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CN116635162A - 用于改进超声图像质量的系统和方法 - Google Patents

用于改进超声图像质量的系统和方法 Download PDF

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CN116635162A
CN116635162A CN202180083620.4A CN202180083620A CN116635162A CN 116635162 A CN116635162 A CN 116635162A CN 202180083620 A CN202180083620 A CN 202180083620A CN 116635162 A CN116635162 A CN 116635162A
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ultrasound
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E·M·阿特梅
B·R·里特兹
D·J·斯佩奇
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Maui Imaging Inc
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Abstract

提供了改进超声图像质量的系统和方法。在一些实施例中，数据集可以由在多个接收元件中的每一个接收元件处接收到的回波形成。数据集之间的数据可以被屏蔽以包括或排除数据。然后可以对被屏蔽的数据集进行波束成形，以形成超声图像。

Description

用于改进超声图像质量的系统和方法
相关申请的交叉引用
本申请要求2020年11月2日提交的美国临时专利申请号63/108,809，标题为“Systems and Methods for Improving Ultrasound Image Quality”的权利，该申请通过整体引用并入本文。
本申请还与以下美国专利申请有关：美国专利8,007,439，标题为“Method andApparatus to Produce Ultrasonic Images Using Multiple Apertures”；美国专利9,247,926，标题为“Multiple Aperture Medical Ultrasound Transducers”；美国专利9,146,313，标题为“Point Source Transmission and Speed-of-Sound Correction UsingMulti-Aperture Ultrasound Imaging”；美国专利9,668,714，标题为“Systems andMethods for Improving Ultrasound Image Quality by Applying WeightingFactors”；美国专利9,986,969，标题为“Ultrasound Imaging System MemoryArchitecture”；美国专利9,572,549，标题为“Calibration of Multiple ApertureProbes”；美国专利9,510,806，标题为“Alignment of Ultrasound Transducer Arraysand Multiple Aperture Probe Assembly”；美国专利9,883,848，标题为“UltrasoundImaging Using Apparent Point-Source Transmit Transducer”；美国专利10,401,493，标题为“Network-Based Ultrasound Imaging System”；美国专利10,380,399，标题为“Ultrasound Imaging Systems and Methods for Detecting Object Motion”；以及美国专利申请公开2017/0209121，标题为“Ultrasound Imaging with Sparse Arrays”。这些专利和专利申请的每一者的整体内容通过引用并入本文。这些相关申请在本文中可称为“申请人在先的专利和申请”。
