A method and system for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamic treatment of gliomas.

Abstract

This invention relates to the field of medical ultrasound therapy technology, and more particularly to a method and system for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamics treatment of gliomas. It includes: acquiring spatial localization information of the glioma target area and individualized skull characteristics of the patient; pre-compensating the emission parameters of each element of a multi-element phased-array ultrasound transducer based on this characteristic information to generate corrected emission parameters; driving the transducer to emit an ultrasound beam, causing the beam to pass through the skull and form a transcranial focused acoustic field in the target area based on the spatial localization information; applying ultrasound to the target area using this acoustic field in the presence of a sonosensitizer to activate the sonosensitizer and generate an acoustic dynamic effect; monitoring changes in the acoustic field state and / or tissue acoustic properties during treatment, and updating the emission parameters in real time based on the monitoring results to maintain stable focusing. This invention can compensate for acoustic beam distortion caused by the skull, improve the accuracy and stability of transcranial focusing, and achieve adaptive correction during treatment.

Description

Technical Field

[0001] This invention relates to the field of medical ultrasound therapy technology, and in particular to a method and system for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamics treatment of gliomas. Background Technology

[0002] Gliomas are among the most common primary malignant tumors of the central nervous system, characterized by invasive growth, high recurrence rates, and poor prognosis. Currently, the main clinical treatment approach is a comprehensive regimen of surgical resection combined with radiotherapy and chemotherapy. However, because these tumors often invade important functional areas or exhibit diffuse growth, complete resection is challenging. Furthermore, radiotherapy and chemotherapy are limited by dosage and systemic toxicity. Therefore, there is an urgent need to develop more precise and minimally invasive treatment techniques.

[0003] Sonodynamic therapy (SDT) utilizes ultrasound to activate sonosensitive agents accumulated in tumor tissue, generating cytotoxic reactive oxygen species that induce tumor cell death. Compared to photodynamic therapy, ultrasound penetrates deeper into biological tissues, making it particularly suitable for treating deep brain tumors, and thus showing promising application prospects in the field of glioma.

[0004] However, transcranial focused ultrasound faces a key physical bottleneck: the skull, as a high-density, non-uniform, multi-layered structure, strongly scatters, attenuates, and distorts ultrasound waves. Specifically, after passing through the skull, the focus shifts, the focal range expands, and the energy in the target area decreases; in severe cases, it may even be impossible to effectively focus at the tumor site. This directly limits the precision and efficacy of sonodynamic therapy.

[0005] To overcome the aforementioned problems, existing technologies propose pre-compensating the transmission parameters of phased array ultrasound transducers based on pre-treatment skull images (such as CT and MRI). A typical procedure involves acquiring information on the geometric morphology, density, or sound velocity distribution of the patient's skull, and using time reversal or phase conjugation methods to calculate the transmission phase, amplitude, or delay of each array element, ensuring that the ultrasound beams propagate transcranially and achieve in-phase superposition in the target area. These methods improve the initial focusing quality to some extent.

[0006] However, when performing focused ultrasound transcranially, the skull, as a high-density, non-uniform, and complex structure, will scatter, attenuate, and distort the propagation of ultrasound waves, which will lead to focus shift, focal range expansion, or energy reduction, making it difficult to stably concentrate ultrasound energy on the target area and affecting the treatment effect.

[0007] Existing transcranial ultrasound focusing compensation methods mostly rely on pre-calibrating the array transducer emission parameters based on skull imaging information acquired before treatment. While these methods can improve initial focusing to some extent, they are typically open-loop controls. During treatment, subtle changes in patient position, physiological activities, and changes in the acoustic properties of local tissues can all cause sound field drift, making it difficult to maintain focus stability consistently by relying solely on pre-treatment compensation.

[0008] In summary, current transcranial focused ultrasound (TCU) control methods remain in an open-loop mode with one-time pre-treatment compensation, lacking real-time monitoring and dynamic adaptive correction capabilities for the transcranial sound field. Therefore, there is an urgent need to develop a control method capable of dynamically updating emission parameters based on actual sound field feedback during treatment to maintain stable and precise focusing on the glioma target area, thereby improving the reliability and clinical efficacy of sonodynamic therapy. Summary of the Invention

[0009] The purpose of this invention is to provide a method and system for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for glioma acoustic dynamics treatment. By combining individualized skull feature information for pre-compensation and introducing an acoustic field monitoring and dynamic update mechanism during treatment, adaptive correction of the transcranial acoustic field is achieved, thereby improving the focusing accuracy and stability in glioma acoustic dynamics treatment.

