WO2012168972A1 - 放射線断層撮影装置 - Google Patents
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- WO2012168972A1 WO2012168972A1 PCT/JP2011/003228 JP2011003228W WO2012168972A1 WO 2012168972 A1 WO2012168972 A1 WO 2012168972A1 JP 2011003228 W JP2011003228 W JP 2011003228W WO 2012168972 A1 WO2012168972 A1 WO 2012168972A1
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Definitions
- the present invention relates to a radiation tomography apparatus that detects annihilation radiation emitted from a subject and images a radiopharmaceutical distribution in the subject, and more particularly to a radiation tomography apparatus for cancer screening.
- a radiation tomography apparatus for imaging the distribution of a radiopharmaceutical is provided.
- a specific configuration of such a radiation tomography apparatus will be described.
- a conventional radiation tomography apparatus includes a detector ring in which radiation detectors that detect radiation are arranged in an annular shape. This detector ring detects a pair of radiations (annihilation radiation pairs) in opposite directions that are irradiated from the radiopharmaceutical in the subject.
- FIG. 8 is a diagram illustrating a conventional radiographic apparatus for breast examination.
- the conventional radiation imaging apparatus 51 for breast examination one side of the subject's breast is introduced into the detector ring 62 during the examination. In this state, the detector ring 62 detects the annihilation radiation pair irradiated from the subject.
- the detector ring 62 identifies the source of the annihilation radiation pair emitted from the breast, and a radiopharmaceutical distribution is generated based on this position information. Radiopharmaceuticals have the property of accumulating more in cancer tissues than in normal tissues. Therefore, if a radiopharmaceutical distribution map is diagnosed, breast cancer can be screened.
- ⁇ Describe specific diagnostic methods. First, the subject's breast is set in a radiation tomography apparatus. Then, detection of an annihilation radiation pair is started. The detection of annihilation radiation pairs continues until a sufficient number of annihilation radiations are detected to generate an image. When the number of annihilation radiation detections becomes sufficient, the detection of annihilation radiation pairs is completed, and a tomographic image in which the breast of the subject is captured is generated based on the accumulated detection data.
- the conventional radiographic apparatus has the following problems. That is, according to the radiation imaging apparatus of the conventional configuration, there is a problem that it is not known what kind of tomographic image can be acquired unless the detection of the annihilation radiation pair is completed.
- the shape is not uniquely determined when introduced into the detector ring 62.
- a tomographic image may be captured in a state where the breast is not well accommodated inside the detector ring.
- the generated tomographic image is one in which the breast wall side of the breast is not reflected. End up. This means that when a portion on the chest wall side of the breast is a region of interest for diagnosis, a tomographic image in which the region of interest is not reflected in the imaging field of view may be generated.
- the present invention has been made in view of such circumstances, and an object of the present invention is to display a radiation tomography that can suppress useless imaging time by displaying a state of an image being captured even during diagnosis. It is to provide a photographing apparatus.
- the radiation tomography apparatus maps a detector ring in which radiation detectors for detecting radiation are arranged in an annular shape, and a generation source of an annihilation radiation pair based on detection data from the detector ring.
- preview image generation means for generating a preview image during photographing.
- the surgeon can know how the subject is reflected in the radiation tomography apparatus even during imaging by the preview image. If the position of the subject in the field of view is not suitable for diagnosis, the surgeon can instruct the user to stop imaging and resume imaging through the input means.
- photography can be interrupted without waiting for a clear diagnostic image being produced
- more accurate diagnosis is possible, and even if re-imaging is performed, the added imaging time is short, and a radiation tomography apparatus that can reduce the burden on the subject can be provided.
- the diagnostic image generation unit generates a diagnostic image using detection data used by the preview image generation unit for generating the preview image.
- the diagnostic image generation unit generates a diagnostic image for diagnosis using also the detection data used by the preview image generation unit to generate the preview image.
- the diagnostic image generation unit since the number of detection data points when generating a diagnostic image can be increased as much as possible, a radiation tomography apparatus capable of generating a clearer diagnostic image can be provided.
- the preview image generation unit generates a preview image by mapping the generation source of the annihilation radiation pair detected during the image generation target time, and the preview image generation unit generates the image. It is more desirable to generate preview images one after another for each target time.
