WO2019191863A1 - 一种超声成像系统、方法及装置 - Google Patents
一种超声成像系统、方法及装置 Download PDFInfo
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- WO2019191863A1 WO2019191863A1 PCT/CN2018/081552 CN2018081552W WO2019191863A1 WO 2019191863 A1 WO2019191863 A1 WO 2019191863A1 CN 2018081552 W CN2018081552 W CN 2018081552W WO 2019191863 A1 WO2019191863 A1 WO 2019191863A1
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- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
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- the invention belongs to the field of ultrasonic medical technology, and in particular relates to an ultrasound imaging system, method and device.
- Ultrasound cranial imaging not only enables real-time imaging of intracranial tissue, but also measures the size of the lesion through intracranial vascular analysis and three-dimensional reconstruction.
- ultrasound focusing has good tissue penetration, localization and energy storage. Ultrasound is applied to the tissue, and its biological effects such as thermal, mechanical and cavitation effects can be used to absorb the diseased tissue.
- transcranial focused ultrasound can effectively stimulate the deeper brain regions under the cortex without trauma and high spatial precision, and achieve non-invasive deep brain nerve stimulation.
- Neural network regulation through focused ultrasound can help develop central nervous system. Potential therapy for the disease.
- Ultrasonic energy can be used to alter brain activity and treat disease, but traditional cranial focusing methods use a single low-frequency one-dimensional phased array probe to penetrate the skull for imaging, treatment, and stimulation, since human skull thickness ranges from 2 mm to 8 mm. Between, the density is high, the ultrasonic waves will have different degrees of energy attenuation and sound field distortion when passing through different positions of the skull, and the shape and distortion of the ultrasonic focal field may also occur, so that the ultrasonic image with high signal to noise ratio cannot be obtained. Accurate and effective treatment and stimulation of the lesion.
- a method for ultrasonic craniotomy focusing comprises: performing a three-dimensional magnetic resonance imaging of a head on a patient, and reconstructing a three-dimensional shape of the skull based on the obtained data.
- the digital model is used to introduce the three-dimensional digital model of the skull into a 3D printer to obtain a corresponding skull solid model, and the skull solid model is time-inverted to obtain an ultrasound transcranial focused emission sequence.
- This method requires three-dimensional reconstruction with Magnetic Resonance Imaging (MRI) in obtaining the solid model of the skull.
- MRI Magnetic Resonance Imaging
- a phased array skull and sacrum imager which includes a display body, a main input device, an ultrasonic probe, an auxiliary input device, a casing, an ultrasound host, Body, power supply, PC host, optical drive, display guide post, monitor bottom cover, display arm, display stand, in actual use, the invention uses a 2MHz low-frequency one-dimensional phased array probe to observe the brain tissue structure through the skull and tibia
- the intracranial vessels and the vascular conditions of the brain stem, through the brain parenchyma and cerebrovascular and their Doppler spectral waveforms for the diagnosis of intracranial lesions, and the low frequency phased array probe in this invention does not consider the thickness of the skull versus ultrasound The influence of the signal, so it is impossible to obtain an ultrasound image with high signal-to-noise ratio to accurately and effectively treat and stimulate the lesion.
- the invention provides an ultrasound imaging system, the system comprising:
- transcranial focused ultrasound transducer comprising a high frequency ultrasound transducer and a low frequency ultrasound transducer, wherein the high frequency ultrasound transducer is used for a patient's skull thickness and ultrasound Measuring the speed of sound propagated in the skull of the patient, the low frequency ultrasound transducer for ultrasound imaging or treating the intracranial tissue to be treated of the patient;
- An ultrasonic excitation receiving device coupled to the transcranial focused ultrasound transducer for displaying ultrasound imaging of the intracranial tissue to be treated formed by the transcranial focused ultrasound transducer.
- the present invention provides an ultrasound imaging method of the above ultrasound imaging system, the method comprising the steps of:
- the present invention provides an ultrasonic imaging apparatus of the above ultrasonic imaging system, the apparatus comprising:
- a parameter measuring unit configured to control the high frequency ultrasound transducer to measure a thickness of the skull of the patient and an ultrasonic wave propagating in the skull of the patient when receiving a request for ultrasonic treatment of the intracranial tissue to be treated of the patient Sound speed
- a signal sequence acquiring unit configured to calculate a phase and intensity compensation value of the ultrasonic transmission signal of each array element of the low frequency ultrasonic transducer according to the measured skull thickness and the sound speed, and a phase and intensity compensation value of the ultrasonic receiving signal To obtain an ultrasound transmission signal sequence and an ultrasound reception signal compensation sequence;
- An ultrasound focusing unit configured to control the low frequency ultrasound transducer to perform focusing according to the obtained sequence of ultrasound emission signals to generate ultrasound waves for ultrasonic treatment of the intracranial tissue to be treated;
- the echo signal compensation unit is configured to perform compensation focusing on the echo signal reflected by the ultrasonic wave according to the obtained ultrasound received signal compensation sequence to display and output ultrasound imaging of the intracranial tissue to be treated by the ultrasonic excitation receiving device.
- the present invention controls the high frequency ultrasonic transducer to measure the thickness of the patient's skull and the speed of sound of the ultrasonic wave propagating in the patient's skull, according to the measured thickness and speed of the skull.
- FIG. 1 is a schematic structural view of an ultrasonic imaging system according to Embodiment 1 of the present invention.
- FIG. 2 is a schematic structural view of an arrangement of a high frequency ultrasonic transducer and a low frequency ultrasonic transducer in an ultrasonic imaging system according to Embodiment 1 of the present invention
- FIG. 3 is a schematic structural view of an arrangement of a high frequency ultrasonic transducer and a low frequency ultrasonic transducer in an ultrasonic imaging system according to Embodiment 1 of the present invention
- FIG. 4 is a flowchart showing an implementation of an ultrasound imaging method according to Embodiment 2 of the present invention.
- FIG. 5 is a schematic structural diagram of an ultrasonic imaging apparatus according to Embodiment 3 of the present invention.
- FIG. 6 is a schematic diagram of a preferred structure of an ultrasonic imaging apparatus according to Embodiment 3 of the present invention.
