WO2017113177A1 - 高强度聚焦超声损伤判定方法及装置 - Google Patents

高强度聚焦超声损伤判定方法及装置 Download PDF

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WO2017113177A1
WO2017113177A1 PCT/CN2015/099843 CN2015099843W WO2017113177A1 WO 2017113177 A1 WO2017113177 A1 WO 2017113177A1 CN 2015099843 W CN2015099843 W CN 2015099843W WO 2017113177 A1 WO2017113177 A1 WO 2017113177A1
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displacement
magnetic resonance
treatment
tissue
coding gradient
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PCT/CN2015/099843
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English (en)
French (fr)
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郑海荣
刘新
乔阳紫
邹超
帖长军
刘孟潇
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深圳先进技术研究院
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Priority to CN201580001252.9A priority Critical patent/CN107249690B/zh
Priority to PCT/CN2015/099843 priority patent/WO2017113177A1/zh
Publication of WO2017113177A1 publication Critical patent/WO2017113177A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy

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  • the invention relates to the field of biomedical engineering technology, in particular to a method and a device for determining high-intensity focused ultrasound damage.
  • High-intensity focused ultrasound can use ultrasonic penetration and energy deposition to concentrate low-energy ultrasound in vitro on target tissues at specific depths, so that the temperature in the focal region rises rapidly to 60 °C, triggering protein denaturation. And tissue coagulative necrosis without damaging surrounding normal tissue, HIFU treatment has gradually developed into an important tumor treatment.
  • Image guidance, monitoring and treatment evaluation during high-intensity focused ultrasound therapy are the basic guarantee for safe treatment of focused ultrasound and the basis for efficient, precise and personalized treatment.
  • the commonly used methods for evaluating the effect of high-intensity focused ultrasound therapy include:
  • T1-W, T2-W, etc. Damage detection based on tissue T1, T2, proton density: T1-W, T2-W, etc. are common sequences for magnetic resonance monitoring of high-intensity focused ultrasound therapy.
  • tissues T1, T2 and The proton density value will change.
  • these parameters are also affected by temperature, such as tissue T1 values increasing with increasing temperature. Therefore, when the damage is judged based on the tissues T1, T2 and the proton density, in order to determine whether or not the deterministic tissue has undergone necrosis or the image signal change caused by the temperature influence, the temperature caused by the high-intensity focused ultrasound needs to be diffused to the heat balance.
  • the principle of ultrasound elastography is to apply an internal or external dynamic or static/quasi-static pressure to the tissue.
  • the signal processing is used to extract the tissue displacement.
  • Information information about organizational strain can be obtained, which indirectly reflects the elastic modulus of the organization.
  • Magnetic Resonance Imaging has become the best for focused ultrasound therapy monitoring due to its multi-dimensional stereo imaging, unique temperature monitoring, and various tissue contrasts. One of the means.
  • the steps of magnetic resonance elastography are mainly as follows: 1. A set of magnetic resonance compatible excitation sources is needed to generate shear waves with a frequency of 50 Hz to 500 Hz in the tissue; 2. The tissue is displaced in the magnetic resonance phase diagram by adding a motion sensitive gradient. Coding on, the phase diagram and tissue displacement are as follows:
  • ⁇ is the tissue motion and the gradient field is applied at the location
  • the phase produced ⁇ is the phase difference between the tissue motion and the motion-sensitive gradient
  • N is the logarithm of the motion-sensitive gradient used, T
  • the length and amplitude of the motion-sensitive gradient, ⁇ 0 is the maximum displacement, It is the wave number; 3.
  • the data is processed to obtain the quantitative distribution result of the tissue elasticity.
  • Damage detection based on tissue T1, T2, proton density affected by temperature, it is necessary to wait until the temperature in the tissue returns to the heat equilibrium temperature, can quickly determine whether the tissue has necrosis, or the image signal change feedback caused by temperature influence;
  • Damage detection based on ultrasound elastography the resolution of the ultrasound image itself is significantly lower than that of the magnetic resonance image, which directly affects the accuracy of the judgment.