- the preview image is updated every image generation target time.
- the operator can sequentially confirm how the subject is currently reflected in the field of view of the radiation tomography apparatus, so that the imaging range can be confirmed at an early stage.
- the image generation target time when the preview image generation means operates is 1 second or more and 1 minute or less.
- the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. That is, if the image generation target time is 1 second or more and 1 minute or less, a radiation tomography apparatus that can balance the processing capability of image generation and the convenience of the operator can be provided.
- the preview image generation means generates a preview image from the detection data by a statistical reconstruction method, and the number of subsets as parameters in the statistical reconstruction method is 2 or more and 600 or less, and It is more desirable that the number of iterations indicating iteration is 1 or more and 16 or less.
- the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the number of subsets, which is a parameter in the statistical reconstruction method performed by the preview image generation means, is 2 or more and 600 or less, and the iteration number is a value of 1 or more and 16, the image generation processing capability and the operator A radiation tomography apparatus that can balance the convenience of the above can be provided.
- the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention. If the configuration is provided with a marker for attaching the subject, the operator can easily know the position of the subject in the field of view of the radiation tomography apparatus simply by checking how the marker is reflected in the preview image. Can do.
- the above-described configuration shows a more specific configuration of the radiation tomography apparatus of the present invention.
- the breast has flexibility and is not uniquely defined in shape.
- breast screening uses a method in which only a part of the subject is introduced into the detector ring to acquire a tomographic image, so there is a possibility that the subject's breast is not properly introduced into the radiation tomography apparatus. It becomes higher than the radiation tomography apparatus of the type that introduces the whole body into the detector ring. Therefore, if the configuration of the present invention is adopted in a radiation tomography apparatus for breast examination, breast imaging can be performed appropriately and with high efficiency.
- preview image generation means for generating a preview image during shooting.
- the surgeon can know how the subject is reflected in the radiation tomography apparatus even during imaging by the preview image. If the position of the subject in the field of view is not suitable for diagnosis, the operator can stop detecting the radiation of the detector ring through the input means. Accordingly, the imaging can be interrupted without waiting for a clear diagnostic image to be generated to the level used for diagnosis, and the diagnostic image can be captured again after the subject is aligned. As a result, more accurate diagnosis is possible, and even if re-imaging is performed, the added imaging time is short, and a radiation tomography apparatus that can reduce the burden on the subject can be provided.
- FIG. 1 is a functional block diagram illustrating a configuration of a radiation tomography apparatus according to Embodiment 1.
- FIG. 1 is a perspective view illustrating a radiation detector according to Embodiment 1.
- FIG. 3 is a schematic diagram illustrating LOR according to the first embodiment.
- 6 is a schematic diagram illustrating the number of subsets according to Embodiment 1.
- FIG. 6 is a schematic diagram illustrating an MIP image according to Embodiment 1.
- FIG. 6 is a flowchart for explaining the operation of the radiation imaging apparatus according to the first embodiment. It is a schematic diagram explaining the marker which concerns on 1 modification of this invention. It is a schematic diagram explaining the structure of the radiation tomography apparatus of a conventional structure.
- the gamma rays in Example 1 are an example of the radiation of the present invention.
- the configuration of the first embodiment is a mammography apparatus for breast examination.
- FIG. 1 is a functional block diagram illustrating a specific configuration of the radiation tomography apparatus according to the first embodiment.
- the radiation tomography apparatus 9 according to the first embodiment includes a gantry 11 that introduces the breast B of the subject M from the z direction, and a ring shape that introduces the breast B of the subject M provided inside the gantry 11 from the z direction.
- the inner hole provided in the detector ring 12 has a cylindrical shape (exactly an octagonal prism) extending in the z direction. Therefore, the detector ring 12 itself extends in the z direction. Note that the area of the inner hole of the detector ring 12 is an imaging field of view in which a tomographic image Pb of the radiation tomography apparatus 9 can be generated.
- the z direction is along the direction in which the central axis of the detector ring 12 extends.
