CN115407252A - 低场强磁共振成像 - Google Patents

低场强磁共振成像 Download PDF

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CN115407252A
CN115407252A CN202211135141.5A CN202211135141A CN115407252A CN 115407252 A CN115407252 A CN 115407252A CN 202211135141 A CN202211135141 A CN 202211135141A CN 115407252 A CN115407252 A CN 115407252A
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magnetic resonance
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詹姆士·F·登普西
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ViewRay Technologies Inc
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Abstract

描述了改进的磁共振成像***、方法、非暂态机器可读介质以及软件，所述***包括：低场强主磁体；梯度线圈组件；RF线圈***；以及控制***，该控制***被配置为在使用稀疏采样成像技术的同时从患者获取磁共振成像数据并进行处理。

Description

低场强磁共振成像
本申请是申请日为2017年6月22日、申请号为201780051306.1且发明名称为“低场强磁共振成像”的发明专利申请的分案申请。
相关申请的交叉引用
本申请要求2016年6月22日提交的标题为“MAGNETIC RESONANCE IMAGING”的美国临时申请No.62/353538的优先权权益，此处以引用的方式将该申请的公开全文并入。
技术领域
本文所描述的主题涉及用于磁共振成像以及与其关联的各种诊断和介入应用的***、方法和计算机软件。
背景技术
磁共振成像(MRI)或核磁共振成像是非侵入性成像技术，该技术使用射频脉冲、强磁场(用弱梯度场修改，该弱梯度场跨强磁场施加，以局部化并编码或解码相位和频率)以及身体组织之间的相互作用来获得来自患者身体内的平面或体积的投影、光谱信号以及图像。磁共振成像在软组织的成像方面特别有帮助，并且可以用于疾病的诊断。实时或电影MRI可以用于需要患者内的移动结构的成像的医疗状况的诊断。实时MRI还可以结合介入程序(例如放射治疗或图像引导手术)来使用，而且还可以用于这样的程序的规划。
发明内容
公开了磁共振成像***、方法以及软件。一些实施方案可以结合以下部件来使用：主磁体，该主磁体具有低场强；梯度线圈组件；RF线圈***；以及控制***，该控制***被配置为从人类患者获取磁共振成像数据并进行处理，同时使用没有并行成像的稀疏采样成像技术。
在一些变体中，主磁体的场强小于1.0特斯拉，并且在其他变体中，场强近似为0.35T。
在一些实施方案中，MRI的控制***可以被配置为使用低梯度场强(例如，低于20mT/m)，使用大翻转角(例如，大于40度)，使用将化学位移和磁敏感性伪影保持小于一毫米的RF带宽(例如，小于1800Hz的RF带宽)，使用高于75mT/m/ms的梯度切换率，和/或采用不需要移相或突变脉冲的脉冲序列。在一些实施方案中，RF线圈***可以不包括表面线圈。
磁共振成像***的控制***还可以被配置为产生(例如，每秒至少4帧的)电影MRI。