- Embodiment 1 is a diagrammatic representation of Embodiment 1:
- Fig. 1 shows the structure of an ultrasonic imaging system according to a first embodiment of the present invention. For the convenience of description, only parts related to the embodiment of the present invention are shown.
- Embodiments of the present invention provide an ultrasound imaging system 1 that includes a transcranial focused ultrasound transducer 11 and an ultrasound excitation receiving device 12, wherein:
- the transcranial focused ultrasound transducer 11 is comprised of a high frequency ultrasound transducer 111 and a low frequency ultrasound transducer 112 for use in the thickness of the patient's skull and the speed of sound of the ultrasound propagating in the patient's skull. To make measurements, the low frequency ultrasound transducer 112 is used to ultrasound imaging or treat the intracranial tissue to be treated of the patient.
- the ultrasonic excitation receiving device 12 can be coupled to the transcranial focused ultrasound transducer 11 via a connecting line for displaying ultrasound imaging of the output of the intracranial tissue to be treated by the output transcranial focused ultrasound transducer 11.
- the high frequency ultrasonic transducer 111 has a frequency range of 5-40 MHz
- the low frequency ultrasonic transducer 112 has a frequency range of 0.5-5 MHz, thereby achieving integration of skull thickness and intracranial focus.
- the user can adjust the frequency range of the high-frequency ultrasonic transducer 111 and the low-frequency ultrasonic transducer 112 through an ultrasonic excitation receiving device including a user operation console, thereby improving the cranial focusing.
- the high frequency ultrasonic transducer 111 is a one-dimensional linear array ultrasonic transducer or a two-dimensional array ultrasonic transducer
- the low-frequency ultrasonic transducer 112 is a one-dimensional array ultrasonic transducer or a two-dimensional array ultrasonic transducer.
- the energy meter improves the accuracy of high frequency thickness measurement and the accuracy of low frequency focusing.
- the high frequency ultrasonic transducer 111 is disposed around the low frequency ultrasonic transducer 112.
- the cranial focused ultrasound transducer 11 includes a high frequency ultrasonic transducer 1 and low frequency ultrasound.
- the transducer 2, the high frequency ultrasonic transducer 1 is mounted close to the periphery of the low frequency ultrasonic transducer 2, thereby reducing the size of the cranial focused ultrasound transducer 11.
- the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 are arranged up and down.
- the cranial focused ultrasound transducer 11 includes a high frequency ultrasonic transducer 1
- the low frequency ultrasonic transducer 2, the high frequency ultrasonic transducer 1 and the low frequency ultrasonic transducer 2 are arranged up and down, thereby reducing the cost of the cranial focused ultrasound transducer 11.
- the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 are arranged in a circular arrangement or in other patterns, thereby increasing the range of application of the cranial focused ultrasound transducer 11.
- the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 in the transcranial focused ultrasound transducer can be determined according to the arrangement structure of the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112. Type, which further improves the accuracy of high frequency thickness measurement and the accuracy of low frequency focusing.
- the high frequency ultrasonic transducer 111 is disposed around the low frequency ultrasonic transducer 112
- the high frequency ultrasonic transducer 111 employs a one-dimensional linear array ultrasonic transducer
- the low frequency ultrasonic transducer 112 employs two-dimensional array ultrasonic imaging.
- the transducer and when the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 are arranged up and down, the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 each employ a one-dimensional linear array ultrasonic transducer .
- the user can adjust the number of phased arrays of the high frequency ultrasonic transducer 111 and the low frequency ultrasonic transducer 112 through an ultrasonic excitation receiving device including a user operation console, thereby further The range of application of the transcranial focused ultrasound transducer 11 is improved.
- Embodiments of the present invention provide an ultrasound imaging system including a transcranial focused ultrasound transducer composed of a high frequency ultrasonic transducer and a low frequency ultrasonic transducer and an ultrasonic excitation coupled to a transcranial focused ultrasound transducer
- the receiving device when receiving a request for ultrasonic treatment of the patient's intracranial tissue to be treated, first measures the thickness of the patient's skull and the speed of sound of the ultrasonic wave propagating in the patient's skull through a high frequency ultrasonic transducer, and then measures the obtained skull The thickness and sound velocity are fed back to the low frequency ultrasonic transducer, and the ultrasonic signal and the ultrasonic receiving signal of the low frequency ultrasonic transducer are subjected to focusing parameter compensation, and finally the low frequency ultrasonic transducer performs the intracranial tissue to be treated according to the compensated ultrasonic emission signal sequence. Focusing and compensating the intracranial imaging for sound field based on the compensated ultrasound received signal sequence, thereby improving the
- Embodiment 2 is a diagrammatic representation of Embodiment 1:
- Embodiment 4 is a flowchart showing an implementation of an ultrasound imaging method according to Embodiment 2 of the present invention.
- the ultrasound imaging apparatus is applicable to the ultrasound imaging system in Embodiment 1. For convenience of description, only parts related to the embodiment of the present invention are shown. , as detailed below:
- step S401 upon receiving a request for ultrasound treatment of the patient's intracranial tissue to be treated, the high frequency ultrasound transducer is controlled to measure the patient's skull thickness and the speed of sound of the ultrasound propagating in the patient's skull.
- Embodiments of the present invention are applicable to the ultrasound imaging system of Embodiment 1 for performing ultrasound focusing and intracranial imaging on a patient's intracranial tissue to be treated, the system comprising a transcranial focused ultrasound transducer and transcranial focused ultrasound transduction
- the ultrasonic excitation receiving device is connected, and the transcranial focused ultrasound transducer is composed of a high frequency ultrasonic transducer and a low frequency ultrasonic transducer, wherein the high frequency ultrasonic transducer is used for the patient's skull thickness and ultrasound in the patient's skull
- the transmitted sound velocity is measured, the low frequency ultrasonic transducer is used for ultrasonic imaging or treatment of the patient's intracranial tissue to be treated, and the ultrasonic excitation receiving device is used to display the output of the transcranial focused ultrasound transducer for the ultrasound formed by the intracranial tissue to be treated. Imaging.
