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    • 1. 发明申请
    • PET DETECTOR SCINTILLATOR ARRANGEMENT WITH LIGHT SHARING AND DEPTH OF INTERACTION ESTIMATION
    • PET检测器扫描仪安装与光共享和深度相互作用估计
    • WO2016059557A1
    • 2016-04-21
    • PCT/IB2015/057843
    • 2015-10-14
    • KONINKLIJKE PHILIPS N.V.UNIVERSITY OF WASHINGTON
    • SOWARDS-EMMERD, DavidLEHNERT, AdrienneHUNTER, WilliamMIYAOKA, RobertSHAO, LingxiongLAURENCE, Thomas Leroy
    • G01T1/164
    • G01T1/1644G01T1/2018G01T1/202
    • A photon detector includes a sensor array of optical sensors disposed in a plane and four substantially identical scintillation crystal bars. Each optical sensor is configured to sense luminescence. Each of the four scintillator crystal bars being a rectangular prism with four side surfaces and first and second end surfaces, each scintillation bar has two side surfaces which each face a side surface of another scintillation bar, and each scintillation crystal bar generating a light scintillation in response to interacting with a received gamma photon. A first layer (80) is disposed in a first plane disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (82) adjacent the first end surface and a reflective portion (84) adjacent the second end surface. A second layer (68) is disposed in a second plane orthogonal to the first plane and disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (88) adjacent the second end surface and a reflective portion (90) adjacent the first end surface.
    • 光子检测器包括设置在平面中的光学传感器的传感器阵列和四个基本相同的闪烁晶体棒。 每个光学传感器被配置为感测发光。 四个闪烁体晶体棒中的每一个是具有四个侧表面和第一和第二端表面的矩形棱镜,每个闪烁棒具有两个侧表面,每个表面面对另一个闪烁棒的侧表面,并且每个闪烁晶体棒产生闪烁 与接收的伽马光子相互作用的响应。 第一层(80)设置在设置在四个基本上相同的闪烁晶体棒的相邻的相对侧表面之间的相邻面的第一平面中,具有与第一端面相邻的光共享部分(82)和邻近第二端 端面。 第二层(68)设置在与第一平面正交的第二平面中,并且设置在四个基本上相同的闪烁晶体棒的相邻的相对的侧表面之间,并且邻近第二端面的光共享部分(88)和反射部分 (90)邻近第一端面。
    • 2. 发明公开
    • PET DETECTOR SCINTILLATOR ARRANGEMENT WITH LIGHT SHARING AND DEPTH OF INTERACTION ESTIMATION
    • PET探测器闪烁器安排与光共享和深度的交互作用估计
    • EP3207406A1
    • 2017-08-23
    • EP15784485.3
    • 2015-10-14
    • Koninklijke Philips N.V.University of Washington Through Its Center for Commercialization
    • SOWARDS-EMMERD, DavidLEHNERT, AdrienneHUNTER, WilliamMIYAOKA, RobertSHAO, LingxiongLAURENCE, Thomas Leroy
    • G01T1/164
    • A photon detector includes a sensor array of optical sensors disposed in a plane and four substantially identical scintillation crystal bars. Each optical sensor is configured to sense luminescence. Each of the four scintillator crystal bars being a rectangular prism with four side surfaces and first and second end surfaces, each scintillation bar has two side surfaces which each face a side surface of another scintillation bar, and each scintillation crystal bar generating a light scintillation in response to interacting with a received gamma photon. A first layer (80) is disposed in a first plane disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (82) adjacent the first end surface and a reflective portion (84) adjacent the second end surface. A second layer (68) is disposed in a second plane orthogonal to the first plane and disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (88) adjacent the second end surface and a reflective portion (90) adjacent the first end surface.