  • image resolution of high-frequency ultrasound is relatively high, but the propagation distance of high-frequency ultrasound in the tissue is limited, which makes ultrasound elastography more suitable for superficial organ diagnosis;
  • Damage detection based on magnetic resonance elastography a complex external excitation source is required, and the shear wave generated by the excitation source has the same problem as ultrasound elastography: spatial resolution increases with frequency, but high frequency shear Wave attenuation is fast and the propagation distance is limited.
  • reconstruction of magnetic resonance elastography requires solving a Helmholtz problem, which is highly susceptible to noise.
  • the embodiment of the invention provides a method for determining high-intensity focused ultrasound damage, which is not affected by temperature, and can realize whether a rapid quasi-deterministic tissue has necrosis; no complicated external excitation source is needed, and is not susceptible to noise; the operation method is simple, It does not generate additional heat and damage to the tissue, and the detection method is safe.
  • the method includes:
  • the lesion tissue is determined to be damaged.
  • the embodiment of the invention further provides a high-intensity focused ultrasound damage determining device, which adopts the device of the invention to determine the high-intensity focused ultrasonic damage, which is not affected by the temperature, and can realize whether the rapid quasi-deterministic tissue has necrosis; no complicated external is needed
  • the excitation source is not susceptible to noise; the operation is simple, no additional heat and damage are generated to the tissue, and the detection method is safe.
  • the device includes:
  • a sequence obtaining module for obtaining a magnetic resonance acoustic radiation force displacement detecting sequence before and after treatment of the diseased tissue by using high-intensity focused ultrasound;
  • a first displacement determining module configured to add a motion coding gradient to the pre-treatment magnetic resonance acoustic radiation force displacement detection sequence, and determine a displacement of the diseased tissue before the treatment according to a phase change of the magnetic resonance phase map obtained before and after adding the motion coding gradient ;
  • a second displacement determining module configured to add a motion coding gradient to the post-treatment magnetic resonance acoustic radiation force displacement detection sequence, and determine a displacement of the diseased tissue after the treatment according to a phase change of the magnetic resonance phase map obtained before and after adding the motion coding gradient ;
  • the damage determination module is configured to determine the lesion tissue damage when the displacement difference of the displacement in the diseased tissue before and after the treatment is greater than a preset threshold.
  • the motion coding gradient is added to the magnetic resonance sound radiation force displacement detection sequence before and after the treatment, and the phase change of the magnetic resonance sound radiation force displacement detection sequence before and after the motion coding gradient is added to determine the treatment.
  • Displacement of the diseased tissue before and after treatment when the displacement difference of the displacement in the diseased tissue before and after treatment is greater than a predetermined threshold, the lesion tissue is determined to be damaged.
  • the method is not affected by temperature, and can realize rapid quasi-deterministic tissue necrosis; no complicated external excitation source is needed, and is not easily affected by noise; the operation method is simple, no additional heat and damage are generated to the tissue, and the detection method is safe.
  • FIG. 1 is a flow chart of a method for determining high-intensity focused ultrasound damage according to an embodiment of the present invention
  • FIG. 2 is a schematic view showing the detection of displacement in tissue before treatment according to an embodiment of the present invention
  • FIG. 3 is a schematic view showing the tissue displacement detection after treatment (immediately) in the embodiment of the present invention.
  • FIG. 5 is a timing chart of an acoustic radiation force displacement detecting sequence used in an embodiment of the present invention.
  • FIG. 6 is a tissue displacement curve before and after high-intensity focused ultrasound heating in the absence of damage in the embodiment of the present invention
  • Figure 8 is a diagram showing the displacement curve of the tissue before and after high-intensity focused ultrasound heating in the wound tissue of the pork in the embodiment of the present invention.
  • Figure 9 is a graph showing the maximum temperature change at the focus in the embodiment of the present invention.
  • Figure 10 is a diagram showing the displacement curve of the tissue before and after high-intensity focused ultrasound heating in the bovine liver tissue in the embodiment of the present invention.
  • Figure 11 is a graph showing the maximum temperature change at the focus in the embodiment of the present invention.
  • Fig. 12 is a structural schematic view showing a high-intensity focused ultrasonic damage determining apparatus in an embodiment of the present invention.
