WO2001059477A1 - Tomographe a emission de positrons - Google Patents
Tomographe a emission de positrons Download PDFInfo
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- WO2001059477A1 WO2001059477A1 PCT/JP2001/000579 JP0100579W WO0159477A1 WO 2001059477 A1 WO2001059477 A1 WO 2001059477A1 JP 0100579 W JP0100579 W JP 0100579W WO 0159477 A1 WO0159477 A1 WO 0159477A1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/037—Emission tomography
Definitions
- the present invention relates to a positron emission tomography apparatus suitably used for evaluation of a test drug and the like.
- a positron emission tomography device (a positron emission tomography device, hereinafter referred to as a PET device) administers a positron-emitting labeling substance into a subject, and measures the measurement site of the subject as the electron-positron pair disappears.
- the radiation generated at the measurement site is counted simultaneously, and the spatial distribution of the radiation concentration at the measurement site is measured and imaged to investigate changes in the amount of labeling substance accumulated in a specific region of interest at the measurement site. It is being applied to the evaluation of drugs for Alzheimer's type or vascular dementia.
- FIG. 10 is a block diagram showing a configuration of a conventional PET device.
- the PET device 100 includes a detecting unit 101, a data collecting unit 102, an image reconstructing unit 103, and an intravenous injection unit 104.
- the data collection unit 102 includes a frame-dependent histogram count memory 105.
- the labeling substance T is injected intravenously into the subject S (for example, a monkey) by the intravenous injection section 104.
- the measurement site H for example, the head
- radiation emitted from the labeling substance T that has reached the head of the subject S is detected by the detection unit 1.
- the coincidence is counted by 01, and the coincidence data is transmitted to the data collection unit 102.
- the transmitted coincidence count data is stored in the frame-dependent histogram count memory 105, and is added according to the imaging frame.
- the added data is sent to the image reconstructing unit 103, and based on this, the data is sent to the measurement site H of the subject S.
- the radiation concentration distribution is imaged.
- the test drug Y is administered to the subject S after the labeling substance ⁇ is administered. Then, by performing a numerical analysis of the radiation concentration obtained as described above based on the physiological constants and the like specific to the subject S, the labeling substance T before and after administration of the test drug Y in the region of interest at the measurement site H is obtained. The change of the accumulation amount of the data is derived. Disclosure of the invention
- bolus injection method a method of injecting a labeling substance by one intravenous injection.
- the S / N ratio decreases in the latter half of the measurement due to the half-life of the labeling substance. Therefore, the dosage of the labeling substance had to be set higher to compensate for this. Therefore, the exposure dose to the subject increases, and it is necessary to widen the measurement range of the radiation concentration in the PET device so that it can measure from high radiation concentration in the early stage of measurement to low radiation concentration in the latter half of the measurement. I got it.
- steady gas inhalation method a method in which gas containing a labeled substance is constantly inhaled by a subject (so-called steady gas inhalation method) may be used instead of the bolus injection method.
- This gas steady-state inhalation method aims to bring the radiation concentration in the subject to a steady state.
- the flow rate of the labeled substance is greatly affected by changes in the physiological state of the subject (particularly the respiratory volume). It was difficult to do. As a result, the measured radiation concentration contained many errors, and the accuracy of the experiment could not be guaranteed.
- the state of the biological function of the subject during the experiment for example, the radiation concentration in blood. Therefore, during or after the experiment, arterial blood is collected from the subject, and this arterial blood is analyzed to derive a physiological constant indicating the state in the subject during the experiment. It had been.
- the present invention has been made in view of the above-described problems, and can perform accurate and simple measurement, and can quickly and easily grasp a measurement result. PET device).
- the positron emission tomography apparatus is configured to administer a positron-emitting labeling substance into a subject, and to generate radiation generated at a measurement site of the subject due to annihilation of electron-positron pairs.
- Area of interest data that extracts radiation data of a specific area of interest from the radiation data that is simultaneously counted from the area to be measured by a PET device that measures the spatial distribution of radiation concentration at the area to be measured by simultaneous counting Means, an administration condition calculating means for calculating an optimal administration condition of the labeling substance into the subject based on the extracted radiation data of the region of interest, and a label on the subject based on the optimal administration condition.
- Administration control means for performing feedback control of the administration conditions of the substance.
