide wire is inserted into the blood vessel of the subject M.
  • the surgeon gives an instruction to start fluoroscopic imaging to the X-ray imaging apparatus through the console 26, pulsed X-rays are intermittently emitted from the X-ray tube 3.
  • the FPD 4 detects X-rays that have passed through the subject M, and sends a detection signal to the image generation unit 11.
  • the image generation unit 11 generates the original image P0 by mapping the X-ray detection intensity in each part of the FPD 4 two-dimensionally.
  • the original image P0 includes a projected image of the subject M and a guide wire.
  • the image generation unit 11 repeats generation of the original image P0 every time X-rays are irradiated.
  • FIG. 3 illustrates the original image P0 generated at this time.
  • FIG. 3 shows three original images P0a, P0b, and P0c generated at different points in time, and the original images are generated in this order. Since the operation is being performed on a blood vessel close to the heart of the subject M, the position and shape of the guide wire G reflected in the original image P0 are the original images P0a, P0b, and P0c according to the pulsation of the heart. Will be different.
  • the guide wire G is provided with two stent markers s and represents the position of the stent in the guide wire G.
  • the stent is a cylindrical wire mesh mounted inside the blood vessel, and the two stent markers s indicate the positions of both ends of the stent.
  • the stent marker s is made of a spherical metal, and therefore appears more clearly in the original image P0. The surgeon can indirectly know the position of the stent by confirming the position of the stent marker s in the original image P0.
  • the number of stent markers s provided on the guide wire G is not limited to two.
  • the original image P0 is sent to the moving image generation unit 16.
  • the moving image generating unit 16 combines the original images P0 in association with time to generate a moving image (live image) in which the subject image and the guide wire G are reflected.
  • the moving image is displayed on the display unit 25. Specifically, as soon as the original image P0 is generated, the corresponding frames are sequentially displayed on the display unit 25.
  • the original image P0 is also sent to the position specifying unit 12.
  • the position specifying unit 12 acquires the positions of the two stent markers s in the original image P0 by image processing.
  • the shape of the stent marker image in the original image P0 is known. Therefore, the position specifying unit 12 can acquire the position of the stent marker s in the original image P0 by applying a filter that searches for the shape of the stent marker image to the original image P0.
  • the position specifying unit 12 adds the position information of the stent marker s to the data of the original image P0 and sends the original image P0 to the trimming unit 13.
  • the position specifying unit 12 repeats this operation every time the original image P0 is acquired.
  • the trimming unit 13 performs a trimming process on each of the original images P0 (P0a, P0b, P0c) as shown in FIG. That is, the trimming unit 13 sets a range R in which both the stent markers s appearing in the original image P0 are included, and extracts this region R from the original image P0.
  • the image generated in this way is a trimmed image P1 (P1a, P1b, P1c in FIG. 4).
  • the trimming unit 13 determines the position of the region R so that one stent marker image appears at one end of the rectangular region R and the other stent marker image appears at the other end of the region R. At that time, the shape of the region R does not change with each trimming operation.
  • the trimming unit 13 sends each trimmed image P1 to the alignment unit 14. The trimming unit 13 repeats this operation every time the original image P0 is acquired.
  • the alignment unit 14 aligns the trimmed image P2 based on the stent marker image appearing in each trimmed image P2. That is, image rotation and translation processing are performed so that the position of one stent marker s appearing in each trimmed image P1 is the same position and the other stent marker s is the same position.
  • Each trimmed image P ⁇ b> 1 that has been aligned is sent to the composite image generation unit 15.
  • the trimming unit 13 and the alignment unit 14 cooperate with each other to perform a data process of translation and rotation on the basis of the position data of the stent marker image output from the position specifying unit 12 to form a part of the original image P0. In other words, the image is aligned.
  • the composite image generation unit 15 generates a composite image P2 by superimposing the trimmed images P1 after alignment. Since a plurality of images are superimposed on the composite image P2, the subject image is reflected with a higher contrast than the original image P0 as well as the guide wire G and the stent marker s.
  • the composite image P2 is displayed on the display unit 25.
  • the composite image generation unit 15 generates a single composite image P2 by superimposing a plurality of (for example, about 7 to 12) trimming images P1.
  • FIG. 5 shows a state in which the composite image P2 is displayed on the display unit 25.
  • the screen of the display unit 25 is divided into three areas, and the original image P0 (more precisely, a live image with the original image P0 as a frame) is displayed in real time on the upper left of the screen.
  • trimmed images P1 after alignment are arranged and displayed in order of shooting time. Since the trimmed images P1 are acquired one after another, the trimmed image P1 at a certain point of time first appears in the rightmost position at the bottom of the screen occupied by the trimmed image P1g in FIG. The frame is moved frame by frame, and finally the image displayed at the left end position of the screen occupied by the trimmed image P1a in FIG. The time interval at which the trimmed image display is updated coincides with the interval at which the original image P0 is acquired.
  • the composite image P2 is displayed on the upper right of the screen.
  • the composite image P2 includes details of the subject image.
  • the live image, the trimmed image P1, and the composite image P2 are displayed by being appropriately enlarged or reduced according to the size of the divided area set in the display unit 25. This enlargement / reduction is performed by the display unit 25.