  • the existing high-intensity focused ultrasound treatment evaluation method will be affected by temperature, and it is necessary to wait until the temperature in the tissue returns to the heat equilibrium temperature to judge the therapeutic effect; the external excitation source is required to detect the tissue elasticity change; it is highly susceptible to noise. The impact and so on.
  • the invention provides a method and a device for determining high-intensity focused ultrasound damage, which can overcome the disadvantages existing in the prior art.
  • FIG. 1 is a flow chart of a method for determining high-intensity focused ultrasound damage according to an embodiment of the present invention. As shown in FIG. 1, the method includes the following steps:
  • Step 101 Obtain a magnetic resonance acoustic radiation force displacement detecting sequence before and after treatment of the diseased tissue by using high-intensity focused ultrasound;
  • Step 102 adding a motion coding gradient to the magnetic resonance acoustic radiation force displacement detection sequence before the treatment, and determining the displacement of the diseased tissue before the treatment according to the phase change of the magnetic resonance phase map obtained before and after adding the motion coding gradient;
  • Step 103 adding a motion coding gradient to the magnetic resonance acoustic radiation force displacement detection sequence after the treatment, and determining the displacement of the diseased tissue after the treatment according to the phase change of the magnetic resonance phase map obtained before and after adding the motion coding gradient;
  • Step 104 Determine the lesion tissue damage when the displacement difference of the displacement in the diseased tissue before and after the treatment is greater than a preset threshold.
  • a motion coding gradient is added to the magnetic resonance acoustic radiation force displacement detection sequence, and the displacement caused by the tissue under the action of the ultrasound is converted into the phase change of the magnetic resonance image, and the displacement in the tissue is quantified based on the following formula:
  • ⁇ x is the displacement within the diseased tissue
  • ⁇ is the phase difference of the magnetic resonance image acquired before and after the addition of the motion coding gradient
  • G e is the intensity of the motion coding gradient
  • ⁇ is the duration of the motion coding gradient
  • ⁇ is the magnetic rotation ratio
  • Fig. 2 and Fig. 3 are schematic diagrams showing the displacement detection in the tissue before and after treatment, respectively, and it can be seen that there is a significant change in the displacement.
  • Figure 4 is a temperature profile during treatment with the temperature increasing continuously.
  • the magnetic resonance acoustic radiation force displacement detecting sequence may adopt a plane echo sequence, a one-dimensional linear scan sequence, a two-bit spin echo sequence, a single-shot plane echo sequence, and the like.
  • the displacement coding gradient may employ a repeated bipolar displacement coding gradient, a unipolar displacement coding gradient, a bipolar inverse displacement coding gradient, and the like.
  • the specific implementation is that the displacement distribution in the tissue is collected before and after the high-intensity focused ultrasound treatment, and multiple sets of displacement distribution results can be collected as needed to ensure the accuracy of the detection. Temperature monitoring can be performed with gradient echo sequences during high-intensity focused ultrasound therapy.
  • the appropriate threshold is selected. When there is a significant difference in tissue displacement before and after treatment, and the displacement difference is greater than the threshold, it can be determined that the tissue has necrosis, thus achieving the damage area. Depiction.
  • the acoustic radiation force displacement detection sequence used in this experiment is a segmented readout plane echo sequence.
  • the bipolar motion coding gradient is added to the sequence to encode the tissue displacement.
  • the sequence timing is shown in Figure 5.
  • the gradient intensity is 32mT/m
  • the motion coding gradient is 10ms long
  • an embodiment of the present invention further provides a high-intensity focused ultrasound damage determining apparatus, as described in the following embodiments. Since the principle of solving the problem by the high-intensity focused ultrasound damage determination device is similar to that of the high-intensity focused ultrasound damage determination method, the implementation of the high-intensity focused ultrasound damage determination device can be referred to the implementation of the high-intensity focused ultrasound damage determination method, and the repetition will not be repeated. .
  • the term "unit” or “module” may implement a combination of software and/or hardware of a predetermined function.
  • the apparatus described in the following embodiments is preferably implemented in software, hardware, or a combination of software and hardware, is also possible and contemplated.