- the optimal administration conditions of the labeling substance are set based on this radiation data so that the radiation concentration in the region of interest becomes constant regardless of the physiological condition (blood flow, etc.) of the subject ( The dose per unit time, etc.) is calculated, and the feedback of the dose of the labeling substance to the subject, etc., is performed so as to meet this optimal dosing condition.
- feed-knock control is performed so that the radiation concentration in the region of interest is steady instead of the radiation concentration in the entire measurement site, it is not necessary to extend the measurement range of the radiation concentration in the PET device.
- FIG. 1 is a block diagram showing a configuration of the PET device according to the first embodiment.
- FIG. 2 is a flowchart illustrating a region-of-interest data extraction process, an administration speed calculation process, and an administration speed control process in the PET device according to the first embodiment.
- FIG. 3 is a schematic diagram for explaining extraction of radiation data of a region of interest in the PET device according to the first embodiment.
- FIG. 4 is a detailed flowchart for explaining an administration speed calculation process in the PET device according to the first embodiment.
- FIG. 5 is a graph showing a time change of the radiation concentration in the region of interest in the PET device according to the first embodiment.
- FIG. 6 is a flowchart illustrating a region of interest data extraction process and an administration speed control process in the PET device according to the second embodiment.
- FIG. 7 is a schematic diagram for explaining extraction of a radiation image of a region of interest in the PET device according to the second embodiment.
- FIG. 8 is a diagram illustrating a region of interest data extraction processing and processing performed by the PET apparatus according to the third embodiment. It is a flowchart explaining a dosing speed control process.
- FIG. 9 is a schematic diagram for explaining calculation of a contribution ratio of a detector pair in the PET device according to the third embodiment.
- FIG. 10 is a block diagram showing a configuration of a conventional PET device.
- PET apparatus positron emission tomography apparatus
- FIG. 1 is a block diagram of the PET device 1 according to the first embodiment.
- the PET device 1 includes a detection unit 10, a data collection unit 20, an image information control unit 30, an intravenous injection unit 40, a calculation processing unit 50, It comprises an administration rate control section 60 and a display section 70.
- the detection unit 10 includes a measurement space in which a measurement site (for example, a head) H of a subject (for example, a monkey) S can be placed, and a large number of detectors are arranged in a ring around a central axis. ing. In these detectors, the light receiving surface is directed in the direction of the measurement space, and detects radiation incident from the measurement space side.
- a measurement site for example, a head
- a subject for example, a monkey
- Each detector of the detection unit 10 and the data collection unit 20 are connected by a signal line, and a detection signal corresponding to the energy of the detected radiation is transmitted from the detector to the data collection unit 20.
- the data collection unit 20 includes an imaging frame dependent histogram memory 21 and an imaging frame independent histogram memory 22.
- the data collection unit 20 detects the radiation (energy of 511 keV) generated by the annihilation of the electron and positron pairs by one of the detectors constituting the detection unit 10. This is recognized based on the detection signal transmitted from the detection unit 10, and coincidence counting data based on each detection signal is stored in the imaging frame dependent histogram memory 21 and the imaging frame independent histogram memory 22.
- the image-frame-dependent histogram memory 21 is connected by a signal line of the image information controller 30.
- the imaging frame-independent histogram memory 22 is connected to the calculation processing unit 50 by a signal line.
- the data stored and added to the imaging frame-dependent histogram memory 21 are transmitted to the image information control unit 30 in accordance with a preset imaging frame (a period during which the data collection is divided).
- the image information control section 30 includes an image information memory 31.
- the image information memory 31 stores information such as a mask image created in advance before the start of measurement.
- the image information control unit 30 is connected to the calculation processing unit 50 by a signal line, and the image information and the like stored in the image information memory 31 are transmitted to the calculation processing unit 50 according to the imaging frame and the like. Is done.
- the intravenous injection unit 40 includes an injection needle for intravenous injection into the subject S, a pump for injecting the labeling substance T into the subject S, and the like. During the measurement period, the state in which the injection needle is inserted into the subject S is maintained, and the labeling substance T is continuously administered by the pump. Further, this pump has a structure capable of changing the intravenous injection speed of the labeling substance T under the control of the administration rate control section 60 which is the administration control means.
- the calculation processing unit 50 determines a specific The radiation data of the region of interest K is extracted, and the radiation concentration of the region of interest K and the optimal administration rate (iv injection amount per unit time) are calculated.
