A device for simultaneous imaging of structure and function during surgery for brain tumor resection

Abstract

The present invention relates to an intraoperative structural function synchronous imaging device for brain tumor resection, comprising a multiplexed transducer, a recording electrode and a controller; the controller comprises a phase amplitude compensation module, a delay control module, a synchronous receiving module, an echo signal processing module, an acoustic-electric signal processing module and a synchronous imaging module; by multiplexing an ultrasonic transducer to generate an image according to acoustic-electric signals and echo signals, and synchronously correlating the images, key information such as neuroanatomy, tumor structure and functional areas can be provided in real time during the operation, and the tumor can be systematically guided to be removed, helping surgeons to make more accurate decisions and improving the accuracy and effectiveness of the operation.

Description

Technical Field

[0001] The present invention relates to the technical field of imaging of pathological tissue structure and neural function, and more specifically to an intraoperative structure-function synchronous imaging device for brain tumor resection. Background Art

[0002] Brain tumors are one of the most common brain diseases worldwide, with high morbidity and mortality.

[0003] (Siegel RL, Miller KD, Fuchs HE, Jemal A. Cancer statistics, 2022[J]. CA Cancer J Clinicians, 2022, 72(1): 7-33) In the surgical treatment of brain tumors, gross total removal (GTR) can improve progression-free survival (PFS) and overall survival (OS), and GTR depends on the precise localization of brain tumors, the detailed demarcation of tumor boundaries, and the accurate identification of residual tumors. However, brain tumor tissue often infiltrates normal brain tissue in a way that cannot be perceived by the naked eye.

[0004] Functional area localization technology provides guidance for neurosurgeons to locate tumor tissue and brain functional areas. Therefore, tumor resection relies heavily on preoperative and intraoperative auxiliary technologies to distinguish brain tumors, nerve fiber bundles and functional areas. At present, preoperative and intraoperative imaging technologies such as diffusion tensor imaging (DTI), transcranial magnetic stimulation (TMS), intraoperative ultrasound (IOUS) and intraoperative neurophysiological monitoring (IONM) have been widely used in clinical practice. Preoperative localization of cerebral cortical functional areas and brain white matter fiber bundles plays a vital role in surgical path planning, which minimizes the risk of surgical complications and facilitates objective postoperative evaluation of patients. (Manan AA, Yahya N, Idris Z, Manan HA. The Utilization of Diffusion Tensor Imaging as an Image-Guided Tool in Brain Tumor Resection Surgery: A Systematic Review [J]. Cancer, 2022, 14(10): 2466) DTI can reconstruct complex white matter pathways to ensure a comprehensive understanding of the brain's structural connections, while TMS can provide in-depth insights into the dynamic patterns of brain activity, helping to identify important areas responsible for key functions. (Wang Q, Zhang D, Zhao YY, Hai H, Ma YW. Effects of high-frequency repetitive transcranial magnetic stimulation over the contralesional motor cortex on motor recovery in severe hemiplegic stroke: A randomized clinical trial [J]. Brain Stimulation, 2020, 13(4): 979-986) In general, the integration of preoperative localization and reconstruction techniques can not only improve the safety and effectiveness of surgery, but also promote the continuous improvement of neurosurgical practice.

[0005] However, during surgical resection, brain displacement of up to 1 cm may occur due to multiple factors such as cerebrospinal fluid outflow and lesion resection. As the operation progresses, the severity of brain displacement will gradually reduce the accuracy of preoperative images, thereby limiting its effectiveness in guiding surgery. Intraoperative imaging technology is an important auxiliary means of brain tumor surgery. It can obtain dynamic and real-time key data during the operation, allowing surgeons to adjust surgical methods according to the changing anatomical environment and improve the accuracy and effectiveness of the operation. (Hou Y, Li Y, Li Q, Yu Y, Tang J. Full-course resection control strategy in glioma surgery using both intraoperative ultrasound and intraoperative MRI [J]. Front Oncol, 2022, 12: 955807) IOUS provides continuous information about the location of the tumor, which helps to perform more accurate and targeted resection. IONM is used to monitor the functional integrity of the nervous system during surgery, avoid permanent nerve damage, and maximize the patient's postoperative neurological function. (Parvizi J, Kastner S. Promises and limitations of human intracraniole electroencephalography [J]. Nat Neurosci, 2018, 21(4): 474-483) Therefore, real-time visualization of tumors and functional areas can achieve precise navigation, ensuring the surgical goals of tumor resection and nerve function protection.