  • FIG. 12 is a structural block diagram of a high-intensity focused ultrasound damage determining apparatus according to an embodiment of the present invention, as shown in FIG. 12, including:
  • the sequence obtaining module 1201 is configured to obtain a magnetic resonance acoustic radiation force displacement detecting sequence before and after treatment of the diseased tissue by using high-intensity focused ultrasound;
  • the first displacement determining module 1202 is configured to add a motion coding gradient to the magnetic resonance sound radiation force displacement detection sequence before the treatment, and determine the pathological tissue before the treatment according to the phase change of the magnetic resonance phase map obtained before and after the motion coding gradient is added. Displacement
  • the second displacement determining module 1203 is configured to add a motion coding gradient to the magnetic resonance acoustic radiation force displacement detection sequence after the treatment, and determine the diseased tissue after the treatment according to the phase change of the magnetic resonance phase map obtained before and after the motion coding gradient is added. Displacement
  • the damage determination module 1204 is configured to determine the lesion tissue damage when the displacement difference of the displacement in the diseased tissue before and after the treatment is greater than a preset threshold.
  • first displacement determining module 1202 and the second displacement determining module 1203 are specifically configured to:
  • ⁇ x is the displacement within the diseased tissue
  • ⁇ is the phase difference of the magnetic resonance image acquired before and after the addition of the motion coding gradient
  • G e is the intensity of the motion coding gradient
  • ⁇ is the duration of the motion coding gradient
  • ⁇ is the magnetic rotation ratio
  • the magnetic resonance acoustic radiation force displacement detecting sequence is a plane echo sequence, a one-dimensional linear scan sequence, a two-bit spin echo sequence or a single-shot plane echo sequence.
  • the displacement coding gradient is a repeated bipolar displacement coding gradient, a unipolar displacement coding gradient or a bipolar reverse displacement coding gradient.
  • the present invention has the following advantages:
  • the method can detect the change of tissue elasticity without adding an excitation source
  • the method is simple to operate, and the therapeutic effect can be judged without waiting for the temperature in the tissue to return to the heat equilibrium temperature;
  • the method is compatible with a plurality of acoustic radiation force displacement detecting sequences
  • the method only needs millisecond-level high-intensity focused ultrasound pulse, which is not easy to cause temperature rise in the tissue, and the detection method is safe.
  • embodiments of the present invention can be provided as a method, system, or computer program product. Accordingly, the present invention may take the form of an entirely hardware embodiment, an entirely software embodiment, or a combination of software and hardware. Moreover, the invention can take the form of a computer program product embodied on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) including computer usable program code.
  • computer-usable storage media including but not limited to disk storage, CD-ROM, optical storage, etc.
  • the computer program instructions can also be stored in a computer readable memory that can direct a computer or other programmable data processing device to operate in a particular manner, such that the instructions stored in the computer readable memory produce an article of manufacture comprising the instruction device.
  • the apparatus implements the functions specified in one or more blocks of a flow or a flow and/or block diagram of the flowchart.
  • These computer program instructions can also be loaded onto a computer or other programmable data processing device such that a series of operational steps are performed on a computer or other programmable device to produce computer-implemented processing for execution on a computer or other programmable device.
  • the instructions provide steps for implementing the functions specified in one or more of the flow or in a block or blocks of a flow diagram.