- the calculation processing unit 50 is connected to the administration rate control unit 60 and the display unit 70 by a signal line, and the calculated radiation concentration of the region of interest K is transmitted to the display unit 70 for calculation.
- the optimal administration speed is transmitted to the administration speed controller 60.
- the administration speed control unit 60 is connected to the intravenous injection unit 40 via a signal line, and controls the administration speed of the intravenous injection unit 40 based on the transmitted optimal administration speed information.
- the display unit 70 is, for example, a liquid crystal monitor or the like, and displays the transmitted radiation concentration of the region of interest K by a graph or the like. Subsequently, the operation of the PET apparatus 1 according to the present embodiment will be described with reference to the flowchart shown in FIG. 2, the region of interest data extraction processing, the administration rate calculation processing (administration condition calculation processing), and the administration rate control processing ( The administration control process will be mainly described.
- an MRI anatomical image of the measurement site H of the subject S measured in advance is input to the image information memory 31 of the image information control unit 30 (step 1— 1, hereafter abbreviated as S1-1).
- a region of interest K is set on this image (S1-2).
- the region of interest K is a site where the accumulation amount of the labeling substance T changes by the administration of the test drug Y, and is appropriately selected depending on the type and purpose of the test drug Y.
- a mask image that leaves only the data of the region of interest K is created based on the set image (S1-3).
- 1 is set in the region of interest K
- 0 is set in regions other than the region of interest K.
- the mask image and the PET image are aligned (S1-4).
- Target part H of the subject S is inserted into the measurement space of the detection unit 1 0, labeled substance T into the subject S (e.g., a compound containing positron emission of 15 0, etc.) administration is started. Then, the radiation generated from the measurement site H due to the annihilation of the electron * positron pair is counted simultaneously, and the same clock data is collected in the imaging frame dependent histogram memory 21 and the imaging frame independent histogram memory 22. (S 1 — 1 1). The coincidence count data is repeatedly collected until one frame ends, and the coincidence count data is stored in the imaging frame dependent histogram memory 21 and the imaging frame independent histogram memory 22.
- the added coincidence data is transmitted to the calculation processing unit 50, and a PET image (radiation data image) of the measurement site H is reconstructed based on the coincidence data. (S 1-1 2).
- the mask image registered in advance is transmitted to the calculation processing unit 50.
- the reconstructed PET image and the mask image are combined (S1-13).
- a PET image of the region of interest K that is, an image showing the radiation density distribution in the region of interest
- the calculation processing unit 50 derives PET data (radiation concentration data) of the region of interest K based on the extracted PET image of the region of interest K (S1-14).
- the PET data of the region of interest K is transmitted to the display unit 70 and displayed as a graph or the like.
- the calculation processing section 50 calculates an optimal administration rate such that the radiation concentration in the region of interest K becomes steady based on the PET data of the region of interest K (S1-15).
- the deviation between the previously created graph of the reference input function and the graph based on the calculated PET data is calculated (S 1-24).
- an optimal administration rate of the labeling substance T that corrects this deviation is calculated (S1-25). Note that the graph of the PET data obtained in this frame may be replaced with a graph of the reference input function created in advance and used as a graph of the reference input function in the next frame.
- the administration rate control unit 60 determines that the administration rate (administration condition) of the labeling substance T in the intravenous injection unit 40 is the optimal administration rate. (S1-16). When such a series of processing is completed, the measurement proceeds to the next frame. Next frame In the measurement of the team, the intravenous unit 40 administers the labeling substance T to the subject S at the calculated optimal administration rate.
- the test drug Y is administered to the subject S. Then, the test drug Y is evaluated by observing the change in the radiation concentration generated from the region of interest K (that is, the change in the amount of accumulation of the labeling substance T).
- FIG. 5 is a graph showing a time change of the radiation concentration in the region of interest in the PET device according to the present embodiment, and such a graph can be visually recognized on the display unit 70 in real time. As shown in the figure, the temporal change of the radiation concentration generated from the region of interest K is roughly divided into three periods.
- the first period P1 is a stage in which the radiation concentration in the region of interest K has not yet stabilized and depends on blood flow and the like.
- the second period P2 is a stage in which the radiation concentration in the region of interest K has reached a steady state due to the feedback control of the administration rate of the labeling substance T.