[0006] In recent years, with the increasing requirements for medical precision, the limitations of intraoperative technology have become increasingly prominent. For example, IOUS can provide high-quality structural imaging but cannot directly obtain neural activity, while IONM is good at providing real-time data on neural activity but needs to be combined with other imaging methods to obtain complete structural information. The dual understanding of anatomical structure and neural function during surgery can enable surgeons to guide surgery more accurately and reduce the inherent risks of patients. The current imaging method that can simultaneously display the structure of the lesion and the functional area during surgery is intraoperative magnetic resonance imaging (iMRI). However, iMRI requires a dedicated operating room equipped with a shielding device to isolate the external magnetic field. In addition, the examination process takes a long time (usually 10 to 30 minutes) and requires the temporary suspension of the surgical process, which may increase the risk of postoperative infection. To date, there is no economical imaging method that can synchronously display structure and function in real time during surgery. With the continuous development of medical and surgical technology, the need to simultaneously obtain anatomical structure and functional information is becoming increasingly urgent. This need is particularly prominent in complex tumor resections. Therefore, integrating technologies that can provide both structural and functional data is crucial to improving efficacy. Summary of the invention

[0007] In view of this, an object of the present invention is to provide an intraoperative structural and functional synchronous imaging device for brain tumor resection.

[0008] In order to solve the above technical problems, the technical solution of the present invention is: an intraoperative structural and functional synchronous imaging device for brain tumor resection, comprising a multiplexed transducer, a recording electrode and a controller;

[0009] The multiplexed transducer comprises an ultrasonic output unit and an echo receiving unit; the ultrasonic output unit comprises a transducer array, the transducer array comprises a plurality of transducer array elements arranged in an array, and the echo receiving unit is used to receive an echo signal;

[0010] The recording electrode is used to receive acoustic and electrical signals;

[0011] The controller includes a phase amplitude compensation module, a time delay control module, a synchronous receiving module, an echo signal processing module, an acoustic and electrical signal processing module and a synchronous imaging module;

[0012] The phase amplitude compensation module is used to generate a phase amplitude compensation signal corresponding to each transducer array element, and generate an excitation signal of the corresponding transducer array element according to the phase amplitude compensation signal;

[0013] The delay control module is used to generate an absolute delay signal of each transducer according to the relative delay information between the transducer array elements, and configure the corresponding transducer array element according to the absolute delay signal;

[0014] The synchronous receiving module establishes a synchronous time stamp for the echo signal and the acoustic-electric signal according to the sound beam output time of the ultrasonic output unit;

[0015] The echo signal processing module is used to process the echo signal to generate an echo processing image in a pre-constructed synchronous coordinate system;

[0016] The acoustic and electrical signal processing module is used to process the acoustic and electrical signals to generate an acoustic and electrical processed image in the synchronous coordinate system;

[0017] The synchronous imaging module associates the image features of the echo-processed image and the electroacoustic-processed image in the synchronous coordinate system to generate a synchronous brain structure image model.

[0018] Further: the phase amplitude compensation module is configured with a phase and amplitude compensation sub-strategy, and the phase and amplitude compensation sub-strategy includes

[0019] Step A1, calculating the corresponding Heinz value according to the skull CT image;

[0020] Step A2, obtaining the theoretical transmission range of each array element according to the Heinrich value of the target position;

[0021] Step A3: time-reversing the actual signal received by each array element according to the theoretical transmission distance to obtain a time-reversed signal;

[0022] Step A4, subtracting a preset compensation threshold from a time-reversed signal corresponding to each array element to obtain a deviation compensation value;

[0023] Step A5: generating a phase amplitude compensation signal of the transducer array element according to the deviation compensation value.