在另一个实施方案中，磁共振成像***可以与放射治疗装置集成，放射治疗装置用于人类患者的放射治疗，并且控制***还可以被配置为使用电影MRI来跟踪人类患者中的组织的位置。放射治疗装置可以是直线加速器，该直线加速器具有在例如4-6MV范围内的能量。放射治疗装置还可以是质子治疗***、重离子治疗***或放射性同位素治疗***。
磁共振成像***还可以包括分离/开孔磁体，并且被配置为允许例如借助集成到***中的机器人手术装置在分离磁体的间隙中进行手术介入。类似地，梯度线圈组件可以是分离梯度线圈组件。主磁体可以是超导磁体、非超导磁体或阻抗型磁体。主磁体可以由电池***供电。
当前主题的实施方案可以包括但不限于与这里提供的描述一致的方法以及物品和计算机程序产品，这些计算机程序产品包括有形地实现的机器可读介质，该介质可操作为使得一个或多个机器(例如，计算机等)引起实现所述特征中的一个或多个的操作。类似地，还预期计算机***，这些计算机***可以包括一个或多个处理器以及耦合到一个或多个处理器的一个或多个存储器。可以包括计算机可读存储介质的存储器可以包括、编码、存储一个或多个程序或对一个或多个程序进行其他动作，该一个或多个程序使得一个或多个处理器执行这里描述的操作中的一个或多个。与当前主题的一个或多个实施方案一致的计算机实施的方法可以由存在于单个计算***或跨多个计算***存在的一个或多个数据处理器来实施。这样的多个计算***可以连接，并且可以经由一个或多个连接(包括但不限于通过网络(例如，互联网、无线广域网、局域网、广域网、有线网络等)进行的连接、经由多个计算***中的一个或多个之间的直接连接)交换数据和/或命令或其他指令。
附图和以下描述中阐述了这里描述的主题的一个或多个变体的细节。这里描述的主题的其他特征和优点将从描述和附图且从权利要求明显。虽然为了例示性目的关于特定实施方案描述了当前公开主题的特定特征，但应容易地理解，这种特征不旨在限制。本公开之后的权利要求旨在限定所保护主题的范围。
附图说明
被包含在本说明书中且构成本说明书一部分的附图示出了这里公开的主题的某些方面，并且连同描述一起帮助说明与所公开实施方案关联的一些原理。在附图中：
图1是例示了根据本公开的某些方面的示例性磁共振成像***的简化透视图的图。
图2是例示了根据本公开的某些方面的、包含示例性介入装置的示例性磁共振成像***的简化透视图的图。
图3是根据本公开的某些方面的实时MRI引导的放射治疗的示例性方法的简化图。
具体实施方式
本公开描述了***、方法以及计算机软件，这些***、方法以及计算机软件尤其允许：高质量磁共振成像，该高质量磁共振成像具有有限的磁敏感性失真和化学位移伪影，其产生亚毫米空间准确度；高帧率电影能力，该高帧率电影能力具有适当的比吸收率(SAR)；以及支持实时2D和体积MRI引导的诊断和介入应用的能力。
图1例示了符合本公开的某些方面的磁共振成像***(MRI)100的一个实施方案。在图1中，MRI 100包括主磁体102、梯度线圈组件104以及RF线圈***106。在MRI 100内的是人类患者100可以位于上面的患者床108。MRI 100还包括下面详细讨论的控制***112。
MRI 100的主磁体102可以为如图1所示的、具有间隙116的、由支撑物114分开的圆柱形分离或开孔磁体、闭孔圆柱形配置、C形配置、双极磁体等。主磁体102可以由多种磁体类型组成，包括电磁体、永磁体、超导磁体或其组合。例如，一个组合或“混合”磁体可以包括永磁体和电磁体。主磁体102可以被配置用于任意常用场强，但优选地被配置用于低场强。在这里使用术语低场强时，它指小于1.0特斯拉的场强。在本公开的特定实施方案中，主磁体102的场强可以被配置为在0.1至0.5特斯拉的范围内，或者被配置为近似0.35特斯拉。***可以被设计为例如在主磁体的场强小于近似0.2特斯拉时使用阻抗型或永磁体或其组合。在一个实施方案中，使用(一个或多个)阻抗型磁体的***可以由直流电池***(例如，锂离子***，例如或类似于特斯拉电力墙)供电。