- the shielding plate 13 is made of tungsten or lead. Since the radiopharmaceutical is also present in a portion other than the breast B of the subject M, an annihilation ⁇ -ray pair is also generated therefrom. However, when an annihilation gamma ray pair generated from a region other than such a region of interest enters the detector ring 12, it interferes with tomographic imaging. Therefore, a ring-shaped shielding plate 13 is provided so as to cover one end of the detector ring 12 on the side close to the subject M in the z direction.
- the clock 19 sends time information that is a serial number to the detector ring 12.
- the detection data output from the detector ring 12 is given time information indicating when the ⁇ -ray is detected, and is input to the filter unit 20 described later.
- the configuration of the detector ring 12 will be described.
- the detector ring 12 is formed by arranging eight radiation detectors 1 in a virtual circle on a plane perpendicular to the z direction (center axis direction) to form one unit ring. Three unit rings are arranged in the z direction to form a detector ring 12.
- FIG. 2 is a perspective view illustrating the configuration of the radiation detector according to the first embodiment.
- the radiation detector 1 includes a scintillator 2 that converts radiation into light, and a photodetector 3 that includes a photomultiplier tube that detects light.
- a light guide 4 for transmitting and receiving light is provided at a position where the scintillator 2 and the photodetector 3 are interposed.
- the scintillator 2 is configured by arranging scintillator crystals three-dimensionally.
- the scintillator crystal is composed of Lu 2 (1-X) Y 2X SiO 5 (hereinafter referred to as LYSO ) in which Ce is diffused.
- the light detector 3 can specify the light generation position of which scintillator crystal emits light, and also specifies the light intensity and the time when the light is generated. Can do.
- the scintillator 2 having the configuration of the first embodiment is merely an example of an aspect that can be adopted. Therefore, the configuration of the present invention is not limited to this.
- Detected data output from the detector ring 12 is sent to the coincidence counting unit 21 (see FIG. 1) via a filter unit 20 described later.
- the two gamma rays simultaneously incident on the detector ring 12 are annihilation gamma ray pairs caused by the radiopharmaceutical in the subject.
- the coincidence counting unit 21 counts the number of times that an annihilation ⁇ -ray pair is detected for every two combinations of scintillator crystals constituting the detector ring 12, and sends the result to the tomographic image generating unit 22b.
- the positional relationship of the scintillator crystals in the coincidence count indicates the position where the annihilation ⁇ -ray pair is incident on the detector ring 12 and the direction in which the annihilation ⁇ -ray pair is incident.
- the number of annihilation ⁇ -ray pairs detected and the energy intensity of annihilation ⁇ -rays stored for each combination of scintillator crystals indicates the variation in the generation of annihilation ⁇ -ray pairs in the subject, and is necessary for mapping radiopharmaceuticals.
- Information The coincidence of the detected data by the coincidence counting unit 21 uses time information given to the detected data by the clock 19.
- the filter unit 20 is provided for the purpose of not sending unnecessary data in the detector ring 12 to the coincidence counting unit 21. Since the coincidence counting unit 21 has to handle a large amount of data, it is likely to be loaded.
- the filter unit 20 can thin out the detection data so as to reduce the load on the coincidence counting unit 21. For example, when the subject M is not inserted into the detector ring 12 or the detection data of scattered radiation components having a small ⁇ -ray intensity are all discarded by the filter unit 20 and are not input to the coincidence unit 21.
- a data set group in which the position data of the line connecting the scintillator crystals output from the filter unit 20, the data related to the fluorescence detection intensity, and the data related to the detection time are related to each other is called list data.
- the preview image generator 22a plays an important role in the present invention.
- the preview image generation unit 22a will be described.
- the preview image generation unit 22a receives the list data from the filter unit 20, and sequentially generates a preview image indicating the position of the subject's breast B in the imaging range of the tomographic image Pb from the list data.
- This preview image is an image in which the source of the annihilation gamma ray pair is mapped in the inner hole of the detector ring 12 and is not clear enough to be suitable for diagnosis, but is roughly a radiopharmaceutical in the breast B of the subject. It is enough to know the distribution.
- the preview image generation unit 22a corresponds to preview image generation means of the present invention.
- LOR Line of Response
- the vanishing points are densely concentrated at a location where the radiopharmaceutical is distributed at a high concentration in the breast B of the subject, if the distribution of the vanishing points is mapped, an image showing the distribution of the radiopharmaceutical can be acquired. become.