[0024] Further: the delay control module is configured with a delay configuration sub-strategy, and the delay configuration sub-strategy includes

[0025] Step A1, determining the position of the focus relative to the center of the array element according to a pre-configured reflectivity expression and an acoustic-electric signal expression;

[0026] Step A2, calculating the distance between the focus and the center of the array element;

[0027] Step A3: Calculate the relative delay value of each pixel according to a preset delay configuration algorithm;

[0028] Step A4: Generate corresponding relative delay information according to the relative delay value.

[0029] Further: the reflectivity is expressed as

[0030]

[0031] Where r is the reflectivity, p r is the echo sound pressure, p 0 is the incident sound pressure, z 1 is the acoustic impedance of the first medium, z 2 is the acoustic impedance of the second medium.

[0032] Further: the acoustic-electric signal expression is

[0033]

[0034] in, is the acoustic signal, J I =J I (x,y,z) is a distributed current source, is the lead field of lead i, σ 0 is the initial conductivity, K is the acoustic-electric effect coefficient, ΔP is the change in the ultrasonic sound pressure at the corresponding site, (x, y, z) is the coordinate of the site in the rectangular coordinate system of ultrasonic focusing, and f PRF is the pulse repetition frequency, and t is the ultrasonic propagation time.

[0035] Further: the delay configuration algorithm is

[0036]

[0037] Among them, τ i is the relative delay value corresponding to the i-th array element, s is the distance from the center array element to the focus, l i is the distance from the ith array element to the center array element, and c is the speed of ultrasound propagation in human tissue.

[0038] Further: the echo signal processing module includes an echo preprocessing unit, an echo data optimization unit and an echo imaging unit;

[0039] The echo preprocessing unit is used to preprocess the echo signal;

[0040] The echo data optimization unit is used to optimize the data of the echo signal;

[0041] The echo imaging unit is used to generate an echo processing image according to the echo signal.

[0042] Further: the acoustic and electrical signal processing module includes an acoustic and electrical preprocessing unit, an acoustic and electrical decoding unit, and an acoustic and electrical space mapping unit;

[0043] The acoustic and electrical preprocessing unit is used to preprocess the acoustic and electrical signals;

[0044] The acoustic and electrical decoding unit is used to decode the acoustic and electrical signals to obtain corresponding acoustic and electrical signal features;

[0045] The acoustic-electrical mapping unit is used to map the acquired acoustic-electrical signal features to a synchronous coordinate system to obtain a corresponding acoustic-electrical processed image.

[0046] The technical effects of the present invention are mainly reflected in the following aspects:

[0047] 1. Existing intraoperative assisted imaging technologies usually have difficulty in taking into account both structural imaging and fMRI, while intraoperative fMRI has a certain time delay and requires the patient to maintain a relatively fixed position. The device has a millisecond-level time resolution and can provide key information about neuroanatomy, tumor structure and functional areas in real time during surgery, systematically guide tumor resection, help surgeons make more accurate decisions, and improve the accuracy and effectiveness of surgery.

[0048] 2. Transcranial focused ultrasound is non-invasive and highly targeted. It can accurately target the target brain area and achieve non-invasive structural-neural brain synchronous imaging with millimeter-level spatial resolution.