- the third period P3 is a stage in which the administration of the test drug Y has caused a change in the radiation concentration in the critical region K, which was in a steady state.
- the effect of the test drug Y is evaluated by examining the change in the radiation concentration in the region of interest K during the period P3.
- the radiation concentration of the region of interest K derived from the coincidence count data is extracted.
- the optimal administration rate is calculated as the optimal administration condition of the labeling substance such that the radiation concentration in the region of interest K becomes constant regardless of the physiological condition (blood flow, etc.) of the subject S. Then, based on the calculated optimal administration rate, the administration rate of the labeling substance T to the subject S is feedback-controlled.
- the extracted radiation concentration data is displayed in real time on the display unit 70 as a graph or the like. Therefore, it is possible to easily visually recognize a change in the radiation concentration or the like in the region of interest K in real time, and it is possible to quickly determine a measurement result or the like.
- the PET device 1 it is possible to increase the extraction accuracy by extracting the radiation data of the region of interest as an image, and to extract the radiation data as a radiation concentration instead of the clock signal. can do.
- a graph of the reference input function is created in advance, and the rate of application of the labeling substance T is calculated so as to correct the deviation from the graph of the reference input function. . Therefore, it is necessary to perform complicated calculations and analyzes not only when performing multiple measurements on the same subject but also when measuring multiple subjects (that is, subjects with different physiological constants). Disappears.
- PET apparatus positron emission tomography apparatus
- a previously measured MRI anatomical image or the like of the measurement site H of the subject S is stored in the image information control unit 30. Is input to the memory 31 (S2-1), and then a region of interest K is set on this image (S2-2) o
- a mask image that leaves only the data of the region of interest K is created based on the set image (S2-3), and the mask image and the PET image are aligned (S2-4). . Thereafter, in the present embodiment, this mask image is forward projected onto the projection data, and a projection mask is created (S2-5).
- the measurement site H of the subject S is inserted into the measurement space of the detection unit 10, and administration of the labeling substance T to the subject S is started. Then, radiation generated from the measurement site is counted simultaneously, and the coincidence data is collected in the imaging frame dependent histogram memory 21 and the imaging frame independent histogram memory 22 (S2-11). The coincidence counting data is repeatedly collected until one frame is completed, and the coincidence counting data is accumulated in the imaging frame dependent histogram memory 21 and the imaging frame independent histogram memory 22.
- the added coincidence count data is transmitted to the calculation processing unit 50, and this data is forward projected onto the projection data (S2_12).
- the projection mask pre-aligned from the image information control unit 30 is transmitted on the projection data of the calculation processing unit 50.
- the calculation processing unit 50 combines the projected PET data (projected radiation data) and the projection mask (S213). By this combination, for example, as shown in FIG. 7, a projected PET image of the region of interest K is extracted.
- the calculation processing unit 50 derives the PET data of the region of interest K based on the extracted projected PET data of the region of interest K (S2-14).
- the PET data of the region of interest K is transmitted to the display unit 70 and displayed as a graph or the like.
- the calculation processing unit 50 calculates an optimal administration rate such that the radiation concentration in the region of interest K becomes steady based on the PET data of the region of interest K, as in the first embodiment. (S2-15). Thereafter, information on the calculated optimal administration rate is transmitted to the administration rate control unit 60, and the administration rate control unit 60 adjusts the administration rate of the labeling substance T in the intravenous injection unit 40 to this optimal administration rate. Feedback control is performed so as to achieve (S2-16). When such a series of processing is completed, the measurement proceeds to the next frame. During the measurement in the next frame, the intravenous unit 40 administers the labeling substance T to the subject S at the calculated optimal administration rate.
- the PET device 2 since the projection radiation data of the region of interest K and the projection mask are combined on the projection data, it is possible to improve the time resolution.
- PET apparatus positron emission tomography apparatus
- a preliminary PET measurement relating to the measurement site H of the subject S is performed in advance (S3_l). Then, a PET image is reconstructed based on the PET data obtained by the preliminary PET measurement (S3-2).
- an MRI anatomical image or the like of the measurement site H of the subject S measured in advance is input to the image information memory 31 of the image information control unit 30.
- a region of interest K is set above (S3-3).
- a mask image that leaves only the data of the region of interest K is created based on the set image (S3-4), and the mask image and the preliminary PET image are combined (S3-5).