    • 光子检测器包括布置在平面中的光学传感器的传感器阵列和四个基本相同的闪烁晶体条。 每个光学传感器被配置为感测发光。 四个闪烁体晶体棒中的每一个是具有四个侧表面以及第一端面和第二端面的矩形棱镜,每个闪烁棒具有两个侧面,每个面都与另一个闪烁棒的侧面相对,并且每个闪烁晶体棒在 响应与接收到的伽玛光子相互作用。 第一层(80)设置在第一平面中,该第一平面设置在四个基本相同的闪烁晶体条的相对的侧表面之间并且邻近第一端表面的光共享部分(82)和邻近第二端的反射部分(84) 端面。 第二层(68)设置在与第一平面正交的第二平面中,并且设置在四个基本上相同的闪烁晶体棒之间并且与相邻的面对的侧表面相邻,具有邻近第二端面的光共享部分(88)和反射部分 (90)邻近第一端面。
    • 4. 发明申请
    • PIXEL BASED DEAD TIME CORRECTION
    • 基于PIXEL的死亡时间校正
    • WO2016097977A1
    • 2016-06-23
    • PCT/IB2015/059594
    • 2015-12-14
    • KONINKLIJKE PHILIPS N.V.
    • LAURENCE, Thomas LeroyWANG, Sharon Xiaorong
    • G01T1/17G01T1/24
    • G01T1/249G01T1/171G01T1/2985
    • A positron emission tomography (PET) apparatus and method employs a plurality of radiation detectors (20) disposed around an imaging region (16) and configured to detect 511 keV radiation events emanating from the imaging region. A calibration phantom is disposed in the imaging region. One or more processors are configured to: acquire and store listmode data of the phantom; measure a random rate for each line of response (LOR) from the listmode data using a coincident 511 keV events detector (34) with a time offset (54); determine a singles rate for each detector pixel from the random event rate, for example via a histogram plotting singles rate for each detector pixel; compute a live time factor of each LOR; compute a dead time correction factor as the reciprocal of the live time factor; and correct images according to the dead time correction factor.
    • 正电子发射断层摄影(PET)装置和方法采用设置在成像区域周围的多个辐射检测器(20),并配置成检测从成像区域发出的511keV辐射事件。 在成像区域中设置校准体模。 一个或多个处理器被配置为:获取和存储幻影的列表模式数据; 使用具有时间偏移(54)的一致的511keV事件检测器(34)从列表模式数据测量每个响应行(LOR)的随机速率; 从随机事件速率确定每个检测器像素的单打速率,例如通过对每个检测器像素绘制单个速率的直方图; 计算每个LOR的实时时间因子; 计算死区时间校正因子作为实时时间因子的倒数; 并根据死区校正因子校正图像。
    • 6. 发明申请
    • HISTOGRAM SMOOTHING IN POSITRON EMISSION TOMOGRAPHY (PET) ENERGY HISTOGRAMS
    • 立体声发射成像(PET)能量组织中的组织学扫描
    • WO2015056163A1
    • 2015-04-23
    • PCT/IB2014/065292
    • 2014-10-14
    • KONINKLIJKE PHILIPS N.V.
    • GRIESMER, Jerome JohnLAURENCE, Thomas Leroy
    • G01T1/164
    • G01T1/2985G01T1/1647
    • A medical nuclear imaging system (10) and method (100) generate smooth energy histograms. Radiation events are detected by a plurality of detectors (14), the radiation events localized to a plurality of pixels of the detectors (14). The energy levels of the detected radiation events are estimated and the estimated energy levels are scaled with scaling parameters that scale the energy centroids of the plurality of pixels to target values differing by offsets around a common target value, the target values differing with spatial location of the plurality of pixels. Target value offsets are removed from the scaled energy levels and the detected radiation events are combined into an energy histogram using the energy levels with the target value offsets removed.
    • 医学核成像系统(10)和方法(100)产生平滑的能量直方图。 辐射事件由多个检测器(14)检测,辐射事件定位于检测器(14)的多个像素。 估计检测到的辐射事件的能量水平,并且用缩放参数缩放所估计的能量水平,其中缩放参数将多个像素的能量质心缩放到围绕公共目标值的偏移量不同的目标值,目标值与 多个像素。 目标值偏移从缩放的能级移除,并且检测到的辐射事件使用去除了目标值偏移的能级合并成能量直方图。
    • 8. 发明申请
    • PET DETECTOR TIMING CALIBRATION
    • PET检测器时序校准
    • WO2016067150A1
    • 2016-05-06
    • PCT/IB2015/057922
    • 2015-10-15
    • KONINKLIJKE PHILIPS N.V.