[0049] Compared with the existing multimodal synchronous functional-structural brain imaging system, this device avoids the shortcomings of time-consuming synchronous data acquisition, cross-fusion constraints of different modal imaging data, and serious interference between devices. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] Figure 1 : Schematic diagram of the signal transmission principle of the use status of the synchronous imaging device of the present invention;

[0051] Figure 2 : Schematic diagram of the structure of synchronous information content of the synchronous imaging device of the present invention;

[0052] Figure 3 : Workflow diagram of the synchronous imaging device of the present invention;

[0053] Figure 4 : Schematic diagram of the time reversal method principle of the synchronous imaging device of the present invention;

[0054] Figure 5 : Focusing and scanning mode diagram of the phased array probe of the synchronous imaging device of the present invention;

[0055] Figure 6 : The signal processing workflow diagram of the synchronous imaging device of the present invention. DETAILED DESCRIPTION

[0056] The specific implementation modes of the present invention are further described below in conjunction with the accompanying drawings to make the technical solutions of the present invention easier to understand and grasp.

[0057] The overall schematic diagram of the intraoperative structural and functional synchronous imaging device for brain tumor resection is shown in the figure. Figure 1As shown. The device mainly includes a phase amplitude compensation module, a delay control module, a synchronous receiving module, an echo signal processing module, an acoustic-electric signal processing module and a synchronous imaging module. Among them, the phase amplitude compensation module calculates the phase difference caused by the skull and compensates for it, so as to achieve adaptive intracranial sound wave precise focusing and improve imaging resolution. The delay control module is used to emit highly spatially targeted focused ultrasound and accurately scan specific brain areas. Based on the reflection principle of sound waves, echo signals related to the acoustic impedance of tissues (normal brain tissues, lesions) can be obtained. At the same time, based on the acoustic-electric effect, the acoustic-electric signal reflecting the current density distribution of neural signals can be obtained through the coupling between the electric field of the brain's electrophysiological activity and the acoustic field of the focused ultrasound. The echo signal processing module and the acoustic-electric signal processing module are used to continuously receive and collect echo signals reflected from the target brain area and the acoustic-electric signals generated by the acoustic-electric effect while the focused ultrasound encodes and scans the target brain area. The synchronous imaging module further analyzes and processes the collected echo signals and acoustic and electrical signals, extracts features from the echo signals to identify and locate the lesion area, and decodes the acoustic and electrical signals to reveal the dynamic changes in brain electrical activity and its association with brain function status. The structural and functional synchronous imaging module images and correlates the processed echo and acoustic and electrical signal information, maps the lesion location, boundaries, and its relationship with brain tissue and nerve fiber bundles, and thus systematically guides the removal of the tumor.

[0058] Reference Figure 1 and Figure 2 As shown, the entire detection process is: the ultrasonic transmitting system generates a beam to scan the location area of ​​interest, the EEG acquisition system records the EEG signal and the acoustic-electric signal after ultrasonic modulation, and the signal processing system effectively extracts the high-frequency and low-frequency signals respectively, records and saves the data, processes and images the data, and decodes the electric field distribution of the source signal. These works have theoretically and experimentally verified the feasibility of an intraoperative structural and functional synchronous imaging device for tumor resection, and provided a theoretical basis for the proposal of the present invention. A device for intraoperative structural and functional synchronous imaging for brain tumor resection, including a multiplexed transducer, a recording electrode, and a controller;

[0059] The multiplexed transducer comprises an ultrasonic output unit and an echo receiving unit; the ultrasonic output unit comprises a transducer array, the transducer array comprises a plurality of transducer array elements arranged in an array, and the echo receiving unit is used to receive an echo signal;

[0060] The recording electrode is used to receive acoustic and electrical signals; the phased array element receives the echo signal in sequence according to the ultrasonic transmission delay, and converts it into an electrical signal, the frequency of which is usually MHz, to ensure sufficient time resolution and imaging quality; at the same time, the acoustic and electrical signals are collected by the EEG amplifier through the recording electrode, the frequency of which is usually kHz, which is suitable for the frequency range of EEG signals. The two signals are synchronously transmitted to the computer, ensuring that signal analysis and medical image reconstruction can be effectively performed in subsequent steps.

