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    • 5. 发明授权
    • Singular value filter for imaging or detection
    • 用于成像或检测的奇异值滤波器
    • US09002080B2
    • 2015-04-07
    • US13650821
    • 2012-10-12
    • F. William Mauldin, Jr.John A. HossackAbhay V. Patil
    • F. William Mauldin, Jr.John A. HossackAbhay V. Patil
    • G06K9/00G06K9/62A61B8/08
    • G06K9/6247A61B8/0891A61B8/481A61B8/485A61B8/5207G01S7/52039G01S7/52041G01S7/52042G01S7/52046G01S15/8915G01S15/8981
    • Apparatus or techniques can include obtaining information indicative of energy, such as ultrasonic energy, reflected from a tissue region, forming respective input matrices representative of the obtained information, the input matrices respectively comprising an ensemble-of-interest and at least one ensemble corresponding to a spatial location nearby a spatial location corresponding to the ensemble-of-interest, performing respective singular value decompositions on the respective input matrices to obtain respective sets of singular values corresponding to respective sets of singular vectors, obtaining respective output matrices including weighting a respective projection of a respective ensemble-of-interest onto at least one of the singular vectors included in a respective set of singular vectors, and, using the respective output matrices, at least one of determining a characteristic, or constructing an image, of at least a portion of the tissue region.
    • 设备或技术可以包括获得指示诸如超声波能量的信息的信息,例如从组织区域反射,形成表示所获得信息的相应输入矩阵,输入矩阵分别包括感兴趣集合和至少一个对应于 相邻于感兴趣集合的空间位置附近的空间位置,在各个输入矩阵上执行各自的奇异值分解,以获得对应于各组奇异矢量的各组奇异值,获得各自的输出矩阵,包括对相应投影加权 将相关的感兴趣整体集合到包含在相应的一组奇异矢量中的奇异矢量中的至少一个,并且使用相应的输出矩阵,确定至少一个 部分组织区域。
    • 6. 发明申请
    • System and Method for Combined ECG-Echo for Cardiac Diagnosis
    • 用于心脏诊断的组合ECG回波的系统和方法
    • US20100168578A1
    • 2010-07-01
    • US12664146
    • 2008-06-12
    • Arthur Garson, JR.William F. WalkerJohn A. HossackTravis N. Blalock
    • Arthur Garson, JR.William F. WalkerJohn A. HossackTravis N. Blalock
    • A61B8/14A61B5/0402
    • A61B8/0858A61B8/0883A61B8/483
    • A system and related method for obtaining volumetric cardiac data of a subject. The data is generated by forming a plurality of focused ultrasound images corresponding to a series of ranges, generating myocardial boundary data for each of the plurality of ultrasound images, calculating the area of the region defined by said myocardial boundary data for each of the plurality of ultrasound images, multiplying the area for each of the plurality of ultrasound images by a slice depth corresponding to said ultrasound image to obtain the slice volume of each slice, and summing the slice volumes to obtain a total volume. In an alternative embodiment the system and related method combine an automated volumetric ultrasound system for finding chamber volumes and myocardial thicknesses, with a diagnostic electrocardiogram system to enable simultaneous diagnosis of mechanical and electrical cardiac problems.
    • 用于获得受试者体积心脏数据的系统和相关方法。 通过形成对应于一系列范围的多个聚焦超声图像来生成数据,为多个超声图像中的每一个生成心肌边界数据,计算由多个超声图像中的每一个的所述心肌边界数据定义的区域的面积 超声图像,将所述多个超声图像中的每一个的面积乘以对应于所述超声图像的切片深度,以获得每个切片的切片体积,并且对切片体积求和以获得总体积。 在替代实施例中,系统和相关方法结合了用于发现腔室体积和心肌厚度的自动化体积超声系统与诊断心电图系统,以实现机电和电心脏问题的同时诊断。
    • 8. 发明授权
    • Medical diagnostic ultrasound system and method for versatile processing
    • US06755787B2
    • 2004-06-29
    • US10299179
    • 2002-11-19
    • John A. HossackJeffrey S. HastingsJeffrey M. GreenbergSamuel H. Maslak
    • John A. HossackJeffrey S. HastingsJeffrey M. GreenbergSamuel H. Maslak
    • A61B800
    • G01S15/899A61B8/483A61B8/5276G01S7/52034G01S7/52077G01S15/8981G01S15/8993G01S15/8995
    • A method and system for reducing speckle for two and three-dimensional images is disclosed. For two-dimensional imaging, a one and a half or a two-dimensional transducer is used to obtain sequential, parallel or related frames of elevation spaced data. The frames are compounded to derive a two-dimensional image. For three-dimensional imaging, various pluralities of two-dimensional frames of data spaced in elevation are compounded into one plurality of spaced two-dimensional frames of data. The frames of data are then used to derive a three dimensional set of data, such as by interpolation. Alternatively, the various pluralities are used to derive a three-dimensional set of data. An anisotropic filter is applied to the set of data. The anisotropic filter filters at least along the elevation dimension. In either situation, various displays may be generated from the final three-dimensional set of data. A method and system for adjustably generating two and three-dimensional representations is also disclosed. For three-dimensional imaging, at least two sets of three-dimensional data corresponding respectively to two types of Doppler or B-mode data are generated. The sets of data are then combined. An image or a quantity may be obtained from the combined data. By combining after generating the three-dimensional sets of data, the same data (sets of data) may be combined multiple times pursuant to different relationships. Thus, a user may optimize the image or quantity. Likewise, frames of data may be combined pursuant to different persistence parameters, such as different finite impulse response filter size and coefficients. The frames of data may then be re-combined pursuant to different persistence parameters. Original ultrasound data may also be used to re-generate an imaging using the same ultrasound image processes as used for a previous image. APPENDIX A ⁢ Filter at Plane ⁢ Y = - 2   ⁢ X ⁢   ⁢ → ⁢ [ 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.2 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 ] ⁢ Z ↓ Filter at Plane ⁢ Y = - 1 ⁢ [ 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.4 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 ] Filter at Plane ⁢ Y = 0 ⁢ [ 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 1.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 ] Filter at Plane ⁢ Y = + 1 ⁢ [ 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.4 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 ] Filter at Plane ⁢ Y = + 2 ⁢ [ 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.2 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 0.0 ] The filter perform no filtering in the X, Z plane. It filters (low pass) contributions from neighboring elements in only the Y direction. The filter may be implemented as a 1-D low pass filter in the Y-direction [0.2, 0.4, 1.0, 0.4, 0.2]=(a 1×5×1 anisotropic filter).