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Abstract

一种高强度聚焦超声损伤判定方法及装置，包括：S101、获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；S102，S103、分别在治疗前和治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前和治疗后的病变组织内位移；S104、当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。该方法不受温度的影响，可实现快速准确定性组织是否已发生坏死；无需复杂的外部激励源，不易受噪声影响；操作方法简单，不会对组织产生附加的热量及损伤，检测方法安全。

Description

高强度聚焦超声损伤判定方法及装置 技术领域
本发明涉及生物医学工程技术领域，尤其一种高强度聚焦超声损伤判定方法及装置。
背景技术
高强度聚焦超声(High intensity focused ultrasound，HIFU)可利用超声波的穿透性和能量沉积性将体外低能量超声波汇聚于特定深度的靶组织，使焦域内温度迅速升高至60℃，引发蛋白质变性和组织凝固性坏死，而不损伤周围正常组织，HIFU治疗已逐渐发展为一种重要的肿瘤治疗手段。高强度聚焦超声治疗过程中的图像引导、监控及治疗效果评判是实现聚焦超声安全治疗的基本保障，也是高效、精细和个性化治疗的基础。目前常用的高强度聚焦超声治疗效果评判方法包括：
(1)基于组织T1、T2、质子密度进行损伤检测：T1-W、T2-W等都是磁共振监控高强度聚焦超声治疗的常用序列，当蛋白质受高温作用变性时，组织T1、T2和质子密度值会发生变化。然而这些参数除了受组织性质改变本身影响外，也受温度的影响，比如组织T1值随温度的升高而增长。因此基于组织T1、T2及质子密度进行损伤判断时，为了准确定性组织是否已发生坏死，还是温度影响引起的图像信号改变，需要等高强度聚焦超声引起的温度扩散到热平衡。
(2)基于超声弹性成像进行损伤检测：弹性是人体组织的重要物理特性，正常组织、异常组织、病变组织之间弹性存在显著差异。如从某一方向对组织施加一定应力，组织内会产生相应应变。相同应力作用下，组织应变越大，位移越大，组织硬度越小。高强度聚焦超声治疗后，焦域坏死表现为细胞核破裂或固缩、蛋白质变性、细胞结构破坏等，直接导致组织弹性的改变。
超声弹性成像的原理是对组织施加一个内部或外部的动态或者静态/准静态的压力，通过采集组织施压前后的射频回波信号，基于信号间的相关性，对其进行信号处理提取组织位移信息，可得到组织应变信息，从而间接反映组织弹性模量。
(3)基于磁共振弹性成像进行损伤检测：磁共振成像(Magnetic Resonance Imaging，MRI)由于其多方位立体成像、特有的温度监控、多种组织对比等特点，已成为聚焦超声治疗监控的最佳手段之一。
磁共振弹性成像的步骤主要是：1、需要一套磁共振兼容的激励源，在组织内产生频率50Hz至500Hz的剪切波；2、通过添加运动敏感梯度，将组织位移在磁共振相位图上进行编码，相位图与组织位移关系如下：
Figure PCTCN2015099843-appb-000001
其中，φ为组织运动及施加梯度场在位置
Figure PCTCN2015099843-appb-000002
处产生的相位，θ为组织运动与运动敏感梯度之间的相位差，γ为磁旋比γ/2π＝42.57MHz/T，N为使用的运动敏感梯度的对数，T、
Figure PCTCN2015099843-appb-000003
分别为运动敏感梯度的时长与幅值，ξ0为最大位移，
Figure PCTCN2015099843-appb-000004
为波数；3、基于上述公式，对数据进行处理得到组织弹性的定量分布结果。
上述三种方法具有如下缺点：
基于组织T1、T2、质子密度进行损伤检测：受温度影响，需要等到组织内温度回复到热平衡温度，才可以快速准确定性组织是否已发生坏死，还是温度影响引起的图像信号改变反馈；
基于超声弹性成像进行损伤检测：超声图像本身分辨率明显低于磁共振图像，会直接影响判断的准确性。此外，高频超声的图像分辨率相对较高，但高频超声在组织内的传播距离有限，导致超声弹性成像更适用于浅表器官诊断；
基于磁共振弹性成像进行损伤检测：需要复杂的外部激励源，且激励源产生的剪切波存在与超声弹性成像相同的问题：空间分辨率会随着频率的增加而增加，但高频剪切波衰减速度快，传播距离有限，此外磁共振弹性成像的重建需要求解一个Helmholtz(赫姆霍兹)问题，极容易受到噪声的影响。
发明内容
本发明实施例提供一种高强度聚焦超声损伤判定方法，该方法不受温度的影响，可实现快速准确定性组织是否已发生坏死；无需复杂的外部激励源，不易受噪声影响；操作方法简单，不会对组织产生附加的热量及损伤，检测方法安全。该方法包括：