[0010] To achieve the above objectives, the present invention adopts the following technical solution. In a first aspect, this application provides a method for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamic treatment of gliomas, comprising:

[0011] To obtain spatial localization information of the glioma target area and individualized characteristics of the patient's skull; Based on the individualized characteristics of the patient's skull, the transmission parameters of each element of the multi-element phased ultrasound transducer are pre-compensated to generate the corrected transmission parameters of each element. The multi-element phased ultrasonic transducer is driven to emit an ultrasonic beam according to the corrected emission parameters of each array element. Based on the spatial positioning information, the ultrasonic beam passes through the skull and forms a transcranial focused sound field at the target area of ​​the glioma. The transcranial focused sound field is used to apply ultrasound to the glioma target area to activate a sonosensitive agent in or around the glioma target area and generate a sonodynamic effect; wherein the sonosensitive agent is introduced into the glioma target area or around the glioma before or during treatment. The transcranial focused acoustic field state and / or changes in the acoustic properties of the skull and brain tissue are monitored, and the emission parameters of each array element are updated in real time based on the monitoring results.

[0012] Secondly, this application provides a transcranial acoustic field adaptively corrected ultrasound emission parameter control system for glioma acoustic dynamic therapy, used to execute the transcranial acoustic field adaptively corrected ultrasound emission parameter control method for glioma acoustic dynamic therapy as described in any one of the above, including: The image acquisition module is used to acquire spatial localization information of the glioma target area and individualized feature information of the patient's skull; The parameter calculation and pre-compensation module, based on the individualized feature information of the patient's skull, pre-compensates the transmission parameters of each element of the multi-element phased ultrasound transducer to generate the corrected transmission parameters of each element. The transcranial focusing module is used to drive the multi-element phased ultrasound transducer to emit an ultrasonic beam according to the corrected emission parameters of each array element, and to make the ultrasonic beam pass through the skull and form a transcranial focused sound field at the target area of ​​the glioma based on the spatial positioning information. A sonodynamic therapy module is used to apply ultrasound to the glioma target area using the transcranial focused sound field to activate a sonosensitive agent in the glioma target area or its surrounding area and generate a sonodynamic effect; wherein the sonosensitive agent is introduced into the glioma target area or its surrounding area before or during treatment. The monitoring and feedback update module is used to monitor the changes in the state of the transcranial focused sound field and / or the acoustic properties of the skull and brain tissue, and update the emission parameters of each array element in real time based on the monitoring results.

[0013] The application employs the above technical solution and has at least the following beneficial effects: First, it can improve the initial focusing effect of transcranial ultrasound. By acquiring individualized characteristic information of the patient's skull and pre-compensating the transmission parameters of each element of the multi-element phased array ultrasound transducer based on the individualized characteristic information, it is beneficial to reduce the phase distortion and energy attenuation caused by the skull to ultrasound propagation, making it easier for the ultrasound beam after transcranial propagation to form a focused sound field in the glioma target area.

[0014] Secondly, it can improve the focusing stability during treatment. This invention introduces a transcranial focused acoustic field monitoring and dynamic update mechanism for emission parameters during treatment. When the acoustic field state or the acoustic properties of the skull and brain tissue change during treatment, the emission parameters of each array element can be adjusted according to the feedback information, which helps to compensate for acoustic field drift and maintain stable focusing on the glioma target area.

[0015] Third, it helps improve the controllability of sonodynamic therapy for gliomas. This invention combines individualized pre-compensation of the skull with dynamic updates during the treatment process, introducing a sonosensitizer into the glioma target area or its surrounding region. This facilitates a more stable application of the transcranial focused sound field to the glioma target area, improves the consistency between the sonosensitizer activation process and the target area effect, and helps reduce the risk of non-target area ultrasound effects caused by focus shift.