梯度线圈组件104包含在主磁体102的场的顶部上添加小变化磁场以允许成像数据的空间编码所需的线圈。梯度线圈组件104可以为连续的圆柱形组件、如图1所示的分离梯度线圈组件或对于所使用的特定MRI配置所需的其他设计。
RF线圈***106负责激励患者110内的氢质子的自旋并接收从患者110发出的随后信号。由此，RF线圈***106包括RF发射器部和RF接收部。图1中的实施方案包括执行RF发射和RF功能这两者的单体线圈。另选地，RF线圈***106可以在主体线圈与表面线圈之间划分发射和接收功能，或者可以在表面线圈内提供发射和接收功能这两者。图1的实施方案中描绘的RF线圈***106具有连续圆柱形形式，但也可以以分离方式来设计，使得间隙116将从患者向主磁体102的外边缘开放。
控制***112被配置为从患者110获取并处理磁共振成像数据，包括图像重构。控制***112可以包含多个子***，例如，控制梯度线圈组件104、RF线圈***106、这些***本身的一些部分的子***，以及处理从RF线圈***106接收的数据并执行图像重构的子***。
在一个有利实施方案中，控制***112被配置为使用没有并行成像的稀疏采样成像技术。在这里使用术语稀疏采样成像技术时，它指这样的图像获取和重构技术，在这样技术中，仅测量频率空间的一部分(为了本公开的目的，利用标准反向投影方法使用频率信息的50％或更少来重构图像)，并且通过优化重构图像以与被成像对象的先验知识一致同时还通常满足所重构图像的频率信息与所测量的频率信息之间的一致性来执行图像重构。由此，稀疏采样成像技术包括例如压缩感测和在美国专利申请No.62/353530中公开的体积成像技术之类的技术，该美国专利申请同此同时提交且被受让给ViewRay技术股份有限公司。
并行成像技术常用于磁共振成像中，特别是对于电影MRI，以缩短数据获取所需的时间。并行成像方法使用由多个RF检测器(例如具有这些“元件”的阵列的表面线圈)接收的信号的空间分布的知识来代替MRI过程中的一些耗时的相位编码步骤。这样，“并行地”从多个线圈元件接收信号，并且由来自所有线圈元件的数据的二重性(duplicity)补偿沿着读出轨迹的k空间中的较少部分的采样(即，较少的相位编码)。
然而，本公开的某些实施方案预期不使用并行成像技术的数据获取和处理。在本公开提及“没有并行成像”的磁共振数据获取和处理的这样的情况下，它预期***、方法以及计算机软件被设计为包含少量并行成像(可能为了避免侵权)，但不足以产生信噪比的在感知上的显著增大，所有其他东西不变。
在一些有利的实施方案中，MRI和控制***112可以被配置为使用低梯度场强(例如，低于20mT/m，或在其他情况下，低于12mT/m)。另外，一些有利实施方案可以使用相对高的梯度切换率(slew rate)或上升时间，例如高于75mT/m/ms的切换率。控制***112还可以被有利地配置为使用大翻转角(flip angle)，例如，大于40度。另外，控制***112可以被有利地配置为采用不需要移相脉冲(dephasing pulse)的脉冲序列(预期这样的脉冲序列不具有移相脉冲，或者仅具有少量的移相或突变脉冲(spoiling pulse)，使得从患者处理量的角度来看没有数据获取时间的显著增加)。
在一些实施方案中，控制***112可以被配置为使用RF带宽以将化学位移和磁敏感性伪影保持低于一毫米甚至低于半毫米。作为示例，控制***112可以被配置为小于1800Hz的RF带宽。可以评估由于磁敏感性和化学位移引起的潜在最坏情况的伪影。例如，对于在人类敏感性评定中观察到的例如8ppm扰动的最坏情况，下面的公式【1】可以用于估计磁敏感性伪影。