除非本文另有规定，本说明书中提到的所有专利、公开和专利申请在本文中都是通过引用并入的，其程度与每个单独的公开或专利申请被特定地并且单独地指出为通过引用并入的程度相同。
技术领域
本发明一般涉及超声成像，更具体地涉及通过最小化噪声来改进超声成像质量的系统和方法。
背景技术
在常规的超声成像中，一束聚焦的超声能量被发射到待检查的身体组织中，返回的回波被检测和绘制以形成图像。虽然超声已广泛用于诊断目的，但常规超声由于扫描深度、散斑噪声、横向分辨率差、组织模糊和其他类似问题而受到很大限制。
为了声穿透身体组织，通常通过相控阵或整形换能器形成和聚焦超声波束。相控阵超声是医学超声成像中常用的导向和聚焦窄超声波束以形成图像的方法。相控阵探头具有许多小的超声换能器元件，每个元件都可以单独地被脉冲调制。通过改变超声脉冲的时间(例如，通过沿着一行顺序地一个接一个地使元件脉冲化)，建立了相长干涉模式，从而产生以选定角度定向的波束。这就是所谓的束控向。这样的被控向的超声波束可以扫过被检查的组织或对象。然后将来自多个波束的数据组合以形成显示穿过对象的切片的视觉图像。
传统上，用于发射超声波束的相同换能器或阵列用于检测返回的回波。这种设计配置是超声成像用于医疗目的的最重要限制之一的核心：横向分辨率差。理论上，可以通过增加超声探头孔径的宽度来提高横向分辨率，但与增加的孔径尺寸相关联的实际问题使孔径保持较小。毫无疑问，即使有这种限制，超声成像也非常有用，但如果分辨率更高，它可能会更有效。
随着多孔径成像的产生，超声成像领域已经取得了重大改进，申请人在先的专利和申请中显示和描述了其中的示例。多孔径成像方法和系统允许超声信号经由单独的孔径被发射和接收。
发明内容
提供了一种在超声成像中减少噪声的方法，其包括以下步骤：将具有多孔径超声阵列的第一非聚焦超声脉冲发射到具有包括骨骼在内的一种或多种类型的组织的感兴趣区域；使用多孔径超声阵列的一个或多个接收元件接收来自感兴趣区域的回波；形成针对一个或多个接收元件的每一个接收元件的感兴趣区域中的多个像素的数字数据集；对所有数字数据集进行平均；使用包括或排除数据的预定的数学条件，应用控件以屏蔽来自数字数据集的数据值；产生屏蔽数据集输出；以及对屏蔽数据集输出进行波束成形以产生一个或多个超声图像。
在一些实施例中，预定的数学条件基于每个数字数据集的平均值的百分比来屏蔽数据。
在另一个实施例中，预定的数学条件消除落在平均值的预定百分比之外的数据。
在一些实施例中，屏蔽数据集输出产生一个或多个3D超声图像。
在一些示例中，预定的数学条件基于每个数字数据集的平均值的百分比来屏蔽数据。
在一个实施例中，波束成形是实时执行的，并且其中新数据可用于改变或选择新的屏蔽数据集输出。
在一些示例中，该方法还包括调整屏蔽数据值。
在一个实施例中，该方法包括将第二未聚焦超声脉冲发射到感兴趣区域，并使用一个或多个接收元件接收来自感兴趣区域的回波。
在一些实施例中，对屏蔽数据集输出进行波束成形，产生感兴趣区域的全部或子集的图像。
在一个实施例中，可以从同一阵列的一个或多个元件接收回波。
在另一个实施例中，第一未聚焦超声脉冲用比第二未聚焦超声脉冲更多的超声换能器发射。
在一些实施例中，第二未聚焦超声脉冲用比第一未聚焦超声脉冲更多的超声换能器发射。
提供了一种减少超声成像噪声的方法，其包括以下步骤：将具有多孔径超声阵列的第一未聚焦超声脉冲发射到具有一种或多种类型的组织的感兴趣区域；使用多孔径超声阵列的一个或多个接收元件接收来自感兴趣区域的回波；形成针对由第一接收元件接收到的回波的第一数字数据；形成针对由第二接收元件接收到的回波的第二数字数据集；标识第一数字数据集和第二数字数据集中的相似数据的组；将第一数字数据集和第二数字数据集之间共享公共值的相似数据关联；屏蔽共享公共值的数据；将第一数字数据集和第二数字数据集中的间隙值减小到零或其他值；产生屏蔽数据集输出；以及对屏蔽数据集输出进行波束成形以产生一个或多个超声图像。
提供了一种在超声成像中减少噪声的方法，其包括以下步骤：将具有多孔径超声阵列的第一未聚焦超声脉冲发射到具有一种或多种类型的组织的感兴趣区域；使用多孔径超声阵列的一个或多个接收元件接收来自感兴趣区域的回波；形成针对由第一接收元件接收到的回波的第一数字数据集；形成针对由第二接收元件接收到的回波的第二数字数据集；标识第一数字数据集和第二数字数据集中的相似数据的组；将第一数字数据集和第二数字数据集共享公共值的相似数据关联；屏蔽共享公共值的数据；仅留下从第一数字数据集和第二数字数据集之间的间隙中保留的数据；产生屏蔽数据集输出；以及对屏蔽数据集输出进行波束成形，以产生一个或多个超声图像。
附图说明