[0061] The controller includes a phase amplitude compensation module, a delay control module, a synchronous receiving module, an echo signal processing module, an acoustic and electrical signal processing module and a synchronous imaging module; Figure 3 As shown, the flow chart of the method of intraoperative structural and functional synchronous imaging device for brain tumor resection is as follows Figure 3 As shown, the entire imaging process is: the probe generates a focused ultrasonic beam to scan the location area of ​​interest, and the ultrasonically modulated acoustic and electrical signals and echo signals are collected and recorded. Subsequently, the two signals are effectively processed and imaged to map the structure and electric field distribution of the location area of ​​interest. These works have theoretically and experimentally verified the feasibility of the brain structure-neural function synchronous imaging device. The application of this invention will greatly promote the precision and individualization of tumor surgery and provide patients with safer and more effective treatment options. An intraoperative structural and functional synchronous imaging device for brain tumor resection, the device includes the following steps:

[0062] The ultrasonic transmitting system sets appropriate parameters such as pulse repetition frequency, pulse width, sound pressure, etc., connects the ultrasonic driving device and the ultrasonic transducer, and realizes the emission of the focused sound beam.

[0063] The ultrasonic transducer receives the echo signal and converts it into an electrical signal, which is then amplified by a pulse gain circuit and recorded. The recording electrodes and EEG amplifier are connected to collect and record the acoustic and electrical signals.

[0064] The delayed emission rules of the transducer array elements are set to control the direction and focal position of the sound beam, and the focus of the sound beam is moved within the target area to achieve a comprehensive scan of the target tissue. At the same time, the signals of each scanning point are collected.

[0065] The echo signals and acoustic and electrical signals collected at each point are processed. The distribution of different tissues in the target area is obtained by analyzing the intensity distribution and delay difference of the echo signals; the acoustic and electrical signals are decoded and imaged to present the distribution image of the source electric field in the target area.

[0066] By correlating tissue images and electric field images at corresponding spatial locations, synchronous imaging of brain structure and neural function is achieved, providing key information for tissue positioning and neural activity. The specific technical means are as follows:

[0067] The phase amplitude compensation module is used to generate a phase amplitude compensation signal corresponding to each transducer array element, and generate an excitation signal of the corresponding transducer array element according to the phase amplitude compensation signal; due to the material inhomogeneity of the skull and the large difference between the acoustic characteristics of the skull and the surrounding tissues, the ultrasonic beam often attenuates and deviates when passing through the skull, resulting in the inability to achieve effective focusing at the predetermined focal point. In order to achieve precise focusing at the focal point, phase compensation is usually performed on each array element of the ultrasonic transducer. One of the effective methods is to implant a hydrophone, that is, to implant a hydrophone at the target point in the skull to receive the ultrasonic signal outside the skull, so as to determine the phase delay of the excitation signal of each array element caused by the skull. Subsequently, the delay parameters of each array element can be adjusted according to these data to achieve phase compensation. However, the implantation process of the hydrophone has certain risks and may cause irreversible damage to the brain. Therefore, in order to avoid this risk, the time reversal method can be used, combined with amplitude compensation to achieve non-invasive transcranial focusing.

[0068] The phase amplitude compensation module is configured with phase and amplitude compensation sub-strategies, and the amplitude compensation sub-strategies include

[0069] Step A1, calculating the corresponding Heinz value according to the skull CT image;

[0070] Step A2, obtaining the theoretical transmission range of each array element according to the Heinrich value of the target position;

[0071] Step A3: time-reversing the actual signal received by each array element according to the theoretical transmission distance to obtain a time-reversed signal;

[0072] Step A4, subtracting a preset compensation threshold from a time-reversed signal corresponding to each array element to obtain a deviation compensation value;

[0073] Step A5: generating a phase amplitude compensation signal of the transducer array element according to the deviation compensation value.