- the preview image generation unit 22a recognizes the inner hole of the detector ring 12 as a space divided into a three-dimensional lattice as shown on the right side of FIG. Since the inner hole of the detector ring 12 has a cylindrical shape, the space recognized by the preview image generating unit 22a is a three-dimensionally divided cylindrical space. On the right side of FIG. 3, a part of the space recognized by the preview image generation unit 22a is extracted. The preview image generating unit 22a superimposes the LOR indicated by the list data on this space. Then, on the right side of FIG. 3, the LOR crosses a plurality of divided sections.
- the preview image generation unit 22a gives a large evaluation value for each of the divided sections that includes the LOR longer, and gives a small evaluation value for the one that includes the LOR shorter. That is, since the divided section indicated by diagonal lines on the right side of FIG. 3 includes LOR longer, a large evaluation value is given. And since the division
- the preview image generation unit 22a stores the evaluation value of the divided section in association with the position of the inner hole of the detector ring 12.
- the preview image generation unit 22a calculates the evaluation values for a plurality of LORs and adds the evaluation values.
- the preview image generation unit 22a repeats such an operation, and acquires three-dimensional data in which the generation points of annihilation ⁇ -ray pairs are mapped.
- the successive approximation reconstruction method which is a statistical reconstruction method with less influence of statistical noise is used.
- a method such as list mode OSEM (Ordered Subset expectation maximization) is used. That is, when the radiopharmaceutical distribution follows a prescribed distribution such as a Poisone distribution, this is a technique for obtaining the radiopharmaceutical distribution so that the reliability is maximized. This method is performed by dividing the obtained list mode data for each preset image generation target time t, performing successive approximation reconstruction, and repeating image correction.
- the number m of the divisions represents the number of subsets.
- FIG. 4 shows list mode data.
- the number of subsets is 12.
- Data areas divided by the number of subsets are represented by S1 to S12.
- D (0.1) in the table indicates data acquired at a time point of 0.1 seconds within a certain image generation target time t. Since the image generation target time t is 5 seconds, the time when the data is acquired is in the range from 0 seconds to 5 seconds. Since the image generation target time t in the first embodiment can be changed from 1 second to 600 seconds, the number of subsets is 2 or more and 600 or less, and the iteration number is 1 or more and 16 or less.
- the number of subsets described above may be obtained by dividing the expected total count number, which is the expected value of the total count number acquired during the inspection, by the image generation count number CT, which is the count number used for image generation. .
- the preview image generation unit 22a calculates an evaluation value for each of the data areas S1 to S6. For example, when the evaluation value is calculated for the data area S1 obtained in 5 seconds from the start of data collection, the evaluation value is only for the rectangular divided section described on the right side of FIG. Is calculated. Then, when the calculation of the evaluation value on the data area S1 is completed, the preview image generation unit 22a calculates the evaluation value in the data area S12 next to the data area S2 and the data area S3.
- the number of iterations is a parameter in the OSEM method, like the number of subsets, and is the number of times to set how many times the evaluation value for the data area of the detector ring 12 is calculated.
- the number of iterations in the first embodiment is preferably set to 1 because of a request for high speed.
- the three-dimensional reconstruction data generated by the preview image generation unit 22a is converted into a MIP (maximum intensity) projection image.
- MIP maximum intensity
- the preview image generation unit 22a selects the maximum pixel value for a straight line that crosses the three-dimensional reconstruction data. Specifically, the preview image generation unit 22a selects the pixel N having the maximum luminance among the pixels included in the three-dimensional reconstruction data and existing on the straight line L indicated by diagonal lines in FIG.
- the preview image generation unit 22a arranges the pixel value of the pixel N at a position indicating a point p on a certain plane F.
- the preview image generation unit 22a repeats the same operation while moving the point p on the plane F (projection plane), and changes the straight line L each time, indicating that the largest number of extinction ⁇ -ray pairs has occurred.
- the pixel having the luminance shown) is selected.
- the straight line L is always orthogonal to the plane F while being changed.
- the pixel values of the selected pixels are successively arranged on the plane F, and an MIP image is generated on the plane F.
- This MIP image is a preview image Pa generated by the preview image generation unit 22a.