- the contribution rate to each detector pair is calculated from the region of interest K based on the synthesized image (S3_6).
- This contribution ratio indicates the contribution ratio of the radiation generated from the region of interest K to the same clock value detected by each detector pair.
- the distance between the line connecting the detector pairs across the region of interest K is a value between 0 and 1 for each detector pair based on the radiation concentration distribution etc. obtained from the preliminary PET image. Is set to Then, a contribution ratio table summarizing the contribution ratio for each detector pair is created (S3-7).
- the measurement site H of the subject S is inserted into the measurement space of the detection unit 10, and administration of the labeling substance T to the subject S is started. Then, the radiation generated from the measurement site is counted simultaneously (S3-1-1) o
- the obtained coincidence count data is transmitted to the calculation processing unit 50 in a time-series manner, not for each frame. You. In the calculation processing unit 50, the detector pair that has detected the coincidence counting data is specified (S3-12).
- each coincidence data is weighted (S3-13). For example, if detected by a detector pair with a contribution of 0.7 (70%), a coincidence of 1 will be reduced to 0.7. Note that a contribution ratio table including the coincidence count data obtained at this time may be newly created and used in the next weighting processing of the coincidence count data.
- the calculation processing unit 50 extracts PET data of the region of interest K based on the coincidence data weighted as described above (S3-14).
- the PET data of the region of interest K is transmitted to the display unit 70 and displayed as a graph or the like. Further, the calculation processing unit 50 calculates an optimal administration rate such that the radiation concentration in the region of interest K becomes steady based on the PET data of the region of interest K, as in the first embodiment.
- the administration rate control unit 60 adjusts the administration rate of the labeling substance T in the intravenous injection unit 40 to the optimal administration rate.
- Perform feedback control S2-16.
- PET imaging proceeds to the next frame when one frame is completed. Only however, since the calculation and control of the optimum administration rate are appropriately performed without depending on the frame, the intravenous unit 40 administers the labeling substance T to the subject S at the optimum administration rate each time.
- the PET device 3 since time-series data based on each detector pair is used, it is possible to extract radiation data of the region of interest K having a very high time resolution. .
- the positron emission tomography apparatus (PET apparatus) is not limited to the above embodiment, and can take various modifications in accordance with other conditions and the like.
- the function of the region-of-interest data extracting means for extracting the radiation data of the region of interest K and the function of the administration condition calculating means for calculating the optimal administration condition are represented by a single calculation process. This is realized by part 50.
- the positron emission tomography apparatus (PET apparatus) according to the present invention can perform accurate and simple measurement, and can quickly and easily grasp the measurement result. It can be used as a positron emission tomography device.
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU2001228845A AU2001228845A1 (en) | 2000-02-07 | 2001-01-29 | Positron emission tomograph |
EP01951111A EP1256817B1 (en) | 2000-02-07 | 2001-01-29 | Positron emission tomograph |
DE60115848T DE60115848T2 (de) | 2000-02-07 | 2001-01-29 | Positronen emittierender tomograph |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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JP2000-29238 | 2000-02-07 | ||
JP2000029238A JP4408162B2 (ja) | 2000-02-07 | 2000-02-07 | ポジトロンエミッショントモグラフィ装置 |
Publications (1)
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WO2001059477A1 true WO2001059477A1 (fr) | 2001-08-16 |