Figure BDA0003851211770000061
这里，δms[mm]是由于磁敏感性伪影引起的单位为毫米的空间失真，其由于磁敏感性引起的磁场变化而产生，mag.suscept.[ppm]为主磁场强度(Bo[T]，单位为特斯拉)的百万分率，并且其中，Ge[T/mm]是单位为特斯拉每毫米的梯度编码强度。
并且，下面的公式【2】可以用于估计由于化学位移引起的位移。
Figure BDA0003851211770000062
这里，δcs[mm]是由于化学位移伪影引起的单位为毫米的空间失真，其中，3.5[ppm]是对于单位为毫米的像素或体素尺寸PixelSize的、结合到氧的氢(H-O)对结合到碳的氢(C-H)的拉莫尔(Larmour)频率的相对百万分率差，并且fBo是水中氢的拉莫尔频率，并且BW[Hz/pixel]是单位为赫兹每像素或体素的、像素或体素的频率带宽。
最坏情况的失真可以被当作这两个失真加由于未校正梯度场非线性产生的任意残余失真的和。
在本公开的磁共振成像***100的一个特定实施方案中，主磁体102场强近似为0.35特斯拉，并且控制***112被配置为使用低于12mT/m的梯度场强、高于75mT/m/ms的梯度切换率、大于40度的翻转角、小于1800Hz的RF带宽以及不包含移相脉冲的脉冲序列。控制***112还可以被配置为使用没有并行成像的稀疏采样成像技术。
在磁共振成像***100的另一个特定实施方案中，主磁体102场强近似为0.15特斯拉，并且控制***112被配置为使用低于10mT/m的梯度场强、高于75mT/m/ms的梯度切换率、大于60度的翻转角、小于1000Hz的RF带宽以及不包含移相脉冲的脉冲序列。在该实施方案中，控制***112还可以被配置为使用没有并行成像的稀疏采样成像技术。
如这里进一步讨论的，本公开的***、方法以及计算机软件的某些实施方案可以对于电影平面、电影多平面、或实时体积或“4D”(3D空间加时间维度)磁共振成像有利。由此，控制***112可以被配置为获取并处理重构图像来产生电影MRI所需的数据，例如，在保持患者110中的可接受比吸收率的同时实现至少每秒4帧的电影MRI。
传统观点是由于较高信噪比而始终优选高主磁体场强，期望的场强主要受尺寸和成本考虑限制。通过较高的信噪比、对比度以及分辨率，较高的场强通常促进提高使医生基于产生图像进行诊断的能力。然而，使用低主磁体场强(例如，低于1.0特斯拉)的本公开的实施方案产生高质量图像并提供多个附加的益处。
例如，本公开的实施方案可以包括小于1800Hz的RF带宽，这引起减小的化学位移伪影(即，其中，在使诸如水和脂肪的不同化学环境中的氢原子由于在O-H和C-H化学键中涉及的电子的共享的差异而部分相对于主磁场被屏蔽并且因此具有不同的核磁共振化学位移的情况，在用频率编码定位信号时出现在不同的空间位置中)。高场***将展示显著的化学位移伪影且需要较高的RF带宽(及其伴随的较低信噪比)，而这里公开的低场***可以使用较低的RF带宽并保持高空间完整性。
另外，高主磁场强***将展示被成像对象的抗磁和顺磁(并且在罕见情况下为铁磁)性质扰乱磁场的显著磁敏感性伪影，这导致空间失真图像。较高场***中的这样的问题通常可以借助梯度场强的增大来解决，但本公开的实施方案避免相同水平的伪影，由此，可以使用较低的梯度场强，这导致改善的信噪比和较低的比吸收率。
而且，这里讨论的***、方法以及软件可以在没有并行成像的情况下实施，这将引起产生的图像的会随着成像速度而增大的信噪比的减小。相反，这里公开的稀疏采样技术例如借助在扫描前使用获取的先验数据、避免使用“网格化”k空间数据并应用迭代优化技术来允许具有不随图像获取速度显著减小的相对高的信噪比的高帧率获取。在没有并行成像时还可以避免相控阵列接收线圈的使用，从而用较不复杂技术实现高质量成像。可以连同较便宜的光谱仪一起使用较少的RF接收通道，实际上，可以仅使用单个RF接收通道。