本发明的新颖性特征在下面的权利要求中被特别地阐述。通过参考以下阐述说明性实施例的详细描述和附图，可以更好地理解本发明的特征和优点，在说明性实施例中利用了本发明的原理，在附图中：
图1A是具有三个换能器阵列的多孔径成像探头和若干待成像的点的示意图。
图1B是来自三个换能器阵列中的每一个换能器上的元件的接收到的波形的图示。
图1C按通道表示与三个换能器阵列的每个元件相关联的数字数据信息。
图2是映射以下步骤的过程的示图：从对感兴趣区域进行成像的基于多孔径声脉冲的系统收集原始数据；从接收来自相同的被发射的声脉冲的回波数据的不同元件中划分数据；标识数据中的大差异；屏蔽掉较大的值；以及然后对图像进行波束成形。
图3是映射以下步骤的过程的示图：从对感兴趣区域进行成像的基于多孔径声脉冲的系统收集原始数据；从接收来自相同的被发射的声脉冲的回波数据的不同元件中划分数据；在数据串中平均数据值；然后从数据中的平均值中屏蔽可选择百分比以外的数据；以及然后对图像进行波束成形。
具体实施方式
将参考附图详细描述各种实施例。对具体示例和实现的引用是为了说明目的，并不旨在限制本发明或权利要求书的范围。
本公开提供了用于通过减轻或消除目标图像点(即，给定像素或体素)中的噪声来改进由基于声脉冲的多孔径成像(“PMA”成像)系统产生的超声图像质量的系统和方法，其中此类噪声是由具有与目标图像点非常不同的回波特征的时间相邻结构引起的。此类噪声将在本文中称为“相邻噪声”。
正如下文以及申请人在先的专利和申请中更详细描述的，PMA成像涉及超声“声脉冲”的传输，其回波可以被位于距离发射器一定距离的接收元件接收。每个接收到的回波信号位于由发射器和接收器位置以及声脉冲传输和回波接收之间的时间间隔定义的椭圆上。可以通过以强调它们的(即，数据样本)的交点的方式组合这些椭圆来形成图像。每个交点可以是二维或三维图像中的图像点。然而，如果一个错误椭圆的值明显高于或低于对同一图像点有贡献的其他椭圆，则错误椭圆的值可能占主导地位，并导致图像点比图像点所代表的真实对象更亮或更暗。
当亮的对象和暗的对象都位于同一个时间椭圆上(即“相邻椭圆”)时，错误的椭圆可能会对图像点有贡献。这可能是由于发射器、反射物对象和接收器之间的材料差异或沿路径的不同结构，或由于在感兴趣的成像区域内，较亮和较暗的反射物彼此靠近而发生的。例如，当直接在硬膜外空间内对脊髓进行成像并且被椎骨的强反射物包围时，这种现象可能会出现问题。类似的，当使用PMA系统在颅骨内成像时，当脑室紧挨着颅骨的内表面时，(相对暗淡的)脑室可能无法与(相对亮的)颅骨区分开。在这些和许多其他成像场景中，代表给定反射物的给定图像点的求和可能无意中包括一个或多个椭圆，该椭圆代表具有与给定反射物明显不同的回波特征(即，明显更亮或更暗)的相邻结构。这种“相邻噪声”现象可能具有模糊边缘和模糊真实结构的影响，否则这些结构在图像中可见。
在一些实施例中，可以通过评估对图像或图像区域有贡献的数据样本以标识包含不可接受程度的相邻噪声的数据样本来减轻或消除相邻噪声。一旦被标识，这种相邻噪声数据样本对最终图像的影响就可以被最小化。在一些实施例中，亚视觉数据分析可以用于标识可能包含具有大量相邻噪声的数据样本的数据样本、数据样本组或图像点区域。
通常可以通过将所有收集的数据样本映射到相应的图像点(例如，像素或体素)来标识噪声数据样本，然后对于每个图像点，集体评估对图像点有贡献的数据样本的集合，并标识相对于该集合包含不可接受的高噪声水平的单个数据样本。一旦标识出来，可以通过调整、加权、忽略或以其他方式修改噪声数据样本的值来减轻或消除噪声数据样本对最终图像的影响。本文描述了这种方法的各种示例和实施例。
尽管本文描述的各种实施例参考各种解剖结构或植入式医疗设备的超声成像，然而可以理解，本文所示和所述的许多方法和设备也可以用于其他应用，诸如成像和评估非解剖结构和对象。
基于声脉冲的多孔径成像
本文描述的系统和方法的一些实施例基于称为基于声脉冲的多孔径成像(“PMA”成像)的独特成像方式。下文提供了基于声脉冲的多孔径成像的介绍性描述。用于执行基于声脉冲的多孔径成像的方法和结构的附加细节、示例、实施例和应用在上述申请人在先的专利申请中被描述。
简而言之，PMA成像涉及将一系列未聚焦的二维或三维“声脉冲”从“传送孔径”(可由一个换能器结构或一组协同工作的换能器组成)发射到介质中，然后接收和存储由每个声脉冲的回波和/或通过传输产生的信号。信号由许多“接收元件”(每个元件由一个或多个换能器结构组成)接收，这些“接收元件”可以分组为“孔径”。接收换能器产生时变模拟信号，其振幅与冲击换能器的能量强度成正比。这样的模拟信号可以以一定采样率进行数字采样，然后可以存储数字采样。每个数字采样的值可以与接收到的超声强度成正比。每个数字样本可以表示介质中某些反射或透射结构的“回波”。由单个接收换能器元件接收的数字样本可以被组织为数据样本的“串”，这些数据样本可以被细分为本文中一些实施例中所述的“子串”。可以通过将样本映射到成像介质内的位置并将亮度(和/或颜色)值与贡献数据样本的值成比例地分配给每个图像点(例如，像素或体素)来形成图像。