- the reason why the preview image is the MIP image will be described.
- the MIP image is an image suitable for grasping as one image how the generation sources of annihilation ⁇ -ray pairs are distributed in the entire imaging field of view of the radiation tomography apparatus 9 which is three-dimensional. Therefore, the MIP image is suitable for grasping the state of the breast B in the field of view of the radiation tomography apparatus 9.
- the radiopharmaceutical since the radiopharmaceutical has a property of being somewhat collected on the skin of the subject, the contour of the subject appears in the MIP image, and the shape of the breast B in the imaging field of view of the radiation tomography apparatus 9 is grasped. Convenient to.
- the preview image generation unit 22a generates a preview image Pa by mapping the generation source of the annihilation ⁇ -ray pairs detected during the image generation target time t.
- the image generation target time t is preferably 1 second or more and 1 minute or less, and more preferably about 10 seconds.
- the preview image generation unit 22a generates MIP images one after another at every image generation target time t.
- the tomographic image generation unit 22b generates a tomographic image Pb when the inner hole of the detector ring 12 is cut along a certain plane based on the list data output from the coincidence counting unit 21.
- This tomographic image Pb is a diagnostic image for diagnosis in which the source of the annihilation gamma ray pair is mapped.
- the tomographic image generation unit 22b generates a tomographic image Pb by a successive approximation reconstruction method. At this time, the tomographic image Pb is generated using all of the detection data output from the detector ring 12.
- the tomographic image generator 22b corresponds to the diagnostic image generator of the present invention.
- the display unit 36 displays an image generated by the preview image generation unit 22a or the tomographic image generation unit 22b, and the console 35 allows the operator to input various operations performed on the radiation tomography apparatus 9. It is.
- the storage unit 37 is referred to in the detection data output from the detector ring 12, the coincidence counting data generated by the coincidence counting unit 21, the data generated by the operation of each unit such as the preview image Pa and the tomographic image Pb, and the operation of each unit. It stores all parameters.
- the console 35 corresponds to the input means of the present invention, and the display unit 36 corresponds to the display means of the present invention.
- the radiation tomography apparatus 9 includes a main control unit 41 that controls each unit in an integrated manner.
- the main control unit 41 is constituted by a CPU, and realizes the respective units 19, 20, 21, 22, 22b and 22b by executing various programs.
- each above-mentioned part may be divided
- the breast B of the subject M is first inserted into the inner hole of the detector ring 12 as shown in FIG. Insertion step S1), the detection of annihilation ⁇ -ray pairs is started (detection start step S2). Then, display of the preview image Pa is started (preview image display start step S3), and the position of the subject is adjusted (subject position adjustment step S4). Finally, a diagnostic image is displayed on the display unit 36 (diagnostic image display step S5).
- these steps will be described in order.
- ⁇ Subject insertion step S1> A radiopharmaceutical is administered to the subject in advance, and when the distribution of the radiopharmaceutical in the body is stabilized to some extent, the breast B of the subject is inserted into the inner hole of the detector ring 12. At this time, the breast B of the subject is introduced as deep as possible into the detector ring 12 for the purpose of accommodating the entire breast as much as possible in the field of view of the radiation tomography apparatus 9.
- ⁇ Detection start step S2 preview image display start step S3>
- the detector ring 12 starts sending detection data.
- the detection data obtained at this time is sent to the preview image generation unit 22a via the filter unit 20 and the coincidence counting unit 21.
- the preview image generation unit 22a sequentially generates a preview image Pa, which is an MIP image, every image generation target time t (1 second to 1 minute).
- the generated preview image Pa is displayed on the display unit 36 one after another. In other words, the preview image generation unit 22a sequentially generates the preview images Pa whose images are updated every image generation target time t.
- the preview image generation unit 22a When the preview image generation unit 22a generates the preview image Pa, it is generated using the detection data of the annihilation ⁇ -ray pairs detected by the detector ring 12 within the image generation target time t. By comparing the preview images Pa, it is possible to sequentially confirm how the subject's breast B is reflected in the radiation tomography apparatus 9. Therefore, the preview image Pa displayed on the display unit 36 is updated every image generation target time t.