本公开的某些实施方案还可以在没有与患者接触的表面线圈的情况下采用。相反，成像可以仅用集成到包含发射和接收线圈的MRI的孔中的体线圈来执行。
另外，可以有利地采用同时多切片成像技术，其中，可以同时激励并同时读出多个成像切片或子体积。同时多切片激励的一个实施方案可以对具有不同相位调制函数的多个RF波形求和，这产生多带脉冲，该多带脉冲可以在存在公共切片选择梯度时激励期望的切片。
此外，本公开的实施方案可以使用相对高的翻转角，这些翻转角在较高的主磁体场强下将引起过度的患者加热。在本公开的实施方案中的较高翻转角将引起图像对比度和信噪比改善。
另外，这里讨论的低主磁体场强实施方案将展示更快的RF信号衰减，这允许不需要移相脉冲的脉冲序列(具有较低比吸收率的伴随优点)。
本公开的某些实施方案的低主磁体场强还允许较低频率RF激励脉冲，由此允许由这些脉冲引起的患者组织的加热减少。
进一步地，由本公开的实施方案展示的良好受控的比吸收率提供以对于高帧率电影MRI足够的速度来获取并处理数据的能力。
凭借上述众多优点，本公开的实施方案非常适于具有可接受的患者比吸收率的高质量电影MRI。这些实施方案还控制磁敏感性和化学位移伪影，以便提供在某些诊断和介入应用中可能是关键的高空间完整性。
本公开的实施方案在用于诊断电影MRI的大量应用中可以是有利的，示例包括解剖***、用于定位和移动(例如，发声)研究的重复快速成像、对自由移动对象成像(例如，胎儿MRI)、心脏成像等。
本公开的实施方案在介入应用中也可以是有利的，这些介入应用也受益于高空间完整性和受控的比吸收率的优点。介入应用的示例包括血管成形术、支架输送、血栓溶解、动脉瘤修复、椎体成形、子宫肌瘤栓塞治疗以及当前使用荧光镜检查(并且电影MRI的使用将降低到患者的放射剂量)的许多其他应用。
本公开的实施方案还可以用于图像引导手术，并且可以提供多个正交平面中的实时程序内引导、关于仪器位置的成像反馈、引导和/或警告***等。与图1所描绘的开孔MRI实施方案类似(但具有分离RF线圈***106)的开孔MRI实施方案对于这种介入程序可能特别有利。由此，MRI 100可以被配置为允许在分离磁体的间隙中的手术介入，并且还可以包括与***集成的机器人手术装置。
伴随本公开的某些实施方案的低场强的又一个优点是减小的磁力，该磁力将被施加在连同MRI 100而被使用的任何介入设备(诸如机器人手术设备、活组织检查仪器、低温消融单元、短距离放射治疗设备、放射治疗设备等)上。
在磁共振成像***100的一个实施方案中，结合介入设备(诸如直线加速器的放射治疗设备)，使用低场强非超导磁体，例如，阻抗型磁体、永磁体或混合磁体。
本公开的某些实施方案的另一个有益应用是在图像引导放射治疗领域中。放射治疗应用也将受益于本公开的提供具有高空间完整性的高帧率电影MRI的能力，高帧率电影MRI和高空间完整性这两者对准确跟踪被治疗目标并避免用大量离子化放射照射患者关键结构是关键的。
图2例示了还被配置为集成治疗患者110的放射治疗装置的MRI 100。在一个实施方案中，MRI 100可以包括被定位在开孔MRI的间隙116中的门架202。门架202可以结合有放射治疗装置204，该放射治疗装置被配置为朝向患者110引导放射治疗束206。在一个特定实施方案中，放射治疗装置204可以是具有在4-6MV范围内的能量的直线加速器，并且如所描绘的，直线加速器的部件可以被分成围绕门架202隔开的单独屏蔽容器208。这些直线加速器部件然后可以通过RF波导210连接。虽然图2描绘了特定放射治疗装置布置，但本公开预期任意类型的放射治疗***(诸如质子治疗、重离子治疗、放射性同位素治疗等)的集成。
如上所述，磁共振成像***100的控制***112可以被配置用于电影MRI，并且还被配置为使用电影MRI来跟踪人类患者110中的组织的位置。