获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
本发明实施例还提供一种高强度聚焦超声损伤判定装置，采用本发明装置进行高强度聚焦超声损伤的判定，不受温度的影响，可实现快速准确定性组织是否已发生坏死；无需复杂的外部激励源，不易受噪声影响；操作简单，不会对组织产生附加的热量及损伤，检测方法安全。该装置包括：
序列获得模块，用于获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
第一位移确定模块，用于在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
第二位移确定模块，用于在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
损伤判定模块，用于当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
在本发明实施例中，通过在治疗前和治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后的磁共振声辐射力位移检测序列的相位变化，确定治疗前和治疗后的病变组织内位移；当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。该方法不受温度的影响，可实现快速准确定性组织是否已发生坏死；无需复杂的外部激励源，不易受噪声影响；操作方法简单，不会对组织产生附加的热量及损伤，检测方法安全。
附图说明
为了更清楚地说明本发明实施例中的技术方案，下面将对实施例描述中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本发明的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。在附图中：
图1为本发明实施例中高强度聚焦超声损伤判定方法流程图；
图2为本发明实施例中治疗前的组织内位移检测示意图；
图3为本发明实施例中治疗后(即刻)的组织位移检测示意图；
图4为本发明实施例中治疗中的温度监控曲线；
图5为本发明实施例中采用的声辐射力位移检测序列时序图；
图6为本发明实施例中无损伤产生时高强度聚焦超声加热前后组织位移曲线；
图7为本发明实施例中无损伤产生时温度变化曲线；
图8是本发明实施例中猪肉组织内产生损伤时高强度聚焦超声加热前后组织内位移曲线；
图9是本发明实施例中焦点处最大温度变化曲线；
图10是本发明实施例中牛肝组织内产生损伤时高强度聚焦超声加热前后组织内位移曲线；
图11是本发明实施例中焦点处最大温度变化曲线；
图12是本发明实施例中高强度聚焦超声损伤判定装置结构示意图。
具体实施方式
为使本发明实施例的目的、技术方案和优点更加清楚明白，下面结合附图对本发明实施例做进一步详细说明。在此，本发明的示意性实施例及其说明用于解释本发明，但并不作为对本发明的限定。
现有的高强度聚焦超声治疗效果评判方法会受温度的影响，需要等到组织内温度恢复到热平衡温度才可以进行疗效的判断；需要外加激励源才可对组织弹性改变进行检测；极容易受到噪声的影响等等。本发明提出了一种高强度聚焦超声损伤判定方法及装置，可以克服现有技术中存在的缺点。
图1是本发明实施例中高强度聚焦超声损伤判定方法流程图，如图1所示，该方法包括如下步骤：
步骤101：获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
步骤102：在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
步骤103：在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
步骤104：当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
具体实施时，在磁共振声辐射力位移检测序列中添加运动编码梯度，将组织在超声作用下引起的位移转换为磁共振图像相位变化，基于以下公式实现组织内位移的定量：
Figure PCTCN2015099843-appb-000005
其中，Δx为病变组织内位移，Δφ为添加运动编码梯度前和后两次采集的磁共振图像的相位差，Ge为运动编码梯度的强度，τ为运动编码梯度的时长，γ为磁旋比。
图2和图3分别为治疗前和后的组织内位移检测示意图，可以看出位移有明显的变化。图4是治疗中的温度曲线，温度是持续升高的。
具体实施是，磁共振声辐射力位移检测序列可以采用分段读出的平面回波序列、一维线性扫描序列、二位自旋回波序列、单次激发平面回波序列等等。