[0074] Reference Figure 4 As shown, any point O in the brain emits an ultrasonic signal p O (t), the signal passes through the non-uniform medium of the skull and brain and is received by the ultrasound transducer array outside the skull. The signal received by each transducer array element is recorded as p i (r i ,t)(The position vector of point O is r 0 , the position vector of the i-th array element is (r i ). Using the Heinz value of the skull slice, the attenuation of the signal during propagation can be calculated, and the signal p received by each array element can be calculated. i (r i ,t) time-reversed, we get p i (r i,Tt). To compensate for the attenuation of the ultrasonic signal amplitude caused by the skull, the amplitude of the time-reversed signal emitted by each array element is adjusted to 1Pa as the excitation signal. Subsequently, the adjusted signal is emitted at the corresponding transducer array element. At this time, the sound wave will focus on point O and reduce the sidelobe energy beside the non-focal point in the skull, so as to achieve precise ultrasonic focusing at point O. Combined with the Heinz value of skull CT, time reversal of each focal point can ensure that the ultrasonic wave has the maximum energy and the best focal shape when reaching each target point, so as to achieve precise focusing of transcranial ultrasound and improve the spatial accuracy and intensity accuracy of transcranial focused ultrasound. Phase and amplitude compensation are performed on each array element of the ultrasonic transducer. Phase compensation can make the ultrasonic waves emitted by each array element superimposed in phase at the focus, forming a focal spot at the predetermined focal point, while amplitude compensation can effectively enhance the sound intensity at the focus, forming a more uniform and significant sound field in the focal area. Combined with phase and amplitude compensation, a high-energy-density acoustic focal spot can be formed at the predetermined focus at the focus, further improving the focusing effect and imaging quality.

[0075] Reference Figure 5 As shown, the delay control module is used to generate an absolute delay signal for each transducer according to the relative delay information between the transducer array elements, and configure the corresponding transducer array elements according to the absolute delay signal; after the focused ultrasound is emitted, the sound beam is reflected at the structure or interface inside the object to form an echo, and at the same time, the electrical signal is encoded in the focusing area to generate an acoustic-electrical signal.

[0076] The delay control module is configured with a delay configuration sub-strategy, and the delay configuration sub-strategy includes

[0077] Step A1, determining the position of the focus relative to the center of the array element according to a pre-configured reflectivity expression and an acoustic-electric signal expression;

[0078] The reflectivity is expressed as

[0079]

[0080] Where r is the reflectivity, p r is the echo sound pressure, p 0 is the incident sound pressure, z 1 is the acoustic impedance of the first medium, z 2 is the acoustic impedance of the second medium.

[0081] The acoustic-electric signal expression is:

[0082]

[0083] in, is the acoustic signal, J I =J I(x,y,z) is a distributed current source, is the lead field of lead i, σ 0 is the initial conductivity, K is the acoustic-electric effect coefficient, ΔP is the change in the ultrasonic sound pressure at the corresponding site, (x, y, z) is the coordinate of the site in the rectangular coordinate system of ultrasonic focusing, and f PRF is the pulse repetition frequency, and t is the ultrasonic propagation time.

[0084] Step A2, calculating the distance between the focus and the center of the array element;

[0085] Step A3: Calculate the relative delay value of each pixel according to a preset delay configuration algorithm; the delay configuration algorithm is:

[0086]

[0087] Among them, τ i is the relative delay value corresponding to the i-th array element, s is the distance from the center array element to the focus, l i is the distance from the ith array element to the center array element, and c is the speed of ultrasound propagation in human tissue. , usually 1540m / s.

[0088] Step A4, generate corresponding relative delay information according to the relative delay value. The scanning of focused ultrasound depends on the precise control of each array element in the ultrasonic phased array. In this process, by applying different delays to each array element in the ultrasonic phased array, it can be ensured that the waveforms emitted by each array element arrive synchronously at a certain point in space (i.e., the focus), thereby forming a beam focusing area (i.e., focal spot) at this point. In addition, by dynamically changing the relative delays between different array elements, dynamic adjustment of the sound beam direction can be achieved. This dynamic adjustment not only utilizes the flexibility of each array element to dynamically focus both the focused emission and focused reception processes of the signal, but also allows the focus position of the sound beam to be controlled so that the focus moves within the target area, thereby performing a comprehensive scan of the area for obtaining echoes and acoustic and electrical signals at different positions.