使用具有低场强的主磁体102的本公开的实施方案的另外益处是减小由于作用在次级电子(和正电子)的运输上的洛伦兹(Lorenz)磁力引起的患者110中的所递送离子化放射剂量分布的失真。由较高场主磁体施加的洛伦兹磁力将使电子(和正电子)的散射能力过度，并且使得它们甩出它们的自然路线，将它们诱捕在低密度界面处，这潜在地导致患者中的意外且有害的剂量浓度。
图3中例示了符合本公开的实施方案的实时图像引导放射治疗的示例性方法。在302处，可以借助磁共振成像***100从人类患者110获取磁共振成像数据，该***具有：超导主磁体，该主磁体具有低场强；梯度线圈组件104；以及RF线圈***106，其中，获取使用没有并行成像的稀疏采样成像技术。在304处，处理磁共振成像数据。在306处，向人类患者110施予放射治疗。在308处，使用磁共振成像数据来跟踪患者110中的(一个或多个)组织的位置。并且在310处，可以基于患者110中的(一个或多个)组织的位置的跟踪改变放射治疗的施予。在改变的治疗中，预期诸如停止治疗、重新优化治疗、调整放射治疗束等的动作。图3所例示的示例性方法还可以包含上述特性(例如，低梯度场强、大翻转角、保持空间完整性的RF带宽、特定脉冲序列等)中的任意一个或全部。
在本公开指示磁共振成像***被配置为以特定方式操作时，它意指这样的***被设置并预期为以该方式操作，而不管它是否还可以被配置为使用(一个或多个)脉冲序列或不以这里描述或要求保护的方式操作的配置。
本公开预期在这里的实施方式中公开的计算可以应用这里示教的相同构思以多种方式来执行，并且这样的计算等效于所公开的实施方式。
这里描述的主题的一个或多个方面或特征可以在数字电子电路、集成电路、专门设计的专用集成电路(ASIC)、现场可编程门阵列(FPGA)计算机硬件、固件、软件和/或其组合中实现。这些各种方面或特征可以包括可在可编程***上执行和/或解释的一个或多个计算机程序中的实施方案，可编程***包括可以为专用或通用的至少一个可编程处理器，该至少一个可编程处理器被耦合为从存储***、至少一个输入装置以及至少一个输出装置接收数据和指令和向其发送数据和指令。可编程***或计算***可以包括客户端和服务器。客户端和服务器通常远离彼此，并且通常借助通信网络交互。客户端和服务器的关系借助于计算机程序出现，并且这些计算机程序运行在各计算机上并且具有到彼此的客户端-服务器关系。
这些计算机程序(还可以被称为程序、软件、软件应用、应用、部件、或代码)包括用于可编程处理器的机器指令，并且可以用高级过程语言、面向对象的编程语言、函数编程语言、逻辑编程语言、和/或用汇编/机器语言来实现。如这里使用的，术语“机器可读介质”(或“计算机可读介质”)指用于向可编程处理器(包括接收机器指令作为机器可读信号的机器可读介质)提供机器指令和/或数据的任意计算机程序产品、设备和/或装置，诸如例如，磁盘、光盘、存储器、以及可编程逻辑装置(PLD)。术语“机器可读信号”(或“计算机可读信号”)指用于向可编程处理器提供机器指令和/或数据的任意信号。机器可读介质可以非暂态存储这种机器指令，诸如例如如将为非暂态固态存储器或磁硬盘驱动器或任意等效存储介质。另选地或另外地，机器可读介质可以以暂态方式存储这种机器指令，诸如例如如将为处理器缓存或与一个或多个物理处理器核心关联的其他随机存取存储器。
为了提供与用户的交互，这里描述的主题的一个或多个方面或特征可以在计算机上实施，该计算机具有：显示装置，该显示装置用于向用户显示信息，诸如例如阴极射线管(CRT)或液晶显示器(LCD)或发光二极管(LED)监测器；以及键盘和指向装置，诸如例如鼠标或跟踪球，用户可以由该键盘和指向装置向计算机提供输入。还可以使用其他种类的装置来提供与用户的交互。例如，向用户提供的反馈可以为任意形式的感觉反馈，诸如例如，视觉反馈、听觉反馈、或触觉反馈；并且来自用户的输入可以以任意形式接收，包括但不限于声、语音或触觉输入。其他可能的输入装置包括但不限于触摸屏或其他触敏装置，诸如单或多点电阻或电容跟踪垫、语音识别硬件和软件、光学扫描仪、光学指针、数字图像捕捉装置和关联的解释软件等。