位移编码梯度可以采用重复双极位移编码梯度、单极位移编码梯度、双极反向位移编码梯度等等。
具体实施是，在高强度聚焦超声治疗前后采集组织中的位移分布，根据需要可采集多组位移分布结果，保证检测的准确性。高强度聚焦超声治疗过程中可辅以梯度回波序列进行温度监控。
不同组织位移改变量可能存在一定的差异，所以根据前期实验选取合适的阈值，当治疗前后组织位移存在显著差异，且位移差大于该阈值时，可判定该点组织已坏死，从而实现对损伤区域的描绘。
为了验证本发明结果，所有实验在西门子3T磁共振成像系统(Siemens TIM Trio，Erlangen，German)上进行。本实验所使用的声辐射力位移检测序列为分段读出平面回波序列，序列中添加双极性运动编码梯度对组织位移进行编码，序列时序如图5所示，序列中所使用运动编码梯度强度为32mT/m，运动编码梯度时长10ms，其他成像参数为：TR＝200ms，TE＝36ms，带宽＝1149Hz/Pixel，层厚＝5mm，分辨率2.2*1.6mm2，EPI factor＝9；实验中所使用GRE序列TR/TE＝29/10ms，带宽＝390Hz/Pixel。加热前后分别采集20组组织内位移变化。
采用两种组织进行实验：猪肉组织和牛肝组织。
如图5所示，实验时共采集两组图像，第二组所用位移编码梯度(实线)与第一组极性相反(虚线)，以提高检测的灵敏度。
由图6和图7可以看出，尽管高强度聚焦超声治疗过程中组织内存在明显温度升高，但是加热前后的组织位移并无明显的变化，组织内并无热损伤产生。
由图8可以看出，当猪肉组织内产生损伤时，加热前后组织内位移存在显著差异，20组测量结果的平均最大位移之差为2.33μm，加热后组织内位移增大。由图9可以看出，焦点处最大温升为37.6℃，在对猪肉组织切开后，猪肉组织内可见明显热损伤。
由图10可以看出，当牛肝组织内产生损伤时，加热前后组织内位移存在显著差异，20组测量结果的平均最大位移之差为2.19um，加热后组织内位移减小。由图11可以看出，焦点处最大温升为40.5℃，在对牛肝组织切开后，牛肝组织内可见明显热损伤。
尽管在猪肉内加热后组织位移增大，而在牛肝内加热后组织位移减小(加热时间相同，功率不同)，但从实验结果可见当组织中产生热损伤时，加热前后的声辐射力位移检测结果存在显著差异。
基于同一发明构思，本发明实施例中还提供了一种高强度聚焦超声损伤判定装置，如下面的实施例所述。由于高强度聚焦超声损伤判定装置解决问题的原理与高强度聚焦超声损伤判定方法相似，因此高强度聚焦超声损伤判定装置的实施可以参见高强度聚焦超声损伤判定方法的实施，重复之处不再赘述。以下所使用的，术语“单元”或者“模块”可以实现预定功能的软件和/或硬件的组合。尽管以下实施例所描述的装置较佳地以软件来实现，但是硬件，或者软件和硬件的组合的实现也是可能并被构想的。
图12是本发明实施例的高强度聚焦超声损伤判定装置的一种结构框图，如图12所示，包括：
序列获得模块1201，用于获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
第一位移确定模块1202，用于在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
第二位移确定模块1203，用于在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
损伤判定模块1204，用于当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
具体实施时，所述第一位移确定模块1202和第二位移确定模块1203具体用于：
按如下公式确定病变组织内位移：
Figure PCTCN2015099843-appb-000006
其中，Δx为病变组织内位移，Δφ为添加运动编码梯度前和后两次采集的磁共振图像的相位差，Ge为运动编码梯度的强度，τ为运动编码梯度的时长，γ为磁旋比。
具体实施时，所述磁共振声辐射力位移检测序列为分段读出的平面回波序列、一维线性扫描序列、二位自旋回波序列或单次激发平面回波序列。
具体实施时，所述位移编码梯度为重复双极位移编码梯度、单极位移编码梯度或双极反向位移编码梯度。
综上，本发明具有以下优点：
1、该方法不需外加激励源，即可对组织弹性改变进行检测；
2、该方法操作简单，不需等组织内温度恢复到热平衡温度即可进行疗效判断；
3、该方法可兼容多种声辐射力位移检测序列；
4、该方法只需毫秒级高强度聚焦超声脉冲作用，不易引起组织内温升，检测方法安全。
本领域内的技术人员应明白，本发明的实施例可提供为方法、系统、或计算机程序产品。因此，本发明可采用完全硬件实施例、完全软件实施例、或结合软件和硬件方面的实施例的形式。而且，本发明可采用在一个或多个其中包含有计算机可用程序代码的计算机可用存储介质(包括但不限于磁盘存储器、CD-ROM、光学存储器等)上实施的计算机程序产品的形式。