- ⁇ Subject position adjustment step S4> The surgeon confirms how the subject's breast B is stored in the detector ring 12 based on the preview image Pa.
- the detection of the annihilation ⁇ -ray pair is continued, and the tomographic image generation unit 22b is generated.
- the breast B is contained in the inner hole of the detector ring 12 shallowly, or there is an occurrence point of an annihilation gamma ray pair at the end of the field of view of the radiation tomography apparatus 9. A case where alignment is required will be described.
- the surgeon determines from the preview image Pa that the breast B needs to be aligned, the surgeon gives an instruction to stop radiation detection to the radiation tomography apparatus 9 through the console 35.
- the detector ring 12 stops detection of radiation when an instruction to stop imaging is given by the operator.
- the surgeon gives an instruction to resume imaging to the radiation tomography apparatus 9 through the console 35.
- the preview image Pa in which the breast B after the position adjustment is displayed is displayed on the display unit 36, and the surgeon can confirm whether the position adjustment of the breast B performed previously is appropriate.
- the detection data used for the tomographic image generation by the tomographic image generation unit 22b will be described.
- the shape of the breast B is different before and after alignment. Accordingly, when the tomographic image Pb is to be generated, the detection data acquired before the interruption of imaging for the purpose of alignment cannot be used for generating the tomographic image.
- the tomographic image generation unit 22b generates the tomographic image Pb using only the detection data after the alignment. That is, the diagnostic image generation unit 22b generates the tomographic image Pb using the detection data acquired after the surgeon is instructed to resume imaging. And the diagnostic image generation part 22b does not use the detection data acquired before the imaging
- the preview image generation unit 22a that generates the preview image Pa during shooting is provided.
- the surgeon can know how the subject is reflected in the radiation tomography apparatus 9 even during imaging using the preview image Pa. If the position of the subject in the field of view is not suitable for diagnosis, the operator can stop detecting the radiation of the detector ring 12 through the console 35. That is, imaging can be interrupted without waiting for a clear tomographic image Pb to be generated to the level used for diagnosis, and imaging of the tomographic image Pb can be resumed after the subject is aligned. Thereby, diagnosis with higher accuracy is possible, and even if re-imaging is performed, the added imaging time is short, and the radiation tomography apparatus 9 that can reduce the burden on the subject can be provided.
- the tomographic image generation unit 22b generates the diagnostic tomographic image Pb using the detection data used by the preview image generation unit 22a to generate the preview image Pa. In this way, since the number of detection data points when generating the tomographic image Pb can be increased as much as possible, the radiation tomography apparatus 9 capable of generating a clearer tomographic image Pb can be provided.
- the preview image Pa is updated every image generation target time t.
- the operator can sequentially confirm how the subject is currently reflected in the field of view of the radiation tomography apparatus 9, so that the tomography can be performed while monitoring the body movement of the subject. You can take a picture.
- Breast B has flexibility and its shape is not uniquely determined.
- a method for acquiring a tomographic image by introducing only a part of the subject into the detector ring 12 is adopted for the breast examination, the subject's breast B is not properly introduced into the radiation tomography apparatus 9.
- the possibility is higher than the type of radiation tomography apparatus that introduces the whole body into the detector ring. Therefore, if the configuration of the first embodiment is employed in the radiation tomography apparatus 9 for breast examination, imaging of the breast B can be performed with high efficiency.
- the present invention is not limited to the above-described configuration, and can be modified as follows.
- the preview image generation unit 22a in the above-described embodiment uses the list mode OSEM
- the preview image Pa is obtained by a statistical method using a list mode DRAMA (Dynamic Row-Action Maximum Likelihood Algorithm) instead. It may be generated.
- DRAMA Dynamic Row-Action Maximum Likelihood Algorithm
- a preview image Pa may be generated by a back projection method based on sinogram data as in the past.
- the preview image generation unit 22a in the above-described embodiment uses the MIP image as the preview image Pa
- the preview image Pa may be replaced with a two-dimensional planar image.
- the MIP image was generated by arranging pixels having the maximum luminance on the plane F on a certain straight line passing through the three-dimensional data.
- the image is generated by adding all the pixels in a certain straight line passing through the three-dimensional data and arranging the total value on the plane F.