虽然在本文中使用诸如“亮”和“暗”的术语来指代图像点和数据样本，但是本领域技术人员将认识到这些术语不是绝对的，因为所显示图像的亮度或对比度可以被调整。相反，在相对意义上使用这些术语来区分表示高度反射或“回波”结构的那些数据样本和图像点，这些高度反射或“回波”结构通常但不一定被称为比通常但不一定被称为“暗”的最小反射结构更“亮”。当然，一些成像系统可以被配置为具有相反的惯例，其中能量强度较大的样本被显示为暗点，而能量强度较低的样本被显示为亮点。在这两种惯例中，在本文所述的系统和方法的上下文中，术语“亮”意在指代表示所接收的能量强度较大的点(不管能量是从成像结构的反射还是通过成像结构的传输后接收到的)，而“暗”点则是接收能量强度相对较低的点。
来自基于声脉冲的多孔径成像系统的波束成形图像
可以从每个接收元件产生的信号中获得介质的完整子图像。从公共孔径的元件获得的子图像可以彼此组合以产生“第一级”图像。来自多个声脉冲传输(从相同或不同的传送孔径发射)的子图像和/或第一级图像可以被组合以产生“第二级”图像。来自多个接收孔径的第二级图像可以被组合以产生“第三级”图像。图像层组合序列的许多排列是可能的，因此子图像、第一级图像、第二级图像和第三级图像不一定需要在由名称所暗示的序列中形成。
如果发射元件和/或接收元件在二维或三维中彼此间隔，则“图像”(包括子图像)可以是由三维体素组成的三维体。可以选择这种体的任何二维截面，并将其显示为二维像素矩阵。术语“图像点”将用于指代二维或三维图像的离散元件(例如，像素或体素)。
当信号被换能器元件接收时，信号可被转换成数字数据的序列，该序列可以被存储在易失性和/或非易失性存储器设备中。这样的数据条目的序列中的每个条目可以称为“数据样本”。术语“数据样本”也可以指通过聚合多个数据条目(例如，取平均值、取最小值或最大值等)获得的值或通过在两个或多个数据条目之间插值获得的值。
为了根据集合数据样本形成子图像，必须通过本文称为“波束成形”的过程将每个样本(单独的、聚合的或内插的)映射到其在图像内的可能位置。每个数据样本表示图像内的潜在位置(轨迹)的范围，这些位置(轨迹)的范围由发射元件和接收元件的位置、声脉冲传输和信号接收之间的时间差以及通过被成像介质的声速确定。
在发射器位于与接收器不同的点处的多孔径成像系统中，针对每个样本的可能位置轨迹采用二维椭圆或三维椭球的形状，其中发射元件和接收元件位于椭圆或椭球的焦点，参考美国专利9,146,313，标题为“Point Source Transmission and Speed-of-SoundCorrection Using Multiple-Aperture Ultrasound Imaging”。术语“轨迹”(及其复数形式“轨迹”)将用于指代椭圆或椭球体。成像系统通过将轨迹与同一图像点相交的的多个数据样本加在一起，从而收敛到每个图像点的正确位置。每个对单个图像点有贡献的数据样本可以被称为该图像点的“贡献者”。椭圆或椭球相交的点被增强(即，比其单个贡献者具有更大的总亮度)，并表示待显示或记录的点的正确位置。
该过程容易受到独特形式的误差的影响，本文将该误差称为相邻噪声。如果特定的数据样本包含高度的噪声，导致其轨迹比图像点的其他贡献者明显更亮，则可以显示相邻噪声样本的更大区域，从而产生轨迹形状的噪声伪影。通过突出显示与成像介质中的物理结构不对应的区域，这样的单个相邻噪声样本可能会造成图像的显著畸变。由相邻噪声引起的畸变可以通过许多技术中的任何一种技术来标识，其中一些技术将在下文描述。一旦被标识，在通过本文描述的一种或多种技术形成图像时，可以将相邻噪声最小化。
通过平均来标识邻居噪声数据样本
比相同图像点的其他贡献者要亮得多的高回波反射物是可能导致相邻噪声的问题。此处，压倒了其他贡献者的“太亮”的贡献者可能会产生亮的伪影或其他虚假信息。这对于图像点来说尤其有问题，否则对于位于数据样本中的强回波反射物而言，图像点会相对“暗”。以一种相反但相关的方式，低回波反射物可能被错误地显示为比预期暗得多，因为同一图像点的其他贡献者往往会抵消“太暗”贡献者的影响。因此，在这两种情况下，标识表示相邻噪声的数据样本(或椭圆)可能是有益的。