[0016] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0017] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0018] Figure 1 This is a flowchart illustrating a method for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamic treatment of gliomas, according to an exemplary embodiment. Figure 2 This is a schematic diagram of the structure of a transcranial acoustic field adaptively corrected ultrasound emission parameter control system for the acoustic dynamic treatment of glioma, according to an exemplary embodiment. Figure 3 This is a schematic diagram illustrating the principle of pre-compensation of transmission parameters in this invention; Figure 4 This is a schematic diagram illustrating the control mechanism for monitoring and dynamically updating transmission parameters in this invention. Figure 5 This is a schematic diagram of the array element layout and array element control relationship of the multi-element phased ultrasonic transducer in this invention. Detailed Implementation

[0019] To make the objectives, technical solutions, and advantages of this application clearer, the technical solutions of this application will be described in detail below. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. Based on the embodiments in this application, all other implementation methods obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0020] For specific implementation details, please refer to [link / reference]. Figure 1 , Figure 1 This is a flowchart illustrating a transcranial acoustic field adaptive correction method for controlling ultrasound emission parameters in the acoustic dynamics treatment of gliomas, according to an exemplary embodiment, comprising: S1. Obtain spatial localization information of the glioma target area and individualized characteristic information of the patient's skull; S2. Based on the individualized feature information of the patient's skull, the transmission parameters of each element of the multi-element phased ultrasound transducer are pre-compensated to generate the corrected transmission parameters of each element. S3. Drive the multi-element phased ultrasonic transducer to emit an ultrasonic beam according to the corrected emission parameters of each array element, and make the ultrasonic beam pass through the skull and form a transcranial focused sound field at the target area of ​​the glioma based on the spatial positioning information. S4. Apply ultrasound to the glioma target area using the transcranial focused sound field to activate the acoustic sensitizer in or around the glioma target area and generate a acoustic dynamic effect; wherein the acoustic sensitizer is introduced into the glioma target area or around the glioma before or during treatment. S5. Monitor the changes in the state of the transcranial focused acoustic field and / or the acoustic properties of the skull and brain tissue, and update the emission parameters of each array element in real time according to the monitoring results, so as to maintain precise focusing on the target area of ​​the glioma and stable implementation of sonodynamic therapy.

[0021] Example 1 In specific implementation, such as step S1, firstly, head image data of the patient is acquired using medical imaging equipment. For example, a thin-slice scan (slice thickness ≤ 1 mm) of the patient's brain is performed using magnetic resonance imaging (MRI) to delineate the boundaries of the glioma lesion from the image, and calculate its three-dimensional coordinates, center position, and contour as spatial localization information of the target area. Simultaneously, individualized characteristic information of the patient's skull can be obtained through computed tomography (CT) images. This characteristic information may include skull thickness distribution, density distribution, and acoustic propagation-related parameters estimated therefrom. In one embodiment, an acoustic model of the skull can be established based on the grayscale values ​​of CT images, and the propagation velocity distribution and attenuation-related parameters of ultrasound waves in the skull can be obtained accordingly.

[0022] It should be noted that the aforementioned method can establish an acoustic model of the skull based on the grayscale values ​​of CT images, and thereby obtain the propagation velocity distribution and attenuation parameters of ultrasound waves in the skull. The porosity of the skull is estimated using the HU value from CT scans, and the density, sound velocity, and attenuation parameters are obtained based on the porosity, as shown in the formula:

[0023]

[0024]

[0025]

[0026] in, It is the maximum mass density of cortical bone. , , .

[0027] represents porosity, H represents HU value, d represents density, c represents sound velocity, and abs represents attenuation coefficient.

[0028] As described in step S2, a multi-element phased-array ultrasound transducer (e.g., a spherical array containing more than 64 independently driven elements) is used to emit therapeutic ultrasound. See also... Figure 5 The transducer adopts a spherical array or ring array structure, with array elements arranged in a regular manner to completely cover the skull's target area. Each array element is an independent driving unit, capable of receiving control signals individually and achieving precise control of transmission phase, transmission amplitude, and transmission time delay. This provides a hardware foundation for element-by-element pre-compensation based on the individualized characteristics of the patient's skull, while also supporting real-time fine-tuning of single-element transmission parameters during treatment to adapt to dynamic changes in the sound field state and tissue acoustic properties.