- the distribution of the radiopharmaceutical can be expressed without being affected by noise than the MIP image.
- a diagnosis may be performed by attaching a marker to the breast B. That is, as shown in FIG. 7, a tomographic image Pb may be taken by attaching a metal marker m that absorbs radiation to the breast B before the detector ring 12 is introduced to the subject. Since the marker m is reflected in the preview image Pa, the operator can easily recognize whether or not the part of the breast B to be photographed belongs to the range of the field of view.
- a point source that emits radiation may be used as a marker instead of metal.
- the nuclide of the radioactive substance in the point source it is desirable to select one that irradiates ⁇ -rays having physical properties similar to annihilation ⁇ -ray pairs.
- the configuration is provided with the marker m for attaching the subject, the operator only has to confirm how the marker m is reflected in the preview image Pa in the field of view of the radiation tomography apparatus 9. The position of the subject can be easily known.
- the scintillator crystal referred to in each of the above embodiments is composed of LYSO.
- the scintillator crystal is composed of another material such as GSO (Gd 2 SiO 5 ) instead. Also good. According to this modification, it is possible to provide a method of manufacturing a radiation detector that can provide a cheaper radiation detector.
- the photodetector is composed of a photomultiplier tube, but the present invention is not limited to this.
- a semiconductor detector such as a photodiode, an avalanche photodiode, or a silicon photomultiplier may be used.
- the detector ring 12 is an O-shaped ring, but may be a C-shaped arc instead.
- the present invention is suitable for a medical radiation tomography apparatus.
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Abstract
Description
すなわち、従来構成における放射線撮影装置によれば、消滅放射線対の検出が終了しないとどのような断層画像が取得できるか分からないという問題点がある。
すなわち、本発明に係る放射線断層撮影装置は、放射線を検出する放射線検出器が円環状に配列された検出器リングと、検出器リングからの検出データを基に消滅放射線対の発生源がマッピングされたプレビュー画像を次々と生成するプレビュー画像生成手段と、プレビュー画像を表示する表示手段と、術者の指示を入力する入力手段と、消滅放射線対の発生源をマッピングすることにより診断用の診断画像を生成する診断画像生成手段を備え、入力手段に撮影中止および撮影再開の指示とがなされると、診断画像生成手段は、撮影再開の指示がなされる前に取得された検出データを用いないで診断画像を生成することを特徴とするものである。
次に、放射線断層撮影装置9の動作について説明する。実施例1に係る放射線断層撮影装置9を用いて被検体の診断を行うには、図6に示すように、まず被検体Mの乳房Bが検出器リング12の内穴に挿入され(被検体挿入ステップS1),消滅γ線対の検出が開始される(検出開始ステップS2)。そして、プレビュー画像Paの表示が開始され(プレビュー画像表示開始ステップS3),被検体の位置が調整される(被検体位置調整ステップS4)。最後に、診断画像が表示部36に表示される(診断画像表示ステップS5)。以降、これらの各ステップについて順を追って説明する。
