A device and method for visualizing the location of an ultrasound brain modulation target region

Abstract

This application discloses a visual ultrasound-guided brain modulation target localization device and method. The device includes: an ultrasound-guided brain modulation module for generating focused ultrasound waves and emitting them onto a target biological sample to achieve ultrasound modulation; a photoacoustic signal excitation module including a pulsed laser and a scanning mechanism for focusing the pulsed laser generated by the pulsed laser onto the target biological sample through the scanning mechanism to generate a target photoacoustic signal; a photoacoustic signal processing module for performing signal processing operations on the target photoacoustic signal to obtain an optimized photoacoustic signal, including amplification processing; and a target localization analysis module for constructing a first three-dimensional photoacoustic image and a second three-dimensional photoacoustic image based on the optimized photoacoustic signals before and after ultrasound modulation, respectively, and performing differential calculations to obtain a target localization image. This application solves the technical problems of existing technologies being unable to determine target depth information and having low resolution target localization images, resulting in poor practical application effects.

Description

Technical Field

[0001] This application relates to the field of photoacoustic imaging technology, and in particular to a visual ultrasound brain modulation target localization device and method. Background Technology

[0002] Photoacoustic imaging is a rapidly developing non-invasive imaging technology in recent years. Based on the photoacoustic effect, it provides a non-invasive, high-resolution imaging method for obtaining two-dimensional tomographic or three-dimensional images of tissues. The photoacoustic effect refers to the phenomenon where biological tissue absorbs the pulse energy and rapidly expands to generate photoacoustic signals when irradiated with a short-pulse laser.

[0003] Alzheimer's disease, epilepsy, Parkinson's disease, and depression are long-term, difficult-to-cure brain disorders that threaten patients' health. Ultrasound-based neuromodulation technology has proven to be an effective tool for conducting neuroscience research and exploring treatment methods for brain disorders. However, using ultrasound for non-invasive neuromodulation often faces the challenge of determining the correct location of the ultrasound focal point.

[0004] Currently, fluorescence imaging, infrared imaging, and MRI are commonly used in medicine to visualize ultrasound-guided brain modulation target areas. However, each of these methods has its own limitations. Fluorescence and infrared imaging can only determine two-dimensional information of the target area, but cannot determine the depth information. MRI suffers from poor target area localization image resolution and is expensive, hindering its widespread adoption. Summary of the Invention

[0005] This application provides a visual ultrasound brain modulation target area localization device and method to solve the technical problem that the existing technology cannot determine the target area depth information and the target area localization image resolution is not high, resulting in poor practical application effect.

[0006] In view of this, the first aspect of this application provides a visual ultrasound brain modulation target localization device, comprising:

[0007] The system includes a sonic brain modulation module, a photoacoustic signal excitation module, a photoacoustic signal processing module, and a target area localization and analysis module.

[0008] The ultrasound brain modulation module is used to generate focused ultrasound waves and transmit the focused ultrasound waves to the target biological sample to achieve ultrasound modulation.

[0009] The photoacoustic signal excitation module includes a pulsed laser and a scanning mechanism, which is used to focus the pulsed laser generated by the pulsed laser onto the target biological sample through the scanning mechanism to generate a target photoacoustic signal;

[0010] The photoacoustic signal processing module is used to perform signal processing operations on the target photoacoustic signal to obtain an optimized photoacoustic signal, and the signal processing operations include amplification processing;

[0011] The target area localization analysis module is used to construct a first three-dimensional photoacoustic image and a second three-dimensional photoacoustic image based on the optimized photoacoustic signals before and after the ultrasound modulation, and to perform differential calculations to obtain the target area localization image.

[0012] Preferably, the ultrasound brain modulation module includes an ultrasound transducer, an acoustic holographic lens, and a transparent acoustic reflector;

[0013] The ultrasonic transducer, the acoustic holographic lens, and the transparent acoustic reflector are arranged coaxially, with the transparent acoustic reflector located between the scanning mechanism and the transparent ultrasonic transducer.

[0014] Preferably, the photoacoustic signal excitation module further includes a collimating lens group and a focusing lens, and the scanning mechanism is a two-dimensional scanning mechanism;

[0015] The pulsed laser, the collimating lens group, the focusing lens, and the two-dimensional scanning mechanism are arranged sequentially on the same axis.