在以上描述和权利要求中，诸如“……中的至少一个”或“……中的一个或多个”的短语可以出现，后面是元件或特征的连接列表。术语“和/或”也可以出现在两个或更多个元件或特征的列表中。除非另外由使用短语的语境含蓄或明确地否定，否则这种短语旨在意指所列元件或特征中独立的任意一个或与其他所列元件或特征中的任意一个组合的、所列元件或特征的任意一个。例如，短语“A和B中的至少一个”、“A和B中的一个或多个”以及“A和/或B”各旨在意指“A独自、B独自或A和B一起”。类似的解释也旨在用于包括三项或更多项的列表。例如，短语“A、B以及C中的至少一个”、“A、B以及C中的一个或多个”以及“A、B和/或C”各旨在意指“A独自、B独自、C独自、A和B一起、A和C一起、B和C一起、或A和B和C一起”。上面和权利要求中的术语“基于”的使用旨在意指“至少部分基于”，使得未列举的特征或元件也是可允许的。
这里描述的主题可以取决于期望配置而在***、设备、方法、计算机程序和/或物品中具体实施。附图中描绘和/或这里描述的任意方法或逻辑流程不是必须需要所示的特定顺序或先后次序来实现期望的结果。前面描述中阐述的实施方案不表示符合这里描述的主题的所有实施方案。相反，它们仅是符合与所述主题有关的方面的一些示例。虽然上面已经详细描述了一些变体，但其他修改或添加是可以的。具体地，除了这里阐述的特征和/或变体之外，还可以提供另外的特征和/或变体。上述实施方案可以致力于所公开特征的各种组合和子组合和/或以上注释的另外特征的组合和子组合。此外，上述优点不旨在将任何所发布权利要求的应用限于伴随优点中的任何一个或全部的处理和结构。
另外，章节标题不应限制在可以从本公开发行的任何权利要求中阐述的本发明或描述其特征。具体地且用示例的方式，虽然标题提及“技术领域”，但这种权利要求不应受该标题下被选择为描述所谓技术领域的语言限制。进一步地，“背景技术”中的技术的描述不被解释为技术是本公开中的任意发明的现有技术的承认。“发明内容”也不被认为是所发行权利要求中阐述的本发明的特征描述。此外，对一般的本公开的任意参考或单数形式的词语“发明”的使用不旨在暗示对下面阐述的权利要求的范围的任何限制。可以根据从本公开发行的多个权利要求的限制阐述多个发明，因此，这种权利要求限定保护的发明及其等同物。

Claims (26)

1.一种磁共振成像***(MRI)，所述磁共振成像***包括：
主磁体，该主磁体具有小于1.0特斯拉的场强；
梯度线圈组件；
RF线圈***；以及
控制***，该控制***被配置为从人类患者获取磁共振成像数据并处理该磁共振成像数据，并且被配置为使用没有并行成像的稀疏采样成像技术并产生电影MRI同时保持人类患者中的可接受比吸收率。
2.根据权利要求1所述的磁共振成像***，其中，所述控制***还被配置为以能够以每秒至少4帧的速率产生所述电影MRI的速率获取磁共振成像数据。
3.根据权利要求1所述的磁共振成像***，其中，所述控制***还被配置为部分地通过控制MRI以高于75mT/m/ms的梯度场强操作来获得所述比吸收率。
4.根据权利要求1所述的磁共振成像***，其中，所述控制***还被配置为部分地通过采用不需要移相脉冲的脉冲序列来获得所述比吸收率。
5.根据权利要求1所述的磁共振成像***，还包括与所述***集成的放射治疗装置，所述放射治疗装置被配置为用于人类患者的放射治疗。
6.根据权利要求5所述的磁共振成像***，其中，所述控制***还被配置为使用所述电影MRI来跟踪人类患者中的组织的位置。