[0029] To overcome the distortion caused by the skull on ultrasound propagation, the system calculates the required transmission phase, transmission amplitude, and / or transmission time delay for each array element based on the individualized skull feature information obtained in step 1. The specific pre-compensation algorithm can employ either the time reversal method or the phase conjugation method; please refer to [link to relevant documentation]. Figure 3 This involves simulating the sound field propagating backward from a virtual sound source in the target area to each array element, and determining compensation values ​​based on the phase and amplitude of the virtual signals received by each array element. These compensation values ​​are then used as the transmission parameters for each array element, resulting in a set of corrected transmission parameters. This set of parameters enables the ultrasonic waves emitted by each array element to achieve in-phase superposition at the target area after passing through the skull.

[0030] As in step S3, the system loads the corrected transmission parameters into the drive circuit of the multi-element phased-array ultrasonic transducer, driving each element to emit ultrasonic waves according to the set center frequency (e.g., 500kHz to 1MHz), pulse repetition frequency, and transmission power. Since the transmission parameters have been pre-compensated for skull deformities, the phase distortion and energy attenuation of the ultrasonic beam are effectively canceled after passing through the skull, thereby forming a high-intensity transcranial focused sound field in the glioma target area (the location determined based on spatial positioning information). Verification shows that the spatial positioning error of this focal zone can be controlled within 1 mm, and the deviation between the actual sound pressure and the preset sound pressure at the focal zone is less than 10%.

[0031] As described in step S4, the sonosensitive agent can be introduced into the glioma target area or its surrounding area before or during treatment. The sonosensitive agent can be at least one of porphyrin-based, phthalocyanine-based, or nano-sound sensitizers. The sonosensitive agent is introduced into the patient's body before or during treatment. For example, it can be concentrated in the glioma target area by intravenous injection of porphyrin-based, phthalocyanine-based, or nano-sound sensitizers. After the sonosensitive agent reaches a predetermined concentration distribution, the transcranial focused sound field formed in step 3 is activated to irradiate the target area with ultrasound. The ultrasound activates the sonosensitive agent, generating reactive oxygen species (ROS), which in turn induce tumor cell apoptosis or necrosis, achieving sonodynamic therapy.

[0032] As described in step S5, during treatment, the patient may experience slight positional changes, tissue displacement due to breathing or heartbeat, or changes in local tissue temperature and acoustic properties caused by ultrasound. These factors can all cause the corrected sound field to drift. Therefore, the system inserts low-power monitoring ultrasound waves during treatment intervals (e.g., after every few treatment pulses), and the transcranial echo signals are received by a multi-element phased-array ultrasound transducer. Please refer to [link to relevant documentation]. Figure 4 The processor analyzes the phase shift and / or amplitude distortion between the current echo signal and the preset reference signal. If the shift or distortion exceeds a preset threshold (e.g., phase shift > 5° or amplitude attenuation > 10%), it triggers the recalculation of the emission parameters of each array element and dynamically updates the driving parameters to compensate for acoustic field drift and ensure that the target area always receives stable focused ultrasound.

[0033] By following the steps described above, the stability of the transcranial focused sound field can be maintained during treatment, thereby improving the consistency of sound field control in the sonodynamic treatment of gliomas.

[0034] This embodiment provides a complete transcranial acoustic field adaptive correction method for controlling the sonodynamic treatment of gliomas, including target localization, skull feature acquisition, pre-compensation, acoustic dynamic application, and dynamic monitoring feedback. Its advantages are: the pre-compensation step effectively offsets the phase distortion and energy attenuation caused by the skull, significantly improving the accuracy of initial focusing and focal domain acoustic intensity. The introduction of low-power monitoring of ultrasound and echo signals during treatment intervals enables real-time detection of acoustic field drift and dynamic updating of transmission parameters, overcoming the limitations of open-loop control in responding to patient movement or changes in tissue characteristics. Through a closed-loop feedback mechanism, the stability of the focused acoustic field in the target area is ensured throughout the treatment process, thereby improving the consistency and safety of sonodynamic therapy.

[0035] Example 2 In another embodiment, this embodiment is basically the same as embodiment 1, except that the method of obtaining individualized feature information of the patient's skull in step S101 is different.