本发明是参照根据本发明实施例的方法、设备(系统)、和计算机程序产品的流程图和/或方框图来描述的。应理解可由计算机程序指令实现流程图和/或方框图中的每一流程和/或方框、以及流程图和/或方框图中的流程和/或方框的结合。可提供这些计算机程序指令到通用计算机、专用计算机、嵌入式处理机或其他可编程数据处理设备的处理器以产生一个机器，使得通过计算机或其他可编程数据处理设备的处理器执行的指令产生用于实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能的装置。
这些计算机程序指令也可存储在能引导计算机或其他可编程数据处理设备以特定方式工作的计算机可读存储器中，使得存储在该计算机可读存储器中的指令产生包括指令装置的制造品，该指令装置实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能。
这些计算机程序指令也可装载到计算机或其他可编程数据处理设备上，使得在计算机或其他可编程设备上执行一系列操作步骤以产生计算机实现的处理，从而在计算机或其他可编程设备上执行的指令提供用于实现在流程图一个流程或多个流程和/或方框图一个方框或多个方框中指定的功能的步骤。
以上所述的具体实施例，对本发明的目的、技术方案和有益效果进行了进一步详细说明，所应理解的是，以上所述仅为本发明的具体实施例而已，并不用于限定本发明的保护范围，凡在本发明的精神和原则之内，所做的任何修改、等同替换、改进等，均应包含在本发明的保护范围之内。

Claims (8)

  1. 一种高强度聚焦超声损伤判定方法，其特征在于，包括：
    获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
    在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
    在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
    当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
  2. 如权利要求1所述的高强度聚焦超声损伤判定方法，其特征在于，按如下公式确定病变组织内位移：
    Figure PCTCN2015099843-appb-100001
    其中，Δx为病变组织内位移，Δφ为添加运动编码梯度前和后两次采集的磁共振图像的相位差，Ge为运动编码梯度的强度，τ为运动编码梯度的时长，γ为磁旋比。
  3. 如权利要求1所述的高强度聚焦超声损伤判定方法，其特征在于，所述磁共振声辐射力位移检测序列为分段读出的平面回波序列、一维线性扫描序列、二位自旋回波序列或单次激发平面回波序列。
  4. 如权利要求1所述的高强度聚焦超声损伤判定方法，其特征在于，所述位移编码梯度为重复双极位移编码梯度、单极位移编码梯度或双极反向位移编码梯度。
  5. 一种高强度聚焦超声损伤判定装置，其特征在于，包括：
    序列获得模块，用于获得采用高强度聚焦超声对病变组织治疗前和治疗后的磁共振声辐射力位移检测序列；
    第一位移确定模块，用于在治疗前的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗前的病变组织内位移；
    第二位移确定模块，用于在治疗后的磁共振声辐射力位移检测序列中添加运动编码梯度，根据添加运动编码梯度前后获得的磁共振相位图的相位变化，确定治疗后的病变组织内位移；
    损伤判定模块，用于当治疗前和治疗后的病变组织内位移的位移差大于预设阈值时，判定病变组织损伤。
  6. 如权利要求5所述的高强度聚焦超声损伤判定装置，其特征在于，所述第一位移确定模块和第二位移确定模块具体用于：
    按如下公式确定病变组织内位移：
    Figure PCTCN2015099843-appb-100002
    其中，Δx为病变组织内位移，Δφ为添加运动编码梯度前和后两次采集的磁共振图像的相位差，Ge为运动编码梯度的强度，τ为运动编码梯度的时长，γ为磁旋比。
  7. 如权利要求5所述的高强度聚焦超声损伤判定装置，其特征在于，所述磁共振声辐射力位移检测序列为分段读出的平面回波序列、一维线性扫描序列、二位自旋回波序列或单次激发平面回波序列。
  8. 如权利要求5所述的高强度聚焦超声损伤判定装置，其特征在于，所述位移编码梯度为重复双极位移编码梯度、单极位移编码梯度或双极反向位移编码梯度。
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