- the ultrasonic signal is preset according to each array element of the high frequency ultrasonic transducer. Delay time, moving the focus point of the high-frequency ultrasonic transducer between the upper and lower surfaces of the patient's skull, adjusting the ultrasonic signal emission delay time of the intermediate array element and the end array element of the high-frequency ultrasonic transducer to adjust the focus point according to the The step length is moved to the lower surface of the patient's skull.
- the delay time difference between the middle array element and the end array element of the high-frequency ultrasonic transducer is obtained, and the high-frequency ultrasonic transducer is obtained.
- the time required to receive the reflected waves on the lower surface of the patient's skull, and the thickness of the skull and the speed of sound of the ultrasound propagating in the patient's skull are calculated according to the delay time difference, the propagation time, and a preset formula, thereby facilitating subsequent low-frequency ultrasound transducers.
- the ultrasound signal provides focus parameter compensation.
- the reflected wave of the lower surface of the patient's skull reaches a maximum
- the delay time difference between the intermediate element of the high-frequency ultrasonic transducer and the end element is obtained
- the reflected wave of the lower surface of the patient's skull is determined according to the amplitude of the echo of the focused point. Whether the maximum is reached, the step of obtaining the delay time difference between the intermediate array element and the end array element of the high-frequency ultrasonic transducer is performed to obtain the delay time difference between the intermediate array element and the end array element of the high-frequency ultrasonic transducer.
- d is the thickness of the skull
- c is the speed of sound
- a is the horizontal distance between the focus point and the most marginal element of the high-frequency transducer
- ⁇ T is the propagation time required to obtain the reflected wave on the lower surface of the skull when the focus is on the lower surface of the skull
- ⁇ t 1 When the reflected wave on the lower surface of the skull is maximum, the delay time difference between the intermediate array element and the end array element improves the calculation accuracy of the thickness of the skull and the speed of sound of the ultrasonic wave propagating in the patient's skull.
- step S402 the phase and intensity compensation values of the ultrasonic transmission signals of the respective elements of the low-frequency ultrasonic transducer and the phase and intensity compensation values of the ultrasonic reception signals are calculated according to the measured skull thickness and the sound velocity to obtain an ultrasonic transmission signal sequence and The ultrasound receives the signal compensation sequence.
- the measured skull thickness and sound velocity are fed back to the low frequency ultrasonic transducer, and the low frequency ultrasonic transducer is calculated according to the thickness and sound velocity of the skull.
- the phase and intensity compensation values of the meta-ultrasonic emission signal, and the phase and intensity compensation values of the ultrasound received signal are obtained from the low frequency ultrasonic transducer, to obtain an ultrasound transmission signal sequence and an ultrasound reception signal compensation sequence.
- step S403 the low frequency ultrasonic transducer is controlled to perform focusing according to the obtained sequence of ultrasonic emission signals to generate ultrasonic waves for ultrasonic treatment of the intracranial tissue to be treated.
- the low frequency ultrasound transducer performs beam synthesis and aggregation based on the obtained sequence of ultrasound emission signals to generate ultrasound waves that are ultrasonically treated for intracranial tissue to be treated.
- step S404 the echo signal reflected by the ultrasonic wave is compensated and focused according to the obtained ultrasonic receiving signal compensation sequence to display the ultrasonic imaging of the tissue to be treated in the output intracranial by the ultrasonic excitation receiving device.
- the echo signal reflected by the ultrasonic wave carries information about the tissue to be treated in the skull, and since the thickness of the skull causes attenuation and distortion of the ultrasonic signal, the ultrasonic reflection signal is compensated according to the obtained ultrasonic receiving signal.
- the wave signal is compensated for focusing to obtain an intracranial image with a high signal to noise ratio, and the intracranial image is displayed and outputted by the ultrasonic excitation receiving device.
- the high frequency ultrasonic transducer when receiving a request for ultrasonic treatment of the intracranial tissue to be treated of the patient, is controlled to measure the thickness of the patient's skull and the speed of sound of the ultrasonic wave propagating in the patient's skull, according to the measurement.
- the thickness and sound velocity of the skull are used to calculate the phase and intensity compensation values of the ultrasonic emission signals of the respective array elements of the low-frequency ultrasonic transducer, and the phase and intensity compensation values of the ultrasonic receiving signals to obtain the ultrasonic transmission signal sequence and the ultrasonic reception signal compensation sequence, according to the obtained
- the ultrasonic transmitting signal sequence controls the low frequency ultrasonic transducer to generate ultrasonic waves for ultrasonic treatment of the intracranial tissue to be treated, and compensates the echo signals reflected by the ultrasonic waves according to the obtained ultrasonic receiving signal compensation sequence to receive by ultrasonic excitation
- the device displays ultrasound imaging of the tissue to be treated in the cranial tissue, thereby improving the accuracy of ultrasound cranial focusing and the clarity of ultrasound imaging.
- Embodiment 3 is a diagrammatic representation of Embodiment 3
- FIG. 5 is a diagram showing the structure of an ultrasonic imaging apparatus according to Embodiment 3 of the present invention.
- the ultrasonic imaging apparatus is applicable to the ultrasonic imaging system in Embodiment 1.
- parts related to the embodiment of the present invention are shown. These include:
- the parameter measuring unit 51 is configured to control the high frequency ultrasonic transducer to measure the thickness of the patient's skull and the speed of sound of the ultrasonic wave propagating in the patient's skull when receiving a request for ultrasonic treatment of the intracranial tissue to be treated of the patient.
- Embodiments of the present invention are applicable to the ultrasound imaging system of Embodiment 1 for performing ultrasound focusing and intracranial imaging on a patient's intracranial tissue to be treated, the system comprising a transcranial focused ultrasound transducer and transcranial focused ultrasound transduction
- the ultrasonic excitation receiving device is connected, and the transcranial focused ultrasound transducer is composed of a high frequency ultrasonic transducer and a low frequency ultrasonic transducer, wherein the high frequency ultrasonic transducer is used for the patient's skull thickness and ultrasound in the patient's skull
- the transmitted sound velocity is measured, the low frequency ultrasonic transducer is used for ultrasonic imaging or treatment of the patient's intracranial tissue to be treated, and the ultrasonic excitation receiving device is used to display the output of the transcranial focused ultrasound transducer for the ultrasound formed by the intracranial tissue to be treated. Imaging.