[0036] In this embodiment, individualized features of the patient's skull can be obtained through reconstruction from magnetic resonance imaging data. For example, a magnetic resonance sequence suitable for short T2 tissue imaging can be used to obtain skull-related information, and a reconstruction algorithm can be combined to obtain the skull's sound velocity distribution or other acoustic features.

[0037] Specifically, the step of acquiring skull-related information using a magnetic resonance imaging sequence suitable for short T2 tissue imaging, and combining it with a reconstruction algorithm to obtain skull sound velocity distribution or other acoustic feature information, includes: By using deep networks, such as CNNs, to learn the mapping relationship between anatomical structures in T2 images and HU values ​​in CT images, pseudo-CT images are obtained. Then, using the conversion relationship of the CT images above, they are converted into acoustic parameters of the skull.

[0038] This implementation method can reduce reliance on CT images in specific application scenarios.

[0039] Example 3 This embodiment is basically the same as embodiment 1, except that the monitoring and dynamic update methods in step S5 are different.

[0040] In this embodiment, low-power monitoring pulses can be inserted between treatment pulses, and some or all array elements can receive transcranial echo signals, while the processor continuously analyzes the sound field change information.

[0041] For example, adaptive filtering or iterative optimization can be used to dynamically fine-tune the emission parameters of each array element to improve the tracking capability for rapid acoustic changes.

[0042] It should be noted that the adaptive filtering can be a Kalman filter or a least squares filter algorithm; the iterative optimization algorithm can be a genetic algorithm or a convex optimization algorithm.

[0043] Example 4 In this invention, the transmission parameters include at least one of transmission phase, transmission amplitude, and transmission time delay. Specifically: Transmission phase: By adjusting the initial phase of the transmitted signals of each array element, the wavefront shape of the ultrasonic beam can be controlled, so that the waves emitted by each array element are superimposed in phase in the target area. Phase correction is usually used as the main means in pre-compensation.

[0044] Emission amplitude: The attenuation degree varies in different regions of the skull. For paths with greater attenuation, appropriately increasing the emission amplitude of the corresponding array element can compensate for energy loss and make the sound pressure in the target area uniform.

[0045] Emission time delay: The focal point position can be controlled by adjusting the emission time of each element (i.e., electronic focusing). Time delay and phase are equivalent in narrowband signals, but can be used independently in broadband ultrasound to improve focusing flexibility.

[0046] In practical implementation, the system can employ both phase and amplitude correction (i.e., complex amplitude compensation) simultaneously, or it can use only phase correction to simplify calculations. Transmission time delay is often used for dynamic focusing or focal scanning.

[0047] Example 5 In a specific embodiment of the present invention, the step of pre-compensating the transmission parameters of each element of the multi-element phased ultrasound transducer based on individualized skull feature information to generate corrected transmission parameters for each element includes the following sub-steps: 5.1: Based on the individualized characteristics of the patient's skull, the compensation phase and / or compensation amplitude of each array element are calculated using the time reversal method or the phase conjugate method.

[0048] Taking the time-reversal method as an example: First, a three-dimensional sound propagation model is established based on CT / MRI data of the skull, including the skull's geometry, density, sound velocity, and attenuation distribution. Then, a virtual point sound source is placed at the center of the glioma target area, emitting a short pulse (such as a Gaussian pulse). The process of this pulse propagating backward through the skull to the surface of each element of the multi-element phased-array ultrasound transducer is simulated using wave equations (such as the k-space method or the finite-difference time-domain method), and the time-domain waveform received by each element is recorded. Next, the time-domain waveform is time-reversed (i.e., the time axis is reversed, making the later-arriving signal become the earlier-transmitted signal), obtaining the required transmission waveform for each element. The compensation phase and compensation amplitude for each element are extracted from the time-reversed waveform (for narrowband signals, the phase and amplitude after Fourier transform can be directly taken). The phase conjugation method is implemented in the frequency domain, that is, the transfer function of the forward propagation is complexly conjugated, which serves as the frequency response of the compensation filter.

[0049] 5.2: Use the compensated phase and / or compensated amplitude as the transmission parameters of each array element to generate the corrected transmission parameters of each array element.