  • FIG. 6 is a diagram schematically illustrating how the composite image P2 is generated. For simplicity of explanation, it is assumed that the composite image P2 is generated from four original images P0.
  • the upper part of FIG. 6 shows how the composite image P2a is generated.
  • the composite image P2a is generated from the four original images P0a, P0b, P0c, and P0d that have been acquired recently.
  • the original images are generated in the order of P0a, P0b, P0c, and P0d, and the original image P0e is currently being generated.
  • the middle part of FIG. 6 shows how the composite image P2b is generated after the original image P0e is generated.
  • the composite image P2b is generated from the four original images P0b, P0c, P0d, and P0e that have been recently acquired.
  • the original image P0f is currently being generated.
  • the lower part of FIG. 6 shows a state in which the composite image P2c is generated after the original image P0f is generated.
  • the composite image P2c is generated from the four original images P0c, P0d, P0e, and P0f that have been acquired recently.
  • the original image P0g is currently being generated.
  • the composite image generation unit 15 uses the recently acquired four (actually 7 to 12) original images P0 represented by shading in FIG. Is generated. That is, every time the original image P0 is acquired, the composite image generation unit 15 replaces the previous acquired image P2 of the original images P0 used for generating the previous combined image P2 with the previous combined image P2. The original image P0 that has not been acquired in the generation of is used for the generation of the current composite image P2.
  • the composite image generation unit 15 continuously generates the composite image P2 in real time by updating the combination of the original images P0 used to generate the composite image P2 every time the original image P0 is acquired. The composite image generation unit 15 repeats this operation every time the original image P0 is acquired.
  • the composite image P2 of Example 1 can also be understood as being displayed on the display unit 25 as a moving image.
  • the frame rate at this time is the same as a live image with the original image P0 as a frame.
  • the display unit 25 displays the composite image P2 in real time together with the live image having the original image P0 as a frame.
  • the operator changes the position of the stent marker s and the blood vessel image of the subject M over time while visually recognizing the original image P0, the trimmed image P1, and the composite image P2 that are successively updated on the screen of the display unit 25. Can be confirmed.
  • the surgeon moves the stent to the stenosis of the blood vessel of the subject M, attaches the stent to the blood vessel, and the operation of the X-ray imaging apparatus is completed.
  • the composite image P2 according to the first embodiment is generated by superimposing the aligned original image P0. Thereby, even if the position where the subject M is reflected differs between the original images P0, the image of the subject M is surely formed in the composite image. Then, the alignment is performed by specifying the position of the stent marker image reflected in each of the original images P0. If alignment is performed based on the image reflected in the original image P0 as described above, the subject image will be clearly reflected in the generated composite image P2, and a configuration suitable for diagnosis can be obtained. Become. Further, if the original image P0 is superposed while performing alignment, the composite image P2 can be generated in real time, so that the operator can observe the temporal change of the subject image with a clear image. It becomes like this.
  • the convenience of the surgeon's diagnosis is further improved.
  • the composite image P2 is not always clear. This is because the position specifying unit 12 may not be able to accurately specify the position of the stent marker image in the original image P0. In such a case, if the surgeon can refer to the moving image with the original image P0 as a frame, the surgeon can visually recognize the moving image showing the image of the subject M more clearly than the synthesized image P2. it can.
  • the composite image P2 can be generated by reliably overlapping the stent marker images at the same position.
  • the operator can also visually recognize the trimmed original image P0 together with the synthesized image P2. Therefore, the operator can surely recognize the change of the stent marker image over time.
  • the stent marker s is devised to be clearly reflected in the original image P0. Therefore, if the position specifying unit 12 operates based on the stent marker s, the original images can be more reliably aligned.
  • Example 1 is suitable for vascular stenosis treatment. This is because when the blood vessel in which stenosis has occurred is close to the heart, the position of the subject image in the original image P0 varies with pulsation.
  • the composite image P2 is generated by superimposing these images after aligning them based on the image reflected in the original image P0, so that even in such a case, a clear composition is achieved. An image P2 can be generated.
  • the present invention is not limited to the above-described configuration, and can be modified as follows.
  • the images are superimposed after the trimming operation of the original image P0, but the present invention is not limited to this configuration. That is, after aligning the original image P0, the images may be superimposed and trimmed.
  • the trimming unit 13 is provided at the subsequent stage of the composite image generation unit 15.
  • the trimming operation was performed on the original image P0. Instead of this trimming operation, the portion where the stent marker image of the original image P0 is reflected is enlarged and displayed.
  • the composite image P2 may be displayed.
  • an image enlargement unit 17 is provided after the composite image generation unit 15.
  • the X-ray referred to in the above-described embodiments is an example of radiation in the present invention. Therefore, the present invention can be applied to radiation other than X-rays.
  • the present invention is suitable for a medical radiation imaging apparatus.