通常，对于单个图像点，由于路径长度、观察角度、障碍物、材料、声脉冲传输的时间或其他因素的差异，被发射的声脉冲和接收元件的不同组合所产生的数据样本可能会显示反射物的更亮或更暗的回波。尽管如此，在正常情况下，这种变化的程度可以预期保持在可预测的范围内，该范围可以基于经验测试和/或数学建模/模拟来确定。明显落在这种预期范围之外的回波值很可能是噪声或其他形式的误差。因此，可能期望系统地定义“异常亮”的值，标识对任何图像点贡献“异常亮”的值的数据样本，并最小化这种异常亮样本的有害影响。
在一些实施例中，取代对高噪声介质内的每个图像点进行评估，可以将待评估的图像点集简化为图像点的候选集。例如，在一些实施例中，可以选择亮度值小于预定值(例如，在0.0到1.0的范围内≤0.9)的图像点进行分析，以检测相邻噪声贡献者。在其他实施例中，可以选择亮度值大于预定的较低值(例如，在0.0至1.0的范围内的0.1)但小于预定的较高值(例如，0.8)的图像点进行分析，以检测相邻噪声贡献者。
在一些实施例中，可以基于对相邻图像点或区域内的图像点的分析来标识针对相邻噪声数据样本的存在而待评估的图像点。例如，如果在应用所有贡献者之后，特定图像点具有明显高于所有相邻图像点或区域内的所有图像点的亮度值，则可以选择该图像点作为可能的相邻噪声贡献者以用于进行贡献者评估。在其他实施例中，可以通过评估对区域中的一组图像点做出贡献的数据样本来标识针对相邻噪声数据样本的存在而待评估的图像点，以便检测该区域中相对较暗和较亮的图像点之间的“边缘”。在下文的部分中描述了这种过程的一个示例。
无论是评估所有图像点还是通过诸如上述那些方法选择的图像点的子集，都可以使用各种过程来标识特定图像点的相邻噪声贡献者。在一个示例实施例中，这样的过程可以包括：从传送孔径发射声脉冲；从声脉冲接收反射的和/或发射的信号；将表示接收到的信号的采样数字数据数字化并存储；以及对所存储的数据进行波束成形，以将数据样本映射到图像点。然后对于待评估的每个图像点：确定对图像点有贡献的数据样本集的聚合值，并将相邻噪声贡献者标识为其值与聚合值相差大于预期方差的那些数据样本。
在各种实施例中，评估数据样本以标识相邻噪声贡献者的步骤可以在如上所述的各种应用中所描述的各种相干或不相干求和步骤之前和/或之后执行，并通过引用并入本文。例如，在一些实施例中，可以在任何数据求和步骤之前对原始数据样本进行评估，以便以比数据求和之后可能具有的细节程度更大的细节程度来检测边缘区域或其他可区分特征。
在各种实施例中，对特定图像点有贡献的一组数据样本的“聚合值”可以是算术平均值(简单平均值)、中位数(集合中所有样本值的中点)、众数(集合中最频繁出现的值)、最大值(集合的最大值)、最小值(集合的最小值)或描述或从数据样本集中获得的其他值。
在各种实施例中，定义相邻噪声数据样本的聚合值的方差可以用多种方式来定义。例如，方差可以是固定的数值、聚合值的倍数、从聚合值变化的百分比、高于聚合值的若干标准差、对图像点有贡献的数据样本集的百分位数、或聚合值的其他方差度量。
在一些实施例中，图像点的相邻噪声贡献者可以被定义为亮度值至少大于图像点的贡献者集的平均值、中位数、众数、最大值或其他聚合值N倍的样本。在这样的实施例中，N可以是至少约1.0至约2.0或更多。
在其他实施例中，相邻噪声贡献者可以被定义为亮度值大于图像点贡献者的平均值N个标准差以上的样本。在其他实施例中，邻点噪声贡献者可以被定义为亮度值大于贡献者集的最大值的样本，或最大值的N倍，或大于最大值的M％以上的样本。在其他实施例中，相邻噪声贡献者可以被定义为亮度值大于众数的N倍的样本，其中“众数”被定义为对图像点有贡献的数据样本集中出现频率最高的值。在一些实施例中，众数可以基于数据样本的舍入值来确定(例如，通过将集合的每个值舍入到预定的位数，并且然后确定最频繁出现的值)。
在一些实施例中，可以在图像波束成形之前对来自PMA系统的多个换能器元件收集的原始数据样本进行数学或其他评估，以便标识待调整的数据样本。在一些实施例中，这种预波束成形评估可以用于其他分析，诸如对象识别或其他分析。
通过边缘检测标识相邻噪声数据样本
当硬组织反射物或一组反射物位于紧邻软组织反射物或一组反射物的位置时，基于声脉冲的多孔径成像(PMA)系统就会出现限制。在这种情况下，贡献于表示硬组织或高回波反射物(即，“亮”反射物图像点)的像素或体素的回波数据样本可能在灰度上被分配比代表紧邻硬反射物的软组织或低回波反射物(即，相对“暗”的图像点)的回波数据样本明显更强的值。相对于多孔径换能器阵列上的超声接收元件，位于同一时间椭圆上的较强和较弱的回波信号可能会产生这种噪声。因此，更准确地检测硬(亮)反射物和相对较软(较暗)反射物之间边缘的能力可用于增强最终显示图像中的那些边缘。这样的“边缘检测”技术在实现对原始回波数据的自动分析，从而甚至在产生图像之前产生可操作的信息方面也可能是有用的。