[0050] The calculated compensation phase and / or compensation amplitude are assigned to the driving channel of each array element as the transmission parameters for that element. For systems requiring a transmission time delay, the compensation phase can be converted into a time delay at the corresponding frequency.

[0051] 5.3: The corrected emission parameters of each array element are used to ensure that the ultrasonic beams emitted by each array element are superimposed in phase at the target area of ​​the glioma after propagating through the skull.

[0052] When each array element emits ultrasonic waves according to the above-mentioned corrected emission parameters, since the pre-compensation has offset the phase distortion and amplitude attenuation caused by the skull, the ultrasonic waves of all array elements can reach the target area simultaneously and have the same phase after propagating through the skull, thus forming a strong focused sound field with in-phase superposition at the target area.

[0053] Example 6 In a preferred embodiment of the present invention, through the aforementioned pre-compensation and dynamic feedback correction, the system can control the three-dimensional spatial distance error between the actual focal point and the preset target area to within less than 1 mm. This error is verified using a high-precision hydrophone or magnetic resonance acoustic radiation force imaging (MR-ARFI). Specific testing method: A multi-element phased-array ultrasound transducer is placed outside a human skull specimen, and a miniature hydrophone is placed at the target area. The deviation between the focal point coordinates and the preset coordinates is measured. Experimental results show that, after adopting the adaptive correction method of the present invention, the average focal point positioning error is 0.3–0.8 mm, significantly better than the 3–5 mm error without correction. This accuracy meets the clinical requirements for sonodynamic treatment of gliomas and can avoid damage to adjacent important functional areas.

[0054] Example 7 In one embodiment of the invention, the system uses pre-compensation and dynamic power adjustment to ensure that the relative deviation between the actual sound pressure at the focal zone and the preset target sound pressure in the treatment plan is less than 10%. Specifically, before treatment, the required target sound pressure (e.g., 1 MPa) is calculated based on the target depth, skull attenuation, and the acoustic sensitizer activation threshold. During treatment, the actual sound pressure at the focal zone is estimated in real time using amplitude information from the monitored echo signal or an implanted miniature pressure sensor. When a deviation exceeding 10% is detected, the system compensates by adjusting the emission amplitude of each array element (increasing or decreasing it). For example, if the actual sound pressure is lower than 90% of the preset value, the overall emission power is increased to 1.1 times the preset value. This mechanism ensures the accuracy and repeatability of the sonodynamic therapy dosage, avoiding treatment failure due to insufficient energy or tissue damage due to excessive energy.

[0055] Example 8 This embodiment provides a transcranial acoustic field adaptive correction ultrasound emission parameter control system for the acoustic dynamics treatment of gliomas, used to implement the method embodiment described in any one of the above embodiments. The system includes: Image acquisition module 10: Used to acquire spatial localization information of the glioma target area and individualized feature information of the patient's skull. This module can connect to the hospital's PACS system or directly integrate with imaging equipment such as MRI and CT to acquire raw image data in DICOM format. Target area coordinates and skull acoustic parameters are extracted through image segmentation and 3D reconstruction algorithms.

[0056] Parameter calculation and pre-compensation module 20: Based on the individualized feature information of the patient's skull, the transmission parameters of each element of the multi-element phased-array ultrasound transducer are pre-compensated to generate the corrected transmission parameters of each element. This module is usually implemented by a high-performance computing unit (GPU or FPGA), which performs numerical calculations using the time reversal method or the phase conjugation method, and outputs the phase, amplitude, or delay values ​​of each element.

[0057] Transcranial focusing module 30: This module drives the multi-element phased-array ultrasonic transducer to emit an ultrasonic beam based on the corrected emission parameters of each element. Based on the spatial positioning information, the ultrasonic beam passes through the skull and forms a transcranial focused sound field at the glioma target area. This module includes a multi-channel arbitrary waveform generator, a power amplifier, and a multi-element phased-array ultrasonic transducer (such as a spherical array or a ring array). The number of transducer elements is typically 64–1024, with a center frequency range of 200 kHz–2 MHz.

[0058] Sonodynamic therapy module 40: Introduces a sonosensitizer into the glioma target area or its surrounding region, and applies ultrasound to the glioma target area using the transcranial focused sound field to activate the sonosensitizer and generate a sonodynamic effect. This module may include a sonosensitizer injection pump, treatment planning software, and an ultrasound irradiation timing controller to ensure synergistic effects between ultrasound and drugs.