[0089] Reference Figure 6 As shown, the synchronous receiving module establishes a synchronous time stamp for the echo signal and the acoustic-electric signal according to the sound beam output time of the ultrasonic output unit;

[0090] The echo signal processing module is used to process the echo signal to generate an echo processing image in a pre-constructed synchronous coordinate system; the echo signal processing module includes an echo pre-processing unit, an echo data optimization unit and an echo imaging unit;

[0091] The echo preprocessing unit is used to preprocess the echo signal; after the echo signal is recorded, it is necessary to perform preprocessing such as amplification and filtering on the echo signal to improve the quality of the signal.

[0092] The echo data optimization unit is used to optimize the data of the echo signal; then time gain compensation, dynamic aperture, logarithmic compression and other technologies are used to adjust echoes at different depths and optimize the spatial resolution of the image.

[0093] The echo imaging unit is used to generate an echo processing image according to the echo signal. Finally, the data is converted into an image matrix and linearly interpolated to obtain high-quality imaging results, revealing structural information such as the location, shape, size, etc. of the lesion.

[0094] The acoustic and electrical signal processing module is used to process the acoustic and electrical signals to generate an acoustic and electrical processed image in the synchronous coordinate system; the acoustic and electrical signal processing module includes an acoustic and electrical preprocessing unit, an acoustic and electrical decoding unit, and an acoustic and electrical space mapping unit;

[0095] The acoustic and electrical preprocessing unit is used to preprocess the acoustic and electrical signals; after recording the acoustic and electrical signals, the acoustic and electrical signals need to be amplified and passed through a pulse repetition frequency bandpass filter.

[0096] The acoustic and electrical decoding unit is used to decode the acoustic and electrical signals to obtain corresponding acoustic and electrical signal characteristics; then, the filtered acoustic and electrical signals are decoded using Hilbert transform to obtain decoded acoustic and electrical signals containing source signal waveform, frequency, and amplitude characteristics.

[0097] The acoustic-electrical mapping unit is used to map the acoustic-electrical signal features to a synchronous coordinate system to obtain a corresponding acoustic-electrical processed image. Extracting features and mapping them to corresponding spatial positions can reflect the current source distribution in the scanned brain area and the position and direction of the imaging fiber bundle.

[0098] The synchronous imaging module associates the image features of the echo-processed image and the electroacoustic-processed image in the synchronous coordinate system to generate a synchronous brain structure image model.

[0099] Of course, the above are only typical examples of the present invention. In addition, the present invention may also have many other specific implementations. All technical solutions formed by equivalent replacement or equivalent transformation fall within the scope of protection required by the present invention.