7.根据权利要求1所述的磁共振成像***，其中，所述控制***还被配置为使RF带宽小于1800Hz。
8.一种存储指令的非暂态机器可读介质，所述指令在由至少一个可编程处理器执行时，使得所述至少一个可编程处理器执行操作，所述操作包括：
借助磁共振成像***(MRI)从人类患者获取磁共振成像数据，该磁共振成像***具有：主磁体，该主磁体具有低场强；梯度线圈组件；以及RF线圈***，所述获取使用没有并行成像的稀疏采样成像技术并同时保持人类患者中的可接受比吸收率；和
处理所述磁共振成像数据，所述处理包括重构人类患者的图像和产生电影MRI。
9.根据权利要求8所述的非暂态机器可读介质，其中，所述电影MRI的产生以每秒至少4帧的速率进行。
10.根据权利要求8所述的非暂态机器可读介质，其中，部分地通过控制MRI以高于75mT/m/ms的梯度场强操作来获得所述比吸收率。
11.根据权利要求8所述的非暂态机器可读介质，其中，部分地通过采用不需要移相脉冲的脉冲序列来获得所述比吸收率。
12.根据权利要求8所述的非暂态机器可读介质，还包括向人类患者施予放射治疗。
13.根据权利要求12所述的非暂态机器可读介质，还包括基于利用电影MRI跟踪人类患者中的组织的位置来改变放射治疗的施予。
14.根据权利要求8所述的非暂态机器可读介质，所述操作还包括利用小于1800Hz的RF带宽。
15.一种磁共振成像***(MRI)，所述磁共振成像***包括：
主磁体，该主磁体具有小于1.0特斯拉的场强；
梯度线圈组件；
RF线圈***；以及
控制***，该控制***被配置为从人类患者获取磁共振成像数据并处理该磁共振成像数据，并且被配置为使用没有并行成像的稀疏采样成像技术并采用同时多切片成像技术。
16.根据权利要求15所述的磁共振成像***，其中，所述多切片成像技术包括同时激励并同时读出多个成像切片或子体积。
17.根据权利要求16所述的磁共振成像***，所述控制***被配置为产生公共切片选择梯度并产生多带脉冲以在存在所述公共切片选择梯度时激励多个成像切片或子体积。
18.根据权利要求15所述的磁共振成像***，所述多切片成像技术包括对具有不同相位调制函数的多个RF波形求和来产生多带脉冲。
19.根据权利要求15所述的磁共振成像***，其中，所述控制***还被配置为使RF带宽小于1800Hz。
20.根据权利要求15所述的磁共振成像***，其中，所述控制***被配置为采用不需要移相脉冲的脉冲序列。
21.一种存储指令的非暂态机器可读介质，所述指令在由至少一个可编程处理器执行时，使得所述至少一个可编程处理器执行操作，所述操作包括：
借助磁共振成像***(MRI)从人类患者获取磁共振成像数据，该磁共振成像***具有：主磁体，该主磁体具有低场强；梯度线圈组件；以及RF线圈***，所述获取使用没有并行成像的稀疏采样成像技术并采用同时多切片成像技术；和
处理所述磁共振成像数据，所述处理包括重构人类患者的图像。
22.根据权利要求21所述的非暂态机器可读介质，所述操作还包括激励并同时读出多个成像切片或子体积。
23.根据权利要求22所述的非暂态机器可读介质，所述操作还包括：
产生公共切片选择梯度；和
产生多带脉冲以在存在所述公共切片选择梯度时激励所述多个成像切片或子体积。
24.根据权利要求21所述的非暂态机器可读介质，所述操作还包括通过对具有不同相位调制函数的多个RF波形求和来产生多带脉冲。
25.根据权利要求21所述的非暂态机器可读介质，其中，所述控制***还被配置为使RF带宽小于1800Hz。
26.根据权利要求21所述的非暂态机器可读介质，其中，所述获取采用不需要移相脉冲的脉冲序列。
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