[0059] Monitoring and Feedback Update Module 50: This module monitors changes in the transcranial focused acoustic field state and / or the acoustic properties of the skull and brain tissue, and updates the emission parameters of each array element in real time based on the monitoring results to maintain precise focusing on the glioma target area and stable implementation of sonodynamic therapy. This module is connected to a multi-element phased-array ultrasound transducer, acquires transcranial echo signals, performs signal processing and analysis, and triggers parameter updates.

[0060] In addition, the system includes one or more processors (such as a central processing unit (CPU) or a digital signal processor (DSP)) and a memory. The memory stores a computer program that, when executed by the processor, enables the system to implement all the steps of the aforementioned method. The processor is responsible for coordinating the workflow of each module, managing data communication, and executing feedback control algorithms.

[0061] The aforementioned modules can be integrated into a dedicated treatment device or distributed across different hardware platforms and connected via a network. This system can automatically complete the entire process from image acquisition, parameter calculation, ultrasound focusing to dynamic feedback correction, achieving precise and intelligent sonodynamic treatment for gliomas.

[0062] It is understood that the same or similar parts in the above embodiments can be referred to each other, and the contents not described in detail in some embodiments can be referred to the same or similar contents in other embodiments.

[0063] It should be noted that in the description of this application, the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance. Furthermore, in the description of this application, unless otherwise stated, "multiple" or "more" means at least two.

[0064] It should be understood that when an element is referred to as "fixed to" or "set on" another element, it may be directly on the other element or may have an intervening element present at the same time; when an element is referred to as "connected to" another element, it may be directly connected to the other element or may have an intervening element present at the same time. In addition, the term "connected" as used herein may include wireless connections; the word "and / or" as used includes any unit and all combinations of one or more of the associated listed items.

[0065] Any process or method description in the flowchart or otherwise herein can be understood as: representing a module, segment, or portion of code comprising one or more executable instructions for implementing a particular logical function or process, and the scope of the preferred embodiments of this application includes additional implementations in which functions may be performed not in the order shown or discussed, including substantially simultaneously or in reverse order depending on the function involved, as should be understood by those skilled in the art to which embodiments of this application pertain.

[0066] It should be understood that various parts of this application can be implemented using hardware, software, firmware, or a combination thereof. In the above embodiments, multiple steps or methods can be implemented using software or firmware stored in memory and executed by a suitable instruction execution system. For example, if implemented in hardware, as in another embodiment, it can be implemented using any one or a combination of the following techniques known in the art: discrete logic circuits having logic gates for implementing logical functions on data signals, application-specific integrated circuits (ASICs) having suitable combinational logic gates, programmable gate arrays (PGAs), field-programmable gate arrays (FPGAs), etc.

[0067] Those skilled in the art will understand that all or part of the steps of the methods in the above embodiments can be implemented by a program instructing related hardware. The program can be stored in a computer-readable storage medium, and when executed, the program includes one or a combination of the steps of the method embodiments.

[0068] Furthermore, the functional units in the various embodiments of this application can be integrated into a processing module, or each unit can exist physically separately, or two or more units can be integrated into a module. The integrated module can be implemented in hardware or as a software functional module. If the integrated module is implemented as a software functional module and sold or used as an independent product, it can also be stored in a computer-readable storage medium.

[0069] The storage media mentioned above can be read-only memory, disk, or optical disk, etc.

[0070] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of this application. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0071] Although embodiments of this application have been shown and described above, it is understood that the above embodiments are exemplary and should not be construed as limiting this application. Those skilled in the art can make changes, modifications, substitutions and variations to the above embodiments within the scope of this application.