被検体には予め放射性薬剤が投与され、体内の放射性薬剤の分布がある程度安定したところで、被検体の乳房Bが検出器リング12の内穴に挿入される。このとき、できるだけ乳房全体を放射線断層撮影装置9の撮影視野に収納する目的で、被検体の乳房Bは検出器リング12の奥深くまで導入される。
術者が操作卓35を通じて放射線断層撮影装置9に断層撮影開始の指示を与えると、検出器リング12は、検出データの送出を開始する。このとき得られた検出データは、フィルタ部20,同時計数部21を介してプレビュー画像生成部22aに送出される。プレビュー画像生成部22aは、MIP画像であるプレビュー画像Paを画像生成対象時間t(1秒~1分)ごとに次々と生成する。生成されたプレビュー画像Paは、次々と表示部36で表示される。すなわち、プレビュー画像生成部22aは、画像生成対象時間t毎に画像更新されたプレビュー画像Paを次々と生成する。プレビュー画像生成部22aがプレビュー画像Paを生成するときは、画像生成対象時間t内に検出器リング12が検出した消滅γ線対の検出データを用いて生成するのであるから、次々と更新されるプレビュー画像Paを比較すれば、被検体の乳房Bが放射線断層撮影装置9に写り込む様子が逐次確認できる。従って表示部36に表示されているプレビュー画像Paは、画像生成対象時間t毎に更新されることになる。
術者は、プレビュー画像Paを基に被検体の乳房Bが検出器リング12にどのように収納されているかを確認する。術者がプレビュー画像Paより被検体の乳房Bが検出器リング12に問題なく収納されているときは、消滅γ線対の検出が続行され、断層画像生成部22bが生成される。本動作説明においては、乳房Bが検出器リング12の内穴に浅く収まっていたり、放射線断層撮影装置9の撮影視野の端部に消滅γ線対の発生箇所があったりして、乳房Bの位置合わせを行う必要がある場合について説明することとする。
放射線の検出は、診断画像を生成するのに十分な点数の検出データが得られるまで続行される。検出データの点数が十分となると、検出器リング12は、放射線の検出を終了し、検出データは、断層画像生成部22bに送出される。断層画像生成部22bが生成した断層画像Pbは、表示部36に表示されて検査は終了となる。
Pa プレビュー画像
P0 診断画像
t 画像生成対象時間
CT 画像生成対象カウント数
12 検出器リング
22a プレビュー画像生成部(プレビュー画像生成手段)
22b 断層画像生成部(診断画像生成手段)
35 操作卓(入力手段)
36 表示部(表示手段)
Claims (7)
- 放射線を検出する放射線検出器が弧状に配列された検出器リングと、
前記検出器リングからの検出データを基に消滅放射線対の発生源がマッピングされたプレビュー画像を次々と生成するプレビュー画像生成手段と、
前記プレビュー画像を表示する表示手段と、
術者の指示を入力する入力手段と、
消滅放射線対の発生源をマッピングすることにより診断用の診断画像を生成する診断画像生成手段を備え、
前記入力手段に撮影中止および撮影再開の指示がなされると、前記診断画像生成手段は、撮影再開の指示がなされる前に取得された検出データを用いないで診断画像を生成することを特徴とする放射線断層撮影装置。 - 請求項1に記載の放射線断層撮影装置において、
前記診断画像生成手段は、前記プレビュー画像生成手段がプレビュー画像の生成に用いた検出データをも用いて診断画像を生成することを特徴とする放射線断層撮影装置。 - 請求項1または請求項2に記載の放射線断層撮影装置において、
前記プレビュー画像生成手段は、画像生成対象時間の間に検出された消滅放射線対の発生源をマッピングして前記プレビュー画像を生成し、
前記プレビュー画像生成手段は、前記画像生成対象時間を経時的に更新しながら前記プレビュー画像を次々と生成することを特徴とする放射線断層撮影装置。 - 請求項3に記載の放射線断層撮影装置において、
前記プレビュー画像生成手段が動作するときの前記画像生成対象時間は、1秒以上1分以下となっていることを特徴とする放射線断層撮影装置。 - 請求項1ないし請求項4のいずれかに記載の放射線断層撮影装置において、
前記プレビュー画像生成手段は、検出データから統計的再構成手法で前記プレビュー画像を生成し、
統計的再構成手法におけるパラメータであるサブセット数は、2以上600以下、かつイテレーションを示す反復回数は1以上16以下の値となっていることを特徴とする放射線断層撮影装置。 - 請求項1ないし請求項5のいずれかに記載の放射線断層撮影装置において、
放射線を吸収する被検体付設用のマーカを備えることを特徴とする放射線断層撮影装置。 - 請求項1ないし請求項6のいずれかに記載の放射線断層撮影装置において、
乳房検診用となっていることを特徴とする放射線断層撮影装置。
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JP2008185335A (ja) * | 2007-01-26 | 2008-08-14 | Kitasato Institute | 医用画像アニメーション表示装置 |
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JPWO2021186504A1 (ja) * | 2020-03-16 | 2021-09-23 | ||
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JPWO2012168972A1 (ja) | 2015-02-23 |
CN103547217B (zh) | 2015-11-25 |
US9820710B2 (en) | 2017-11-21 |
US20140119505A1 (en) | 2014-05-01 |
JP5610248B2 (ja) | 2014-10-22 |
CN103547217A (zh) | 2014-01-29 |
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