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    • 43. 发明申请
    • NUCLEAR MEDICAL DIAGNOSTIC DEVICE
    • 核医学诊断装置
    • US20100127179A1
    • 2010-05-27
    • US12376488
    • 2006-09-19
    • Hiromichi TonamiJunichi Ohi
    • Hiromichi TonamiJunichi Ohi
    • G01T1/166G01T1/20
    • G01T1/1644G01T1/1648
    • Parameters T1, T2, and K required by a scintillator array identification mechanism in a two-stage scintillator γ-ray detector (depth of interaction (DOI)) are accurately and easily determined. The parameters required by the scintillator array identification mechanism are determined with reference to a first signal count ratio, which is obtained by irradiating a γ-ray on each scintillator array with luminescence pulses in an incident depth direction of the γ-ray having different attenuation time during an inspection stage of the γ-ray detector single unit. Furthermore, a second signal count ratio is obtained by irradiating the γ-ray on a front surface of the γ-ray detector single unit, and then a third signal count ratio is obtained by irradiating the γ-ray on the front surface after the γ-ray detector single unit is installed in a PET device.
    • 在两级闪烁体γ射线检测器(相互作用深度(DOI))中的闪烁体阵列识别机构所需的参数T1,T2和K被精确且容易地确定。 闪烁体阵列识别机构所要求的参数参照第一信号计数比来确定,该第一信号计数比通过在具有不同衰减时间的γ射线的入射深度方向上照射每个闪烁体阵列上的γ射线 在γ射线检测器单元的检查阶段。 此外,通过在γ射线检测器单元的前表面上照射γ射线获得第二信号计数比,然后通过在γ射线之后照射前表面上的γ射线获得第三信号计数比 射线检测器单元安装在PET装置中。
    • 47. 发明申请
    • SYSTEM AND METHOD FOR QUANTITATIVE MOLECULAR BREAST IMAGING
    • 定量分子乳腺成像的系统和方法
    • US20100034734A1
    • 2010-02-11
    • US12515369
    • 2007-12-10
    • Michael K. O'ConnorCarrie B. Hruska
    • Michael K. O'ConnorCarrie B. Hruska
    • A61K51/00
    • G01T1/1644A61B6/4258
    • A system and method for performing quantitative lesion analysis in molecular breast imaging (MBI) using the opposing images of a slightly compressed breast that are obtained from the dual-head gamma camera. The method uses the shape of the pixel intensity profiles through each tumor to determine tumor diameter. Also, the method uses a thickness of the compressed breast and the attenuation of gamma rays in soft tissue to determine the depth of the tumor from the collimator face of the detector head. Further still, the method uses the measured tumor diameter and measurements of counts in the tumor and background breast region to determine relative radiotracer uptake or tumor-to-background ratio (T/B ratio).
    • 使用从双头伽马照相机获得的略微压缩的乳房的相对图像,在分子乳腺成像(MBI)中进行定量病变分析的系统和方法。 该方法使用通过每个肿瘤的像素强度分布的形状来确定肿瘤直径。 此外,该方法使用压缩乳房的厚度和软组织中的γ射线的衰减来确定来自检测器头的准直仪面的肿瘤的深度。 此外,该方法使用测量的肿瘤直径和肿瘤和背景乳腺区域中的计数测量来确定相对放射性示踪剂摄取或肿瘤与背景比(T / B比)。
    • 49. 发明授权
    • CT detector array having non-pixelated scintillator array
    • 具有非象素化闪烁体阵列的CT检测器阵列
    • US07643607B2
    • 2010-01-05
    • US11380488
    • 2006-04-27
    • Haochuan JiangDavid M. HoffmanJames S. Vartuli
    • Haochuan JiangDavid M. HoffmanJames S. Vartuli
    • H05G1/64G01T1/202
    • G01T1/2985A61B6/032A61B6/4233G01N23/046G01N2223/419G01T1/1644G01T1/201G21K1/02
    • The present invention is a directed to a non-pixelated scintillator array for a CT detector as well as an apparatus and method of manufacturing same. The scintillator array is comprised of a number of ceramic fibers or single crystal fibers that are aligned in parallel with respect to one another. As a result, the pack has very high dose efficiency. Furthermore, each fiber is designed to direct light out to a photodiode with very low scattering loss. The fiber size (cross-sectional diameter) may be controlled such that smaller fibers may be fabricated for higher resolution applications. Moreover, because the fiber size can be controlled to be consistent throughout the scintillator array and the fibers are aligned in parallel with one another, the scintillator array, as a whole, also is uniform. Therefore, precise alignment with the photodiode array or the collimator assembly is not necessary.
    • 本发明涉及一种用于CT检测器的非像素化闪烁体阵列以及其制造方法。 闪烁体阵列包括相对于彼此平行对准的多个陶瓷纤维或单晶纤维。 因此,该包装具有非常高的剂量效率。 此外,每个光纤被设计成将光引导到具有非常低的散射损耗的光电二极管。 可以控制纤维尺寸(横截面直径),使得可以制造更小的纤维用于更高分辨率的应用。 此外,由于可以将整个闪烁体阵列的纤维尺寸控制为一致,并且纤维彼此平行排列,所以闪烁体阵列整体上也是均匀的。 因此,不需要与光电二极管阵列或准直器组件的精确对准。
    • 50. 发明授权
    • PMT gain and energy calibrations using lutetium background radiation
    • 使用镥背景辐射的PMT增益和能量校准
    • US07633057B2
    • 2009-12-15
    • US12088087
    • 2006-09-15
    • Steven CookeThomas Laurence
    • Steven CookeThomas Laurence
    • G01T1/20
    • G01T1/2985A61B6/037G01T1/1644G01T1/202
    • A scintillator (18) includes radioactive elements which emit radiation of a characteristic energy, such as lutetium176, which emits 202 keV and 307 keV γ-rays. The scintillators have light output levels that vary and photomultiplier tubes that respond to the light scintillations tend to drift. When a scanner (10) is not generating diagnostic images, the photomultiplier tubes detect scintillations from the lutetium 176 radiation. A self-calibration processor (40) adjusts the gain for each photomultiplier tube such that its output peak corresponds to 202 keV or 307 keV and adjusts a scaling factor for PMT outputs corresponding to each scintillator such that the output peaks have a common amplitude.
    • 闪烁体(18)包括发射特征能量的辐射的放射性元素,例如镥176,其发射202keV和307keV伽马射线。 闪烁体具有变化的光输出水平,并且响应于光闪烁的光电倍增管倾向于漂移。 当扫描器(10)不产生诊断图像时,光电倍增管检测来自镥176辐射的闪烁。 自校准处理器(40)调整每个光电倍增管的增益,使得其输出峰值对应于202keV或307keV,并且调整对应于每个闪烁体的PMT输出的缩放因子,使得输出峰值具有共同的幅度。