    • YE, JinghanSONG, XiyunLAURENCE, Thomas LeroyWANG, Sharon Xiaorong
    • G01T1/29
    • A61B6/583A61B6/037A61B6/4266G01T1/2985
    • A diagnostic imaging system comprises a plurality of radiation detectors (20) configured to detect radiation events emanating from an imaging region. The system comprises a calibration phantom (14) configured to be disposed in the imaging region spanning substantially an entire field of view and to generate radiation event pairs that define lines-of-response, wherein the calibration phantom is thin such that each LOR intersects the calibration phantom along its length, the thickness of the phantom being smaller than the length of the LORs. A calibration processor (24) receives input of the radiation detectors and calculates an incidence angle independent crystal delay Ʈ i for each detector. The calibration processor (24) constructs a first look-up table for the timing correction of each LOR and a second look-up table for the angle depth of interaction correction for each crystal by combining Ʈ i and η i
    • 诊断成像系统包括被配置为检测从成像区域发出的辐射事件的多个辐射检测器(20)。 该系统包括校准体模(14),其配置成设置在跨越整个视野的成像区域中并且产生限定线响应的辐射事件对,其中校准体模薄,使得每个LOR与 沿其长度的校准体模,体模的厚度小于LOR的长度。 校准处理器(24)接收辐射检测器的输入并且计算每个检测器的入射角独立晶体延迟Ʈi。 校准处理器(24)通过组合Ʈi和ηi构成用于每个LOR的定时校正的第一查找表和用于每个晶体的相互作用校正的角度深度的第二查找表
    • 9. 发明申请
    • TIME OF FLIGHT CALIBRATION IN DIGITAL POSITRON EMISSION TOMOGRAPHY
    • 数字正射影像断层扫描时间飞行校准
    • WO2016046703A3
    • 2016-03-31
    • PCT/IB2015/057160
    • 2015-09-17
    • KONINKLIJKE PHILIPS N.V.
    • WANG, Sharon XiaorongLAURENCE, Thomas Leroy
    • G01T1/29
    • Time of flight (TOF) corrections for radiation detector elements of a TOF positron emission tomography (TOF PET) scanner are generated by solving an over-determined set of equations defined by calibration data acquired by the TOF PET scanner from a point source located at an isocenter of the TOF PET scanner, suitably represented as matrix equation Formula I = CS where Formula I represents TOF time differences, C is a relational matrix encoding the radiation detector elements, and S represents the TOF corrections. A pseudo-inverse C -1 of relational matrix C may be computed to solve S = C -1 Formula I . TOF corrections can be generated for a particular type of detector unit by identifying the radiation detector elements in C by detector unit. Further, multi-photon triggering time stamps can be adjusted to first-photon triggering based on Formula II where P 1 is average photon count using first-photon triggering and P m is a photon count using multi-photon triggering.
    • 对TOF正电子发射断层扫描(TOF PET)扫描仪的辐射检测器元件的飞行时间(TOF)校正通过求解由TOF PET获取的校准数据定义的超出确定的一组等式来生成 来自位于TOF PET扫描仪等角点的点源的扫描仪,适当地表示为矩阵方程:公式I = CS其中公式I表示TOF时间差,C 是编码辐射探测器元件的关系矩阵,并且S表示TOF校正。 可以计算关系矩阵C的伪逆-C C -1 -1来求解S = C 公式I 通过检测器单元识别C中的辐射检测器元件,可以为特定类型的检测器单元生成TOF校正。 此外,可以将多光子触发时间戳调整为基于公式II的第一光子触发,其中,P 1是使用第一光子触发的平均光子计数,并且P m是 使用多光子触发的光子计数。