Claims

1. A device for synchronous imaging of structure and function during brain tumor resection, characterized in that: It includes a multiplexed transducer, a recording electrode, and a controller; The multiplexed transducer comprises an ultrasonic output unit and an echo receiving unit; the ultrasonic output unit comprises a transducer array, the transducer array comprises a plurality of transducer array elements arranged in an array, and the echo receiving unit is used to receive an echo signal; The recording electrode is used to receive acoustic and electrical signals; The controller includes a phase amplitude compensation module, a time delay control module, a synchronous receiving module, an echo signal processing module, an acoustic and electrical signal processing module and a synchronous imaging module; The phase amplitude compensation module is used to generate a phase amplitude compensation signal corresponding to each transducer array element, and generate an excitation signal of the corresponding transducer array element according to the phase amplitude compensation signal; The delay control module is used to generate an absolute delay signal of each transducer according to the relative delay information between the transducer array elements, and configure the corresponding transducer array element according to the absolute delay signal; The synchronous receiving module establishes a synchronous time stamp for the echo signal and the acoustic-electric signal according to the sound beam output time of the ultrasonic output unit; The echo signal processing module is used to process the echo signal to generate an echo processing image in a pre-constructed synchronous coordinate system; The acoustic and electrical signal processing module is used to process the acoustic and electrical signals to generate an acoustic and electrical processed image in the synchronous coordinate system; The synchronous imaging module associates the image features of the echo-processed image and the acoustic-electrical-processed image in the synchronous coordinate system to generate a synchronous brain structure image model; The phase amplitude compensation module is configured with an amplitude compensation sub-strategy, and the amplitude compensation sub-strategy includes Step A1, calculating the corresponding Heinz value according to the skull CT image; Step A2, obtaining the theoretical transmission range of each array element according to the Heinrich value of the target position; Step A3: time-reversing the actual signal received by each array element according to the theoretical transmission distance to obtain a time-reversed signal; Step A4, subtracting a preset compensation threshold from a time-reversed signal corresponding to each array element to obtain a deviation compensation value; Step A5, generating a phase amplitude compensation signal of the transducer array element according to the deviation compensation value; The delay control module is configured with a delay configuration sub-strategy, and the delay configuration sub-strategy includes Step A1, determining the position of the focus relative to the center of the array element according to a pre-configured reflectivity expression and an acoustic-electric signal expression; Step A2, calculating the distance between the focus and the center of the array element; Step A3: Calculate the relative delay value of each pixel according to a preset delay configuration algorithm; Step A4: Generate corresponding relative delay information according to the relative delay value.

2. The device for synchronous imaging of structure and function during brain tumor resection as claimed in claim 1, characterized in that: The reflectivity is expressed as Where r is the reflectivity, p r is the echo sound pressure, p0 is the incident sound pressure, z1 is the acoustic impedance of the first medium, and z2 is the acoustic impedance of the second medium.

3. The device for synchronous imaging of structure and function during brain tumor resection as claimed in claim 2, characterized in that: The acoustic-electric signal expression is: in, is the acoustic signal, J I =J I ( x,y,z ) is a distributed current source, is the lead field of lead i, σ0 is the initial conductivity, K is the acoustic-electric effect coefficient, ΔP is the change in the ultrasonic sound pressure at the corresponding site, (x, y, z) is the coordinate of the site in the rectangular coordinate system of ultrasonic focusing, and f PRF is the pulse repetition frequency, and t is the ultrasonic propagation time.

4. The device for synchronous imaging of structure and function during brain tumor resection as claimed in claim 1, characterized in that: The delay configuration algorithm is: Among them, τ i is the relative delay value corresponding to the i-th array element, s is the distance from the center array element to the focus, l i is the distance from the ith array element to the center array element, and c is the speed of ultrasound propagation in human tissue.

5. The device for synchronous imaging of structure and function during brain tumor resection as claimed in claim 1, characterized in that: The echo signal processing module includes an echo preprocessing unit, an echo data optimization unit and an echo imaging unit; The echo preprocessing unit is used to preprocess the echo signal; The echo data optimization unit is used to optimize the data of the echo signal; The echo imaging unit is used to generate an echo processing image according to the echo signal.

6. The device for synchronous imaging of structure and function during brain tumor resection as claimed in claim 1, characterized in that: The acoustic and electrical signal processing module includes an acoustic and electrical preprocessing unit, an acoustic and electrical decoding unit, and an acoustic and electrical space mapping unit; The acoustic and electrical preprocessing unit is used to preprocess the acoustic and electrical signals; The acoustic and electrical decoding unit is used to decode the acoustic and electrical signals to obtain corresponding acoustic and electrical signal features; The acoustic-electrical space mapping unit is used to map the acquired acoustic-electrical signal features to a synchronous coordinate system to obtain a corresponding acoustic-electrical processing image.

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