- the ultrasonic signal is preset according to each array element of the high frequency ultrasonic transducer. Delay time, moving the focus point of the high-frequency ultrasonic transducer between the upper and lower surfaces of the patient's skull, adjusting the ultrasonic signal emission delay time of the intermediate array element and the end array element of the high-frequency ultrasonic transducer to adjust the focus point according to the The step length is moved to the lower surface of the patient's skull.
- the delay time difference between the middle array element and the end array element of the high-frequency ultrasonic transducer is obtained, and the high-frequency ultrasonic transducer is obtained.
- the time required to receive the reflected waves on the lower surface of the patient's skull, and the thickness of the skull and the speed of sound of the ultrasound propagating in the patient's skull are calculated according to the delay time difference, the propagation time, and a preset formula, thereby facilitating subsequent low-frequency ultrasound transducers.
- the ultrasound signal provides focus parameter compensation.
- d is the thickness of the skull
- c is the speed of sound
- a is the horizontal distance between the focus point and the most marginal element of the high-frequency transducer
- ⁇ T is the propagation time required to obtain the reflected wave on the lower surface of the skull when the focus is on the lower surface of the skull
- ⁇ t 1 When the reflected wave on the lower surface of the skull is maximum, the delay time difference between the intermediate array element and the end array element improves the calculation accuracy of the thickness of the skull and the speed of sound of the ultrasonic wave propagating in the patient's skull.
- the signal sequence obtaining unit 52 is configured to calculate a phase and intensity compensation value of the ultrasonic transmission signal of each array element of the low frequency ultrasonic transducer according to the measured skull thickness and the sound speed, and a phase and intensity compensation value of the ultrasonic receiving signal to obtain the ultrasonic emission.
- the signal sequence and the ultrasound receive signal compensation sequence are configured to calculate a phase and intensity compensation value of the ultrasonic transmission signal of each array element of the low frequency ultrasonic transducer according to the measured skull thickness and the sound speed, and a phase and intensity compensation value of the ultrasonic receiving signal to obtain the ultrasonic emission.
- the measured skull thickness and sound velocity are fed back to the low frequency ultrasonic transducer, and the low frequency ultrasonic transducer is calculated according to the thickness and sound velocity of the skull.
- the phase and intensity compensation values of the meta-ultrasonic emission signal, and the phase and intensity compensation values of the ultrasound received signal are obtained from the low frequency ultrasonic transducer, to obtain an ultrasound transmission signal sequence and an ultrasound reception signal compensation sequence.
- the ultrasonic focusing unit 53 is configured to control the low frequency ultrasonic transducer to perform focusing according to the obtained ultrasonic emission signal sequence to generate ultrasonic waves for ultrasonic treatment of the intracranial tissue to be treated.
- the low frequency ultrasound transducer performs beam synthesis and aggregation based on the obtained sequence of ultrasound emission signals to generate ultrasound waves that are ultrasonically treated for intracranial tissue to be treated.
- the echo signal compensation unit 54 is configured to perform compensation focusing on the echo signal reflected by the ultrasonic wave according to the obtained ultrasonic receiving signal compensation sequence to display the ultrasonic imaging of the tissue to be treated in the intracranial region by the ultrasonic excitation receiving device.
- the echo signal reflected by the ultrasonic wave carries information about the tissue to be treated in the skull, and since the thickness of the skull causes attenuation and distortion of the ultrasonic signal, the ultrasonic reflection signal is compensated according to the obtained ultrasonic receiving signal.
- the wave signal is compensated for focusing to obtain an intracranial image with a high signal to noise ratio, and the intracranial image is displayed and outputted by the ultrasonic excitation receiving device.
- the parameter measuring unit 51 includes:
- a focus point moving unit 511 configured to move a focus point of the high frequency ultrasonic transducer between the upper and lower surfaces of the patient's skull according to an ultrasonic signal transmission delay time preset by each array element of the high frequency ultrasonic transducer;
- the delay time adjustment unit 512 is configured to adjust an ultrasonic signal emission delay time of the intermediate array element and the end array element of the high frequency ultrasonic transducer to move the focus point to the lower surface of the patient's skull according to a preset step size;
- the time obtaining unit 513 is configured to obtain a delay time difference between the middle array element of the high frequency ultrasonic transducer and the end array element when the reflected wave of the lower surface of the patient's skull reaches a maximum, and obtain a high frequency ultrasonic transducer to receive the patient under the skull The propagation time required for the surface to reflect the wave;
- the thickness sound velocity calculation unit 514 is configured to calculate the thickness of the skull and the speed of sound of the ultrasonic wave propagating in the skull of the patient according to the delay time difference value, the propagation time, and a preset formula.
- the parameter measuring unit 51 further includes an echo amplitude determining unit configured to determine whether the reflected wave of the lower surface of the patient's skull reaches a maximum according to the echo amplitude of the focus point, and the trigger time acquiring unit 513 performs the acquisition of the high frequency ultrasonic transducer.
- each unit of the ultrasound imaging apparatus may be implemented by a corresponding hardware or software unit, and each unit may be an independent software and hardware unit, or may be integrated into a soft and hardware unit, and the present invention is not limited thereto. .