图1A展示了针对皮肤表面S的基于声脉冲的多孔径探头100，其具有阵列12、14和16。子阵列或通常每个阵列中的单个元件被指示为点a、b、c、d、e、f、g、h和i。然而，子阵列可以位于阵列之间的物理间隙中，并且不应被认为局限于单个阵列上的单个元件。声脉冲传输由阵列12上“a”处的传送孔径产生的波前13((多个)虚线波前)表示，并由小浪指示。介质或组织20中的A点表示硬结构(例如，来自动脉粥样硬化的钙或硬化斑块，或其他坚硬对象(诸如骨头))，它将立即在多个方向上反射或散射透射波前13，这里表示为反射波前15(实波前))。从A点发出的反射波前可向阵列12、14和16中的接收元件提供相对亮的信号。发射波前13也可以继续通过介质或组织20到达B点，B点表示一种消声结构(例如，血管或其他软组织)，该消声结构将向阵列12、14和16上的元件提供相对较弱的反射波前17。
图1B是表示分别返回到图1A的三个阵列12、14和16上的接收器a、b、c、d、e、f、g、h和i的波前13和17的振幅和时间的波形图。如图1B所示，可以看到来自对象A和B的反射振幅。注意B处对象的振幅在对象边缘处较强，而在大部分无回波的对象内部减弱。基于每个接收元件到对象的距离，在阵列上的不同时间处接收反射。例如，可以看到阵列12上的元件a更接近对象A，因为反射是在时间t+1处接收的。相比之下，阵列16上距对象A最远的元件I直到时间t+4才接收到反射。对象B也可以看到同样的情况，元件b、c和d是距对象B最近的，而元件i是距对象B最远的。
图1C是指示相对于声脉冲的传输，来自每个接收器的数据通道的被存储的与信号强度相关联的数字数据样本值的表格。图1C中限定的数据样本表明，强反射物A位于阵列12元件a附近，并且该信号的振幅可以通过该信号在探头上的元件上被接收时而被映射。如图所示，该数据表示介质20中的A点；然而，即使没有波束成形，并且即使反射物强度随着从原点或反射物接收到的回波越远而下降，仍然可以清楚地看到，该点可以在仍然处于数字范围的情况下被映射和跟踪。换句话说，即使没有波束成形和显示图像，也可以通过分析数据样本来检测和区分A点。
此外在图1C中，随着时间在阵列12元件a上向t+10前进，小信号建立，然后在t+11处几乎没有信号，然后在t+12处再次出现小信号，接着几乎没有信号。如果图像要从点B进行波束成形，则该数据将表示点B。然而，即使在稍微不同的时间被接收到，同样的小信号包围弱信号的模式也会出现在通过探测数据下行的通道中。该模式似乎最接近阵列12元件b和c，然后在移动到阵列14和16时变得更远。
不考虑图1B和图1C中观察到的单个声脉冲传输，当前基于声脉冲的多孔径系统在该点处将来自可选声脉冲序列(例如，13,15…n)的总数据和来自所有接收器的相关反射数据(未波束成形的原始数据)组合在一起，以创建单个数据集。然后，该数据集被波束成形为像素化图像。该组合波束成形随后可以使噪声从靠近弱目标的强目标中累积。
减轻相邻噪声数据样本
标识后，可以通过各种方式减轻相邻噪声贡献者对图像点的影响。在一些实施例中，标识为包含亮度高噪声的数据样本可以通过预先确定的分数调整因子进行加权。例如，相邻噪声数据样本的亮度可以乘以约0.5至0.001或更小的调整因子。示例调整因子可以包括0.50、0.45、0.40、0.35、0.30、0.25、0.20、0.15、0.10、0.05、0.04、0.03、0.02、0.01、0.005、0.001或更小的权重。在其他实施例中，相邻噪声数据样本可以被重新设置为等于其共同贡献者的聚合值。例如，可以将相邻噪声数据样本重新设置为等于从对包括所标识的相邻噪声样本的贡献者集的分析中获得的中位数、平均值、众数、最小值或其他值。在其他示例中，可以将相邻噪声数据样本重新设置为等于或小于预先确定的与平均值、中位数、众数或其他聚合值的标准差数。在其他实施例中，相邻噪声数据样本可以被重新设置为零的亮度值或预先确定的最小值。在一些实施例中，用于整个图像或图像区域的一组调整因子可在本文中称为应用于该图像或区域的“掩模”。这样的掩模可以简单地是与用于形成图像或图像区域的图像点和/或数据样本相对应的调整因子的阵列。