Claims

1. A method for controlling ultrasound emission parameters in transcranial acoustic field adaptive correction for the acoustic dynamic treatment of gliomas, characterized in that, include: To obtain spatial localization information of the target area of ​​glioma and individualized feature information of the patient's skull; Based on the individualized characteristics of the patient's skull, the transmission parameters of each element of the multi-element phased ultrasound transducer are pre-compensated to generate the corrected transmission parameters of each element. The multi-element phased ultrasonic transducer is driven to emit an ultrasonic beam according to the corrected emission parameters of each array element. Based on the spatial positioning information, the ultrasonic beam passes through the skull and forms a transcranial focused sound field at the target area of ​​the glioma. The transcranial focused sound field is used to apply ultrasound to the glioma target area to activate a sonosensitive agent in or around the glioma target area and generate a sonodynamic effect; wherein the sonosensitive agent is introduced into the glioma target area or around the glioma before or during treatment. The transcranial focused acoustic field state and / or changes in the acoustic properties of the skull and brain tissue are monitored, and the emission parameters of each array element are updated in real time based on the monitoring results.

2. The method according to claim 1, characterized in that, The individualized characteristics of the patient's skull are obtained through at least one of the following methods: Skull density and thickness distribution information obtained from computed tomography images; Information on the distribution of sound velocity in the skull reconstructed from magnetic resonance imaging data; Skull phase distortion information is obtained by analyzing transcranial echo signals received by ultrasound detection array elements.

3. The method according to claim 1, characterized in that, The launch parameters include at least one of launch phase, launch amplitude, and launch time delay.

4. The method according to claim 1, characterized in that, Based on the individualized feature information of the patient's skull, the transmission parameters of each element of the multi-element phased array ultrasound transducer are pre-compensated to generate corrected transmission parameters for each element, including: Based on the individualized characteristics of the patient's skull, the compensation phase and / or compensation amplitude of each array element are calculated using the time reversal method or the phase conjugate method. The compensated phase and / or compensated amplitude are used as the transmission parameters of each array element to generate the corrected transmission parameters of each array element. The corrected emission parameters of each array element are used to ensure that the ultrasonic beams emitted by each array element are superimposed in phase at the target area of ​​the glioma after propagating through the skull.

5. The method according to claim 1, characterized in that, The monitoring of changes in the transcranial focused sound field state and / or acoustic properties of the skull and brain tissue includes: During or between treatment sessions, monitoring ultrasound waves are emitted and transcranial echo signals of the monitoring ultrasound waves are received. Information on changes in the state of the transcranial focused sound field and / or the acoustic properties of the skull and brain tissue is obtained based on the transcranial echo signal.

6. The method according to claim 1, characterized in that, The step of updating the transmission parameters of each array element in real time based on monitoring results includes: Analyze the phase shift and / or amplitude distortion of the transcranial echo signal relative to a preset reference signal; when the phase shift and / or amplitude distortion exceeds a preset threshold, recalculate and update the transmission parameters of each array element.

7. The method according to claim 1, characterized in that, The acoustic sensitizer is introduced into the glioma target area or its surrounding area before the ultrasound beam is emitted or during treatment. The sound-sensitizing agent is at least one of porphyrin-based sound-sensitizing agents, phthalocyanine-based sound-sensitizing agents, or nano-sound-sensitizing agents.

8. A transcranial acoustic field adaptively corrected ultrasound emission parameter control system for glioma acoustic dynamic therapy, used to execute the transcranial acoustic field adaptively corrected ultrasound emission parameter control method for glioma acoustic dynamic therapy according to any one of claims 1-7, characterized in that, include: The image acquisition module is used to acquire spatial localization information of the glioma target area and individualized feature information of the patient's skull; The parameter calculation and pre-compensation module, based on the individualized feature information of the patient's skull, pre-compensates the transmission parameters of each element of the multi-element phased ultrasound transducer to generate the corrected transmission parameters of each element. The transcranial focusing module is used to drive the multi-element phased ultrasound transducer to emit an ultrasonic beam according to the corrected emission parameters of each array element, and to make the ultrasonic beam pass through the skull and form a transcranial focused sound field at the target area of ​​the glioma based on the spatial positioning information. A sonodynamic therapy module is used to apply ultrasound to the glioma target area using the transcranial focused sound field to activate a sonosensitive agent in the glioma target area or its surrounding area and generate a sonodynamic effect; wherein the sonosensitive agent is introduced into the glioma target area or its surrounding area before or during treatment. The monitoring and feedback update module is used to monitor the changes in the state of the transcranial focused sound field and / or the acoustic properties of the skull and brain tissue, and update the emission parameters of each array element in real time based on the monitoring results.

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