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Abstract
一种超声成像系统（1）、方法及装置，系统包括：由高频超声换能器（111）和低频超声换能器（112）组成的穿颅聚焦超声换能器（11）和与穿颅聚焦超声换能器（11）连接的超声激励接收设备（12），当接收到对患者的颅内待治疗组织进行超声治疗的请求时，首先控制高频超声换能器（111）测量患者的颅骨厚度和超声波在患者颅骨中传播的声速，然后将测量得到的颅骨厚度和声速反馈给低频超声换能器（112），对低频超声换能器（112）的超声发射信号和超声接收信号进行聚焦参数补偿，最后低频超声换能器（112）根据补偿的超声发射信号序列对颅内待治疗组织进行聚焦，并根据补偿的超声接收信号序列对颅内成像进行声场补偿，从而提高了超声穿颅聚焦的精确度和超声成像的清晰度。
Description
本发明属于超声医疗技术领域，尤其涉及一种超声成像系统、方法及装置。
随着社会人口老龄化和人们不规律的作息生活，造成脑部疾病(例如，阿尔茨海默病和帕金森病等)发病率越来越高，且发病不易被诊断发现，传统检测脑内疾病的手段主要是磁共振成像与CT成像，然而，磁共振成像技术图片分辨率较低，很多病变组织检测不出来，而CT成像中的放射线对人体本身有一定影响，增强CT扫描时患者对造影剂还可能过敏，因此，检测和表征颅内疾病成为生物医学成像研究中最活跃的领域之一。
相比于磁共振成像与CT成像，医学超声成像技术以其无创、无辐射、实时性好、对软组织鉴别力较高、仪器使用方便、价格低廉等特点，成为现代医学成像中不可替代的诊断技术，目前已成为临床多种疾病诊断的首选方法。超声穿颅成像不仅可以对颅内组织进行实时成像，而且还可以通过颅内血管分析和三维重建对病变大小进行测量。除了超声成像，利用超声聚焦具有良好的组织穿透性、定位性和能量存积性，将超声波作用于组织内，利用其热效应、机械效应、空化效应等生物学效应，可以使病变组织吸收能量而快速升温，并产生生化反应，最终使病变组织变性、促进组织重建和微循环改善从而达到治疗目的。此外，穿颅聚焦超声还能无创伤、高空间精度地有效刺激皮层下较深部位脑区，实现非侵入式的深脑神经刺激，通过聚焦超声波进行神经网络调控有助于开发出对中枢神经疾病的潜在疗法。
超声波能量可用于改变大脑活动和治疗疾病，但传统穿颅聚焦方法多采用单一低频一维相控阵探头穿透颅骨来进行成像、治疗以及刺激，而由于人类颅 骨厚度在2毫米到8毫米之间，密度较高，超声波在经过颅骨不同位置时会有不同程度的能量衰减和声场畸变，超声焦域也会出现形状扭曲和位置偏移的现象，以至无法获取信噪比高的超声图像来对病灶进行精确有效的治疗和刺激。
在专利申请号为201410855314.X的发明专利申请文件中，公开了一种超声穿颅聚焦的方法，该方法包含：对患者进行头部三维磁共振成像，根据获得的数据重建出其颅骨的三维数字模型，将该颅骨三维数字模型导入3D打印机，获得对应的颅骨实体模型，对该颅骨实体模型进行时间反演，获得的超声穿颅聚焦发射序列。该方法在获得颅骨实体模型时需要用磁共振成像(Magnetic Resonance Imaging，简称MRI)进行三维重建，而MRI操作复杂，使用成本高，所以该方法存在较大的局限性。
在专利申请号为201510659855.X的发明专利申请文件中，公开了一种相控阵头颅颞骨成像仪，该成像仪包括显示器主体、主输入设备、超声探头、辅助输入设备、外壳、超声主机、机体、电源、PC主机、光驱、显示器导向柱、显示器底盖、显示器臂、显示器支架，实际使用时，此发明采用2MHz的低频一维相控阵探头，穿过颅脑颞骨来观察脑组织结构、颅内血管以及脑干部的血管情况，通过脑实质和脑血管以及它们的多谱勒频谱波型来进行颅内病变的诊断，而此发明中的低频相控阵探头没有考虑颅骨厚度对超声信号的影响，因此无法获取信噪比高的超声图像来对病灶进行精确有效的治疗和刺激。
发明内容
本发明的目的在于提供一种超声成像系统、方法及装置，旨在解决由于现有技术无法提供一种有效的超声成像方法，导致超声穿颅聚焦不精确、超声成像不清晰的问题。
一方面，本发明提供了一种超声成像系统，所述系统包括：
穿颅聚焦超声换能器，所述穿颅聚焦超声换能器由高频超声换能器和低频超声换能器组成，其中，所述高频超声换能器用于对患者的颅骨厚度和超声波 在所述患者颅骨中传播的声速进行测量，所述低频超声换能器用于对所述患者的颅内待治疗组织进行超声成像或治疗；以及
与所述穿颅聚焦超声换能器连接的超声激励接收设备，用于显示输出所述穿颅聚焦超声换能器对所述颅内待治疗组织形成的超声成像。
另一方面，本发明提供了一种上述超声成像系统的超声成像方法，所述方法包括下述步骤：
当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制所述高频超声换能器测量所述患者的颅骨厚度和超声波在所述患者颅骨中传播的声速；
根据所述测量得到的颅骨厚度和所述声速计算所述低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列；
根据所述得到的超声发射信号序列，控制所述低频超声换能器进行聚焦，以产生对所述颅内待治疗组织进行超声治疗的超声波；
根据所述得到的超声接收信号补偿序列对所述超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出所述颅内待治疗组织的超声成像。
另一方面，本发明提供了一种上述超声成像系统的超声成像装置，所述装置包括：
参数测量单元，用于当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制所述高频超声换能器测量所述患者的颅骨厚度和超声波在所述患者颅骨中传播的声速；
信号序列获取单元，用于根据所述测量得到的颅骨厚度和所述声速计算所述低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列；
超声聚焦单元，用于根据所述得到的超声发射信号序列，控制所述低频超声换能器进行聚焦，以产生对所述颅内待治疗组织进行超声治疗的超声波；以及
回波信号补偿单元，用于根据所述得到的超声接收信号补偿序列对所述超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出所述颅内待治疗组织的超声成像。