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Abstract

L'invention concerne un appareil d'imagerie radiographique permettant de générer des images combinées, des images radiographiques d'un sujet étant projetées en temps réel par superposition de trames d'images animées. Les images combinées de l'invention sont générées par superposition d'images originales ayant été alignées. Ledit alignement est effectué en spécifiant la position d'images d'un marqueur de stent qui sont projetées ensemble dans chacune des images originales. Comme les images combinées peuvent ainsi être générées en temps réel, le praticien est en mesure d'observer des modifications au cours du temps de l'image du sujet à l'aide d'images nettes.
PCT/JP2011/002288 2011-04-19 2011-04-19 Appareil d'imagerie radiographique Ceased WO2012143971A1 (fr)

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Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015150049A (ja) * 2014-02-12 2015-08-24 株式会社島津製作所 Ｘ線撮影装置
JP2015217020A (ja) * 2014-05-15 2015-12-07 株式会社島津製作所 Ｘ線撮影装置およびｘ線画像の生成方法
JP2016120144A (ja) * 2014-12-25 2016-07-07 株式会社島津製作所 Ｘ線透視撮影装置
JP2016131618A (ja) * 2015-01-16 2016-07-25 株式会社島津製作所 放射線透視撮影装置
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JP2018175854A (ja) * 2018-03-23 2018-11-15 株式会社島津製作所 Ｘ線撮影装置
US10278667B2 (en) 2014-08-04 2019-05-07 Toshiba Medical Systems Corporation X-ray diagnostic apparatus
CN110505842A (zh) * 2017-04-13 2019-11-26 株式会社岛津制作所 X射线摄影装置

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JPH02271836A (ja) * 1989-04-13 1990-11-06 Toshiba Corp Ｘ線画像認識方法及びその表示装置
JP2000217035A (ja) * 1999-01-21 2000-08-04 Toshiba Corp Ｘ線診断装置
JP2008528165A (ja) * 2005-01-31 2008-07-31 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 電気生理学的介入においてカテーテルを誘導するシステム及び方法
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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015150049A (ja) * 2014-02-12 2015-08-24 株式会社島津製作所 Ｘ線撮影装置
JP2015217020A (ja) * 2014-05-15 2015-12-07 株式会社島津製作所 Ｘ線撮影装置およびｘ線画像の生成方法
US9801602B2 (en) 2014-08-01 2017-10-31 Toshiba Medical Systems Corporation X-ray diagnostic apparatus to identify a target in x-ray images
US10278667B2 (en) 2014-08-04 2019-05-07 Toshiba Medical Systems Corporation X-ray diagnostic apparatus
JP2016120144A (ja) * 2014-12-25 2016-07-07 株式会社島津製作所 Ｘ線透視撮影装置
JP2016131618A (ja) * 2015-01-16 2016-07-25 株式会社島津製作所 放射線透視撮影装置
CN110505842A (zh) * 2017-04-13 2019-11-26 株式会社岛津制作所 X射线摄影装置
JP2018175854A (ja) * 2018-03-23 2018-11-15 株式会社島津製作所 Ｘ線撮影装置

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