在一个实施例中，可以通过使用诸如图2中图示的过程200的数据屏蔽技术来大幅度减少相邻噪声。步骤202指示PMA系统以以其标准数据收集格式被用户使用以对感兴趣区域进行成像。这可以包括从PMA系统将一个或多个未聚焦的超声脉冲发射到感兴趣区域。在一些实施例中，感兴趣区域可以包括一种或多种类型的组织，包括骨骼。虽然PMA系统可以实时利用波束成形向用户呈现图像，但PMA系统也可以连续收集数据集。事实上，在成像会话期间呈现的图像可能只是可用于波束成形为图像的数据的子集，并且可以纯粹地由用户在系统上实时或经由云操作远程地进行选择。因此，步骤204强调了PMA系统正在从整个感兴趣区域收集数据集的事实，而不仅仅是正在被呈现的图像。这可以包括接收来自组织的回波并将回波转换为一个或多个通道上的数字通道数据。
图2，步骤206然后开始分析感兴趣区域中的数据的过程。在模数转换后收集的数据被存储为用于第一接收器元件的数据串。该接收器元件可以是阵列的一部分，也可以是作为全向接收器使用的独立元件。它不需要结合其他元件使用以实时收集和组合数据。因此，步骤208强调使用第二接收器元件以产生第二数据串，该第二数据串来自于用于在步骤206中向接收器提供接收器元件数据的相同声脉冲的。类似地，来自206和208的相同声脉冲传输的回波数据由步骤210中描述的第三接收器元件使用。
然后，在步骤212中利用处理器以对所有数据串的所有数据集值进行平均。在一些实现中，可以为整个感兴趣区域(即，大样本周期)收集数据串。在其他实现中，可以收集仅针对特定像素(即，特定样本周期)的数据。然后，用户可以基于步骤214中描述的每个串的平均数据的百分比来选择控制以屏蔽数据。屏蔽消除了落在平均值范围百分比以外的数据，无论是高数据还是低数据。相反，屏蔽可以用来消除平均值范围百分比内的数据，从而保留“异常值”。步骤216利用波束成形过程中剩余的数据来产生像素图像。在3D成像的情况下，可以利用相同的过程来产生体素图像。步骤218指示该过程可以被重复。在实时成像时，可以使用新的数据来改变或选择新的屏蔽值。在处理存储或静态数据集时，可以在现有数据集上调整调整屏蔽值。
在一个实施例中，可以通过对图3过程300中概述的数字数据进行分组以大幅减少相邻噪声。步骤302指示，PMA系统以其标准数据收集格式被用户使用，以对感兴趣区域成像。步骤304强调了PMA系统从整个感兴趣区域收集数据集的事实，而不仅仅是正在被呈现的图像。步骤306使用人工智能将不同数据串上相似值的数据分组到已知的对象位置中。这在图1和图1B中得到了最好的说明。图1B表示在时间段t+1到t+20上的沿不同阵列12、14和16的元件a到i的数字数据串。尽管在不同的数据串中出现在不同的时间处，但在每个数据串中都明显存在强反射物(A)的存在的相关性。与周围反射物相比，这种存在是有差异的，尽管当回波到达远离图1中A点的接收器元件时，较弱的辨别力是显而易见的。类似地，在图1中可能代表点B的数据串中，可以辨别出中等信号强度的出现，然后信号变弱，然后以鞍型形状再次变强。尽管该反射物的振幅较弱且为动态的，但即使接收时间不同，也可以在接收器数据串内建立明确的相关性。
图3的步骤306使用数据相关性或人工智能将相似的数据模式指定为最终将在图像中一起显示的组或基准。而在数据串状态下，它们成为被命名或编号的分组或基准。步骤308和310显示对第二和第三接收器元件的元件执行的相同的过程。步骤312使系统能够自动或手动地将标记组或基准组之间的间隙减小到零。相反，步骤314使系统能够屏蔽标记组或基准组，并仅留下从基准组之间的间隙中保留的数据。系统中的控制可以被配置为在方法312和314之间自动交替，或使用户能够在步骤312或步骤314之间进行选择。
步骤316利用现在被过滤的数据以被波束成形为图像。步骤318开始获取新数据的过程。图像数据也可以在步骤316之后被存储，保存在存储器中，然后使用其他滤波路径被添加到数据。
上述任何实施例均可以与任何所需结构的多孔径成像探头结合使用。多孔径超声成像探头的示例在本文引用的申请人的在先专利申请中提供。
上述系统和方法的实施例也可以有益地应用于利用聚焦相控阵发射脉冲而不是点源发射脉冲(声脉冲)的多孔径超声成像系统。类似地，上述系统和方法的实施例也可以有益地应用于使用多个子孔径进行声脉冲传输的单孔径成像系统。在另外的实施例中，上述方法还可以应用于使用来自单孔径探头的相控阵传输的常规超声系统。
尽管本发明已在某些优选实施例和示例的环境下公开，但本领域技术人员将理解，本发明超出了具体公开的实施例，延伸到本发明的其他备选实施例和/或本发明的用途和其明显的修改以及其等同物。对于本领域技术人员来说，对上述实施例的各种修改将是显而易见的，并且本文定义的一般原理可以应用于其他实施例，而不会偏离本发明的精神或范围。因此，旨在本文公开的本发明的范围不应受到上述特定公开的实施例的限制，而应仅通过对以下权利要求的公正解读来确定。