本发明当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速，根据测量得到的颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列，根据得到的超声发射信号序列，控制低频超声换能器产生对颅内待治疗组织进行超声治疗的超声波，并根据得到的超声接收信号补偿序列对超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出颅内待治疗组织的超声成像，从而提高了超声穿颅聚焦的精确度和超声成像的清晰度。
图1是本发明实施例一提供的超声成像系统的结构示意图；
图2是本发明实施例一提供的超声成像系统中高频超声换能器和低频超声换能器排列的结构示意图；
图3是本发明实施例一提供的超声成像系统中高频超声换能器和低频超声换能器排列的结构示意图；
图4是本发明实施例二提供的超声成像方法的实现流程图；
图5是本发明实施例三提供的超声成像装置的结构示意图；以及
图6是本发明实施例三提供的超声成像装置的优选结构示意图。
为了使本发明的目的、技术方案及优点更加清楚明白，以下结合附图及实施例，对本发明进行进一步详细说明。应当理解，此处所描述的具体实施例仅 仅用以解释本发明，并不用于限定本发明。
以下结合具体实施例对本发明的具体实现进行详细描述：
实施例一：
图1示出了本发明实施例一提供的超声成像系统的结构，为了便于说明，仅示出了与本发明实施例相关的部分。
本发明实施例提供了一种超声成像系统1，该超声成像系统1包括穿颅聚焦超声换能器11和超声激励接收设备12，其中：
穿颅聚焦超声换能器11由高频超声换能器111和低频超声换能器112组成，其中，高频超声换能器111用于对患者的颅骨厚度和超声波在患者颅骨中传播的声速进行测量，低频超声换能器112用于对患者的颅内待治疗组织进行超声成像或治疗。超声激励接收设备12可通过连接线与穿颅聚焦超声换能器11相连接，用于显示输出穿颅聚焦超声换能器11对颅内待治疗组织形成的超声成像。
优选地，高频超声换能器111的频率范围为5-40MHz，低频超声换能器112的频率范围为0.5-5MHz，从而实现了颅骨测厚和颅内聚焦的一体化。
在本发明实施例中，根据颅骨厚度，用户可通过包括用户操作控制台的超声激励接收设备对高频超声换能器111和低频超声换能器112的频率范围进行调整，从而提高穿颅聚焦超声换能器11的适用范围。
优选地，高频超声换能器111为一维线阵超声换能器或二维面阵超声换能器，低频超声换能器112为一维阵列超声换能器或二维面阵超声换能器，从而提高了高频测厚的准确度以及低频聚焦的精确度。
优选地，将高频超声换能器111设置在低频超声换能器112四周，作为示例地，如图2所示，穿颅聚焦超声换能器11包括高频超声换能器1和低频超声换能器2，高频超声换能器1紧贴低频超声换能器2的四周安装，从而降低了穿颅聚焦超声换能器11的尺寸。
又一优选地，高频超声换能器111和低频超声换能器112成上下排列设置， 作为示例地，如图3所示，穿颅聚焦超声换能器11包括高频超声换能器1和低频超声换能器2，高频超声换能器1和低频超声换能器2成上下排列设置，从而降低了穿颅聚焦超声换能器11的成本。
又一优选地，高频超声换能器111和低频超声换能器112成环形排列设置或者其它样式排列设置，从而提高了穿颅聚焦超声换能器11的适用范围。
在本发明实施例中，可根据高频超声换能器111和低频超声换能器112的排列结构，确定穿颅聚焦超声换能器中高频超声换能器111和低频超声换能器112的类型，从而进一步提高高频测厚的准确度以及低频聚焦的精确度。例如，当高频超声换能器111设置在低频超声换能器112四周时，高频超声换能器111采用一维线阵超声换能器，低频超声换能器112采用二维面阵超声换能器，而当高频超声换能器111和低频超声换能器112成上下排列设置时，高频超声换能器111和低频超声换能器112都采用一维线阵超声换能器。
在本发明实施例中，根据颅骨厚度，用户可通过包括用户操作控制台的超声激励接收设备对高频超声换能器111和低频超声换能器112的相控阵阵列数量进行调整，从而进一步提高穿颅聚焦超声换能器11的适用范围。
本发明实施例提供了一种超声成像系统，该系统包括由高频超声换能器和低频超声换能器组成的穿颅聚焦超声换能器和与穿颅聚焦超声换能器连接的超声激励接收设备，当接收到对患者的颅内待治疗组织进行超声治疗的请求时，首先通过高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速，然后将测量得到的颅骨厚度和声速反馈给低频超声换能器，对低频超声换能器的超声发射信号和超声接收信号进行聚焦参数补偿，最后低频超声换能器根据补偿的超声发射信号序列对颅内待治疗组织进行聚焦，并根据补偿的超声接收信号序列对颅内成像进行声场补偿，从而提高了超声穿颅聚焦的精确度和超声成像的清晰度。
实施例二：
图4示出了本发明实施例二提供的超声成像方法的实现流程，该超声成像 装置适用于实施例一中的超声成像系统，为了便于说明，仅示出了与本发明实施例相关的部分，详述如下：
在步骤S401中，当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速。
本发明实施例适用于实施例一中的超声成像系统，以对患者的颅内待诊疗组织进行超声聚焦和颅内成像，该系统包括穿颅聚焦超声换能器和与穿颅聚焦超声换能器连接的超声激励接收设备，穿颅聚焦超声换能器由高频超声换能器和低频超声换能器组成，其中，高频超声换能器用于对患者的颅骨厚度和超声波在患者颅骨中传播的声速进行测量，低频超声换能器用于对患者的颅内待治疗组织进行超声成像或治疗，超声激励接收设备用于显示输出穿颅聚焦超声换能器对颅内待治疗组织形成的超声成像。
在本发明实施例中，在控制高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速时，优选地，根据高频超声换能器各个阵元预先设置的超声信号发射延迟时间，将高频超声换能器的聚焦点移动到患者颅骨的上下表面之间，调整高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，以将聚焦点根据预设的步长向患者颅骨的下表面移动，当患者颅骨下表面反射波达到最大时，获取高频超声换能器中间阵元与末端阵元的延迟时间差值，并获取高频超声换能器接收患者颅骨下表面反射波所需要的传播时间，根据延迟时间差值、传播时间以及预先设置的公式计算颅骨厚度和超声波在患者颅骨中传播的声速，从而为后续对低频超声换能器的超声信号提供聚焦参数补偿。