[0016] Preferably, the photoacoustic signal processing module includes a transparent ultrasonic transducer, a water tank, a signal amplifier, and a high-speed data acquisition card;

[0017] The transparent ultrasonic transducer is used to convert the target photoacoustic signal into a target electrical signal;

[0018] The signal amplifier is used to amplify the target electrical signal;

[0019] The high-speed data acquisition card is used to convert the amplified target electrical signal into a digital signal to obtain an optimized photoacoustic signal.

[0020] Preferably, the transparent ultrasonic transducer is immersed in the water tank and located directly below the two-dimensional scanning mechanism;

[0021] The transparent ultrasonic transducer, the signal amplifier, and the high-speed data acquisition card are electrically connected in sequence.

[0022] Preferably, the bottom of the water tank has an imaging port for filling with deionized water as a coupling liquid;

[0023] The imaging port is sealed by a single layer of transparent film.

[0024] Preferably, it further includes: a synchronization control module;

[0025] The synchronization control module includes an analog voltage output card, which is electrically connected to the pulsed laser, the scanning mechanism, and the high-speed data acquisition card to achieve timing synchronization.

[0026] The second aspect of this application provides a method for visualizing ultrasound brain modulation target localization, including:

[0027] The pulsed laser generated by the pulsed laser is projected onto the target biological sample, and the first target photoacoustic signal generated by the target biological sample is collected at the same time.

[0028] After processing the photoacoustic signal of the first target, a first three-dimensional photoacoustic image is constructed.

[0029] The ultrasonic transducer generates ultrasonic waves that are emitted to the target biological sample, thereby raising the temperature of the target area of ​​the target biological sample.

[0030] The second target photoacoustic signal generated after the target sample is heated is collected, and a second three-dimensional photoacoustic image is constructed based on the second target photoacoustic signal;

[0031] The target area localization image is obtained by performing difference calculation between the first three-dimensional photoacoustic image and the second three-dimensional photoacoustic image.

[0032] Preferably, the step of constructing a first three-dimensional photoacoustic image after signal processing of the first target photoacoustic signal includes:

[0033] The first target photoacoustic signal is sequentially subjected to signal conversion and amplification processing to obtain an optimized photoacoustic signal;

[0034] A first three-dimensional photoacoustic image is constructed based on the optimized photoacoustic signal.

[0035] Preferably, the step of projecting the pulsed laser generated by the pulsed laser onto the target biological sample and simultaneously acquiring the first target photoacoustic signal generated by the target biological sample further includes:

[0036] The pulsed laser generated by the pulsed laser is optically shaped to obtain a collimated and focused beam.

[0037] As can be seen from the above technical solutions, the embodiments of this application have the following advantages:

[0038] This application provides a visual ultrasound-guided brain modulation target localization device, comprising: an ultrasound-guided brain modulation module, a photoacoustic signal excitation module, a photoacoustic signal processing module, and a target localization analysis module; the ultrasound-guided brain modulation module generates focused ultrasound waves and emits them to a target biological sample to achieve ultrasound modulation; the photoacoustic signal excitation module includes a pulsed laser and a scanning mechanism, used to focus the pulsed laser generated by the pulsed laser onto the target biological sample through the scanning mechanism to generate a target photoacoustic signal; the photoacoustic signal processing module performs signal processing operations on the target photoacoustic signal to obtain an optimized photoacoustic signal, including amplification processing; the target localization analysis module constructs a first three-dimensional photoacoustic image and a second three-dimensional photoacoustic image based on the optimized photoacoustic signals before and after ultrasound modulation, respectively, and performs differential calculations to obtain a target localization image.