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Application Number | Title | Priority Date | Filing Date |
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PCT/JP2001/000579 WO2001059477A1 (fr) | 2000-02-07 | 2001-01-29 | Tomographe a emission de positrons |
Country Status (6)
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US (1) | US7191109B2 (ja) |
EP (1) | EP1256817B1 (ja) |
JP (1) | JP4408162B2 (ja) |
AU (1) | AU2001228845A1 (ja) |
DE (1) | DE60115848T2 (ja) |
WO (1) | WO2001059477A1 (ja) |
Cited By (1)
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CN113925523A (zh) * | 2020-06-29 | 2022-01-14 | 通用电气精准医疗有限责任公司 | 医疗成像系统的状态检测方法和装置以及ct成像系统检测 |
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DE10214254A1 (de) * | 2002-03-30 | 2003-10-16 | Philips Intellectual Property | Organspezifische Rückprojektion |
WO2005044311A2 (en) * | 2003-11-11 | 2005-05-19 | Philips Intellectual Property & Standards Gmbh | Device and method for determining the concentration of a tracer in blood |
JP2005197792A (ja) * | 2003-12-26 | 2005-07-21 | Canon Inc | 画像処理方法、画像処理装置、プログラム、記憶媒体及び画像処理システム |
DE102005048853A1 (de) * | 2005-10-12 | 2007-04-26 | Siemens Ag | Bildgebende medizinische Modalität |
EP1949136A1 (en) * | 2005-11-10 | 2008-07-30 | Koninklijke Philips Electronics N.V. | Pet imaging using anatomic list mode mask |
DE102005053994A1 (de) * | 2005-11-10 | 2007-05-24 | Siemens Ag | Diagnosevorrichtung für kombinierte und/oder kombinierbare radiographische und nuklearmedizinische Untersuchungen sowie entsprechendes Diagnoseverfahren |
KR101121926B1 (ko) * | 2006-03-10 | 2012-03-20 | 가부시키가이샤 시마즈세이사쿠쇼 | 핵의학 진단장치 및 그것에 이용되는 진단시스템 |
GB2450073B (en) | 2006-08-25 | 2009-11-04 | Siemens Molecular Imaging Ltd | Regional reconstruction of spatially distributed functions |
DE102006042572A1 (de) * | 2006-09-11 | 2008-03-27 | Siemens Ag | Bildgebende medizinische Einheit |
DE102008019645A1 (de) | 2008-04-18 | 2009-10-22 | Siemens Aktiengesellschaft | Positronenemissionstomographie-Gerät |
DE102010020605A1 (de) | 2010-05-14 | 2011-11-17 | Siemens Aktiengesellschaft | Medizinische Untersuchungseinrichtung zur CT-Bildgebung und zur nuklearmedizinischen Bildgebung |
CN103279964B (zh) * | 2013-04-23 | 2015-10-28 | 浙江大学 | 一种基于prca的pet图像动态重建方法及系统 |
JP6433681B2 (ja) * | 2014-05-15 | 2018-12-05 | 浜松ホトニクス株式会社 | 薬物評価システム、薬物評価システムの作動方法、薬物評価プログラム及び記録媒体 |
DE102014219196A1 (de) * | 2014-09-23 | 2016-01-14 | Siemens Aktiengesellschaft | Verfahren und Vorrichtung zur Gewinnung zweier Bilder mittels zweier unterschiedlicher medizinischer Bildgebungsverfahren |
US10733770B2 (en) * | 2017-04-21 | 2020-08-04 | General Electric Company | System and method for performing fault-tolerant reconstruction of an image |
CN109350099A (zh) * | 2018-09-13 | 2019-02-19 | 中山市明峰医疗器械有限公司 | 一种应用于临床pet系统的随机事件去除处理方法 |
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- 2000-02-07 JP JP2000029238A patent/JP4408162B2/ja not_active Expired - Fee Related
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- 2001-01-29 AU AU2001228845A patent/AU2001228845A1/en not_active Abandoned
- 2001-01-29 EP EP01951111A patent/EP1256817B1/en not_active Expired - Lifetime
- 2001-01-29 US US10/203,161 patent/US7191109B2/en not_active Expired - Fee Related
- 2001-01-29 WO PCT/JP2001/000579 patent/WO2001059477A1/ja active IP Right Grant
- 2001-01-29 DE DE60115848T patent/DE60115848T2/de not_active Expired - Lifetime
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CN113925523A (zh) * | 2020-06-29 | 2022-01-14 | 通用电气精准医疗有限责任公司 | 医疗成像系统的状态检测方法和装置以及ct成像系统检测 |
CN113925523B (zh) * | 2020-06-29 | 2024-03-26 | 通用电气精准医疗有限责任公司 | 医疗成像系统的状态检测方法和装置以及ct成像系统检测 |
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Publication number | Publication date |
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EP1256817A1 (en) | 2002-11-13 |
JP2001221861A (ja) | 2001-08-17 |
DE60115848T2 (de) | 2006-06-14 |
EP1256817A4 (en) | 2003-05-21 |
EP1256817B1 (en) | 2005-12-14 |
US20030014132A1 (en) | 2003-01-16 |
AU2001228845A1 (en) | 2001-08-20 |
JP4408162B2 (ja) | 2010-02-03 |
US7191109B2 (en) | 2007-03-13 |
DE60115848D1 (de) | 2006-01-19 |
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