进一步优选地，当患者颅骨下表面反射波达到最大时，获取高频超声换能器中间阵元与末端阵元的延迟时间差值之前，根据聚焦点的回波幅度判断患者颅骨下表面反射波是否达到最大，是则才执行获取高频超声换能器中间阵元与末端阵元的延迟时间差值的步骤，以获取高频超声换能器中间阵元与末端阵元的延迟时间差值，否则跳转到调整高频超声换能器中间阵元与末端阵元的超声 信号发射延迟时间的步骤，以调整高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，直至患者颅骨下表面反射波达到最大，从而提高获取的高频超声换能器中间阵元与末端阵元延迟时间差值的准确性。
进一步优选地，通过公式
计算颅骨厚度和超声波在患者颅骨中传播的声速，其中，
d为颅骨厚度，c为声速，a为聚焦点与高频换能器最边缘阵元的水平距离，ΔT为当聚焦点在颅骨下表面时获取颅骨下表面反射波所需要的传播时间，Δt
1颅骨下表面反射波最大时，中间阵元与末端阵元之间的延迟时间差值，从而提高了对颅骨厚度和超声波在患者颅骨中传播的声速的计算准确度。
在步骤S402中，根据测量得到的颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列。
在本发明实施例中，为了避免颅骨对超声信号造成衰减和畸变，因此，将测量得到的颅骨厚度和声速反馈给低频超声换能器，根据该颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列。
在步骤S403中，根据得到的超声发射信号序列，控制低频超声换能器进行聚焦，以产生对颅内待治疗组织进行超声治疗的超声波。
在本发明实施例中，低频超声换能器根据得到的超声发射信号序列进行波束合成并聚集，以产生对颅内待治疗组织进行超声治疗的超声波。
在步骤S404中，根据得到的超声接收信号补偿序列对超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出颅内待治疗组织的超声成像。
在本发明实施例中，超声波反射的回波信号承载了颅内待治疗组织的信息，由于颅骨的厚度会对超声信号造成衰减和畸变，因此根据得到的超声接收信号 补偿序列对超声波反射的回波信号进行补偿聚焦，以获得信噪比较高的颅内图像，并将该颅内图像在超声激励接收设备显示输出。
在本发明实施例中，当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速，根据测量得到的颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列，根据得到的超声发射信号序列，控制低频超声换能器产生对颅内待治疗组织进行超声治疗的超声波，并根据得到的超声接收信号补偿序列对超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出颅内待治疗组织的超声成像，从而提高了超声穿颅聚焦的精确度和超声成像的清晰度。
实施例三：
图5示出了本发明实施例三提供的超声成像装置的结构，该超声成像装置适用于实施例一中的超声成像系统，为了便于说明，仅示出了与本发明实施例相关的部分，其中包括：
参数测量单元51，用于当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制高频超声换能器测量患者的颅骨厚度和超声波在患者颅骨中传播的声速。
本发明实施例适用于实施例一中的超声成像系统，以对患者的颅内待诊疗组织进行超声聚焦和颅内成像，该系统包括穿颅聚焦超声换能器和与穿颅聚焦超声换能器连接的超声激励接收设备，穿颅聚焦超声换能器由高频超声换能器和低频超声换能器组成，其中，高频超声换能器用于对患者的颅骨厚度和超声波在患者颅骨中传播的声速进行测量，低频超声换能器用于对患者的颅内待治疗组织进行超声成像或治疗，超声激励接收设备用于显示输出穿颅聚焦超声换能器对颅内待治疗组织形成的超声成像。
在本发明实施例中，在控制高频超声换能器测量患者的颅骨厚度和超声波 在患者颅骨中传播的声速时，优选地，根据高频超声换能器各个阵元预先设置的超声信号发射延迟时间，将高频超声换能器的聚焦点移动到患者颅骨的上下表面之间，调整高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，以将聚焦点根据预设的步长向患者颅骨的下表面移动，当患者颅骨下表面反射波达到最大时，获取高频超声换能器中间阵元与末端阵元的延迟时间差值，并获取高频超声换能器接收患者颅骨下表面反射波所需要的传播时间，根据延迟时间差值、传播时间以及预先设置的公式计算颅骨厚度和超声波在患者颅骨中传播的声速，从而为后续对低频超声换能器的超声信号提供聚焦参数补偿。
进一步优选地，通过公式
计算颅骨厚度和超声波在患者颅骨中传播的声速，其中，
d为颅骨厚度，c为声速，a为聚焦点与高频换能器最边缘阵元的水平距离，ΔT为当聚焦点在颅骨下表面时获取颅骨下表面反射波所需要的传播时间，Δt
1颅骨下表面反射波最大时，中间阵元与末端阵元之间的延迟时间差值，从而提高了对颅骨厚度和超声波在患者颅骨中传播的声速的计算准确度。
信号序列获取单元52，用于根据测量得到的颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列。
在本发明实施例中，为了避免颅骨对超声信号造成衰减和畸变，因此，将测量得到的颅骨厚度和声速反馈给低频超声换能器，根据该颅骨厚度和声速计算低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列。
超声聚焦单元53，用于根据得到的超声发射信号序列，控制低频超声换能器进行聚焦，以产生对颅内待治疗组织进行超声治疗的超声波。
在本发明实施例中，低频超声换能器根据得到的超声发射信号序列进行波束合成并聚集，以产生对颅内待治疗组织进行超声治疗的超声波。
回波信号补偿单元54，用于根据得到的超声接收信号补偿序列对超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出颅内待治疗组织的超声成像。
在本发明实施例中，超声波反射的回波信号承载了颅内待治疗组织的信息，由于颅骨的厚度会对超声信号造成衰减和畸变，因此根据得到的超声接收信号补偿序列对超声波反射的回波信号进行补偿聚焦，以获得信噪比较高的颅内图像，并将该颅内图像在超声激励接收设备显示输出。
其中，如图6所示，优选地，参数测量单元51包括：
聚焦点移动单元511，用于根据高频超声换能器各个阵元预先设置的超声信号发射延迟时间，将高频超声换能器的聚焦点移动到患者颅骨的上下表面之间；
延迟时间调整单元512，用于调整高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，以将聚焦点根据预设的步长向患者颅骨的下表面移动；