具体地，材料和制造技术可以在相关技术领域的技术人员的水平范围内使用。此外，对单个项的引用时，包括存在相同项的复数形式的可能性。更具体地，如本文和所附权利要求书中所使用的，单数形式“一”、“和”、“所述”和“该”包括复数指示物，除非上下文另有明确规定。如本文所用，除非另有明确说明，术语“或”包括所有提出的备选，并且本质上意味着与常用短语“和/或”相同。进一步指出，权利要求可以被起草以排除任何可选要素。因此，该陈述旨在用作使用与权利要求要素的叙述有关的诸如“单独”、“仅”等排他性术语或使用“否定”限制的先行基础。除非本文另有定义，否则本文使用的所有技术和科学术语具有与本发明所属领域的普通技术人员通常理解的相同含义。

Claims (14)

1.一种在超声成像中减少噪声的方法，包括以下步骤：
将具有多孔径超声阵列的第一未聚焦超声脉冲发射到具有一种或多种类型的组织的感兴趣区域，所述一种或多种类型的组织包括骨骼；
使用所述多孔径超声阵列的一个或多个接收元件接收来自所述感兴趣区域的回波；
对于所述一个或多个接收元件中的每一个接收元件，形成针对所述感兴趣区域中的多个像素的数字数据集；
对所有所述数字数据集进行平均；
使用包括或排除数据的预定的数学条件，应用控件以屏蔽来自所述数字数据集的数据值；
产生屏蔽数据集输出；以及
对所述屏蔽数据集输出进行波束成形，以产生一个或多个超声图像。
2.根据权利要求1所述的方法，其中所述预定的数学条件基于每个数字数据集的平均值的百分比来屏蔽数据。
3.根据权利要求1所述的方法，其中所述预定的数学条件消除了落在预定的所述平均值的百分比之外的数据。
4.根据权利要求1所述的方法，其中对所述屏蔽数据集输出进行波束成形产生一个或多个3D超声图像。
5.根据权利要求4所述的方法，其中所述预定的数学条件基于每个数字数据集的所述平均值的百分比来屏蔽数据。
6.根据权利要求1所述的方法，其中实时执行所述波束成形，并且其中可以使用新数据来改变或选择新的屏蔽数据集输出。
7.根据权利要求1所述的方法，还包括调整所述屏蔽数据值。
8.根据权利要求1所述的方法，还包括将第二未聚焦超声脉冲发射到所述感兴趣区域，并使用一个或多个接收元件接收来自所述感兴趣区域的回波。
9.根据权利要求1所述的方法，其中对所述屏蔽数据集输出进行波束成形产生所述感兴趣区域的全部图像或子集的图像。
10.根据权利要求1所述的方法，其中所述回波可以从同一阵列的一个或多个元件接收。
11.根据权利要求8所述的方法，其中所述第一未聚焦超声脉冲用比所述第二未聚焦超声脉冲更多的超声换能器发射。
12.根据权利要求8所述的方法，其中所述第二未聚焦超声脉冲比所述第一未聚焦超声脉冲更多的超声换能器发射。
13.一种在超声成像中减少噪声的方法，包括以下步骤：
将具有多孔径超声阵列的第一未聚焦超声脉冲发射到具有一种或多种类型的组织的感兴趣区域；
使用所述多孔径超声阵列的一个或多个接收元件接收来自所述感兴趣区域的回波；
形成针对第一接收元件接收到的回波的第一数字数据集；
形成针对第二接收元件接收到的回波的第二数字数据集；
标识所述第一数字数据集和所述第二数字数据集中的相似数据的组；
关联在所述第一数字数据集和所述第二数字数据集之间共享公共值的所述相似数据；
屏蔽共享公共值的数据；
将所述第一数字数据集和所述第二数字数据集中的间隙值减少到零或其他值；
产生屏蔽数据集输出；以及
对所述屏蔽数据集输出进行波束成形，以产生一个或多个超声图像。
14.一种在超声成像中减少噪声的方法，包括以下步骤：
将具有多孔径超声阵列的第一未聚焦超声脉冲发射到具有一种或多种类型的组织的感兴趣区域，所述一种或多种类型的组织包括骨骼；
使用所述多孔径超声阵列的一个或多个接收元件接收来自所述感兴趣区域的回波；
形成针对第一接收元件接收到的回波的第一数字数据集；
形成针对第二接收元件接收到的回波的第二数字数据集；
标识所述第一数字数据集和所述第二数字数据集中的相似数据的组；
关联在所述第一数字数据集和所述第二数字数据集之间共享公共值的所述相似数据；
屏蔽共享公共值的数据；
仅留下从所述第一数字数据集和所述第二数字数据集之间的间隙中保留的数据；
产生屏蔽数据集输出；以及
对所述屏蔽数据集输出进行波束成形，以产生一个或多个超声图像。
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