时间获取单元513，用于当患者颅骨下表面反射波达到最大时，获取高频超声换能器中间阵元与末端阵元的延迟时间差值，并获取高频超声换能器接收患者颅骨下表面反射波所需要的传播时间；以及
厚度声速计算单元514，用于根据延迟时间差值、传播时间以及预先设置的公式计算颅骨厚度和超声波在患者颅骨中传播的声速。
进一步优选地，参数测量单元51还包括回波幅度判断单元，用于根据聚焦点的回波幅度判断患者颅骨下表面反射波是否达到最大，是则触发时间获取单元513执行获取高频超声换能器中间阵元与末端阵元的延迟时间差值，否则触发延迟时间调整单元512执行调整高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，直至患者颅骨下表面反射波达到最大，从而提高获取的高频超声换能器中间阵元与末端阵元延迟时间差值的准确性。
在本发明实施例中，超声成像装置的各单元可由相应的硬件或软件单元实现，各单元可以为独立的软、硬件单元，也可以集成为一个软、硬件单元，在 此不用以限制本发明。
以上所述仅为本发明的较佳实施例而已，并不用以限制本发明，凡在本发明的精神和原则之内所作的任何修改、等同替换和改进等，均应包含在本发明的保护范围之内。
Claims (10)
- 一种超声成像系统，其特征在于，所述系统包括：穿颅聚焦超声换能器，所述穿颅聚焦超声换能器由高频超声换能器和低频超声换能器组成，其中，所述高频超声换能器用于对患者的颅骨厚度和超声波在所述患者颅骨中传播的声速进行测量，所述低频超声换能器用于对所述患者的颅内待治疗组织进行超声成像或治疗；以及与所述穿颅聚焦超声换能器连接的超声激励接收设备，用于显示输出所述穿颅聚焦超声换能器对所述颅内待治疗组织形成的超声成像。
- 如权利要求1所述超声成像系统，其特征在于，所述高频超声换能器为一维阵列超声换能器或二维面阵超声换能器，所述低频超声换能器为一维阵列超声换能器或二维面阵超声换能器。
- 如权利要求1所述超声成像系统，其特征在于，所述高频超声换能器的频率范围为5-40MHz，所述低频超声换能器的频率范围为0.5-5MHz。
- 如权利要求1所述超声成像系统，其特征在于，所述高频超声换能器和所述低频超声换能器成上下排列设置，或者所述高频超声换能器设置在所述低频超声换能器四周。
- 一种基于权利要求1-4任一所述超声成像系统的超声成像方法，其特征在于，所述方法包括下述步骤：当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制所述高频超声换能器测量所述患者的颅骨厚度和超声波在所述患者颅骨中传播的声速；根据所述测量得到的颅骨厚度和所述声速计算所述低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列；根据所述得到的超声发射信号序列，控制所述低频超声换能器进行聚焦，以产生对所述颅内待治疗组织进行超声治疗的超声波；根据所述得到的超声接收信号补偿序列对所述超声波反射的回波信号进行 补偿聚焦，以通过超声激励接收设备显示输出所述颅内待治疗组织的超声成像。
- 如权利要求5所述的方法，其特征在于，控制所述高频超声换能器测量所述患者的颅骨厚度和超声波在所述患者颅骨中传播的声速的步骤，包括：根据所述高频超声换能器各个阵元预先设置的超声信号发射延迟时间，将所述高频超声换能器的聚焦点移动到所述患者颅骨的上下表面之间；调整所述高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，以将所述聚焦点根据预设的步长向所述患者颅骨的下表面移动；当所述患者颅骨下表面反射波达到最大时，获取所述高频超声换能器中间阵元与末端阵元的延迟时间差值，并获取所述高频超声换能器接收所述患者颅骨下表面反射波所需要的传播时间；根据所述延迟时间差值、所述传播时间以及预先设置的公式计算所述颅骨厚度和超声波在所述患者颅骨中传播的声速。
- 如权利要求6所述的方法，其特征在于，当所述患者颅骨下表面反射波达到最大时，获取所述高频超声换能器中间阵元与末端阵元的延迟时间差值的步骤之前，包括：根据所述聚焦点的回波幅度判断所述患者颅骨下表面反射波是否达到最大；是则，跳转到获取所述高频超声换能器中间阵元与末端阵元的延迟时间差值的步骤；否则，跳转到调整所述高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间的步骤。
- 一种基于权利要求1-4任一所述超声成像系统的超声成像装置，其特征在于，所述装置包括：参数测量单元，用于当接收到对患者的颅内待治疗组织进行超声治疗的请求时，控制所述高频超声换能器测量所述患者的颅骨厚度和超声波在所述患者颅骨中传播的声速；信号序列获取单元，用于根据所述测量得到的颅骨厚度和所述声速计算所述低频超声换能器各个阵元超声发射信号的相位和强度补偿值、以及超声接收信号的相位和强度补偿值，以得到超声发射信号序列和超声接收信号补偿序列；超声聚焦单元，用于根据所述得到的超声发射信号序列，控制所述低频超声换能器进行聚焦，以产生对所述颅内待治疗组织进行超声治疗的超声波；以及回波信号补偿单元，用于根据所述得到的超声接收信号补偿序列对所述超声波反射的回波信号进行补偿聚焦，以通过超声激励接收设备显示输出所述颅内待治疗组织的超声成像。
- 如权利要求8所述的装置，其特征在于，所述参数测量单元包括：聚焦点移动单元，用于根据所述高频超声换能器各个阵元预先设置的超声信号发射延迟时间，将所述高频超声换能器的聚焦点移动到所述患者颅骨的上下表面之间；延迟时间调整单元，用于调整所述高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间，以将所述聚焦点根据预设的步长向所述患者颅骨的下表面移动；时间获取单元，用于当所述患者颅骨下表面反射波达到最大时，获取所述高频超声换能器中间阵元与末端阵元的延迟时间差值，并获取所述高频超声换能器接收所述患者颅骨下表面反射波所需要的传播时间；以及厚度声速计算单元，用于根据所述延迟时间差值、所述传播时间以及预先设置的公式计算所述颅骨厚度和超声波在所述患者颅骨中传播的声速。
- 如权利要求9所述的装置，其特征在于，所述参数测量单元还包括：回波幅度判断单元，用于根据所述聚焦点的回波幅度判断所述患者颅骨下表面反射波是否达到最大，是则触发所述时间获取单元执行获取所述高频超声换能器中间阵元与末端阵元的延迟时间差值，否则触发所述延迟时间调整单元执行调整所述高频超声换能器中间阵元与末端阵元的超声信号发射延迟时间。
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