[0039] The visualization device for ultrasound-guided brain modulation target localization provided in this application, based on the Grinesen relaxation effect, determines the location information of the ultrasound focus by increasing the temperature of the target area, thereby enhancing the photoacoustic signal. This allows for visualization of the ultrasound-guided brain modulation target area. Furthermore, two optimized photoacoustic signals acquired before and after ultrasound modulation can be used to construct two three-dimensional photoacoustic images. The target localization image determined using a differential calculation method has the advantages of high resolution and high contrast in photoacoustic imaging, and it includes three-dimensional information about the location of the ultrasound focus. Therefore, this application solves the technical problems of existing technologies that cannot determine target depth information and have low resolution target localization images, resulting in poor practical application effects. Attached Figure Description

[0040] Figure 1 A schematic diagram of the structure of a visual ultrasound brain modulation target localization device provided in this application embodiment;

[0041] Figure 2 A flowchart illustrating a method for visualizing ultrasound brain modulation target localization provided in this application embodiment.

[0042] Figure 3 A schematic diagram of the normalized amplitude curves of photoacoustic signals at different temperatures provided in the embodiments of this application;

[0043] Figure label:

[0044] 1. Pulsed laser; 2. Collimating lens group; 3. Focusing lens; 4. Two-dimensional scanning mechanism; 5. Ultrasonic transducer; 6. Acoustic holographic lens; 7. Transparent acoustic reflector; 8. Transparent ultrasonic transducer; 9. Water tank; 10. Signal amplifier; 11. High-speed data acquisition card; 12. Analog voltage output card; 13. Computer. Detailed Implementation

[0045] To enable those skilled in the art to better understand the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present application, and not all embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the scope of protection of the present application.

[0046] For easier understanding, please refer to Figure 1 An embodiment of a visual ultrasound brain modulation target localization device provided in this application includes: an ultrasound brain modulation module, a photoacoustic signal excitation module, a photoacoustic signal processing module, and a target localization analysis module.

[0047] The ultrasound brain modulation module is used to generate focused ultrasound waves and emit them to the target biological sample to achieve ultrasound modulation.

[0048] Furthermore, the ultrasound brain modulation module includes an ultrasound transducer 5, an acoustic holographic lens 6, and a transparent acoustic reflector 7; the ultrasound transducer 5, the acoustic holographic lens 6, and the transparent acoustic reflector 7 are arranged coaxially, and the transparent acoustic reflector 7 is located between the scanning mechanism and the transparent ultrasound transducer 8.

[0049] The amplitude of the photoacoustic signal is proportional to the absorbed light energy density, and its coefficient is called the Grüneisen parameter, denoted by Γ. Γ depends on the coefficient of volume expansion and the speed of sound, both of which are temperature-dependent and quasi-linearly proportional to the pre-pulse temperature. Therefore, within the physiological temperature range, the Grüneisen parameter has a linear relationship with the pre-pulse temperature (T). When external factors cause a local transient temperature increase, the local Grüneisen parameter increases during the thermally confined time (i.e., the time before the local heat dissipates), which is called the Grüneisen relaxation effect. This embodiment utilizes this effect to design an ultrasound brain modulation module to irradiate the target biological sample with ultrasound, changing its local temperature, thereby enhancing the target photoacoustic signal generated in the target area of ​​the target biological sample and achieving precise localization.

[0050] It should be noted that the acoustic holographic lens 6 can focus the ultrasound emitted by the ultrasonic transducer 5 onto the desired position on the sample, achieving single-probe control. The focused ultrasound is also reflected by the transparent acoustic reflector 7. Furthermore, the focused ultrasound position can be adjusted by replacing the acoustic holographic lens 6. Understandably, if the positioning image shows a deviation in the focused ultrasound position, it can be adjusted by replacing the acoustic holographic lens 6.

[0051] The photoacoustic signal excitation module includes a pulsed laser 1 and a scanning mechanism, which is used to focus the pulsed laser generated by the pulsed laser 1 onto the target biological sample through the scanning mechanism to generate a target photoacoustic signal.

[0052] Furthermore, the photoacoustic signal excitation module also includes a collimating lens group 2 and a focusing lens 3, and the scanning mechanism is a two-dimensional scanning mechanism 4;

[0053] The pulsed laser 1, collimating lens group 2, focusing lens 3, and two-dimensional scanning mechanism 4 are arranged sequentially on the same axis.

[0054] Specifically, the pulsed laser 1 emits a pulsed laser beam, which is collimated by the collimating lens group 2 to obtain a parallel beam. The parallel beam is then converged by the focusing lens 3 and enters the light inlet of the two-dimensional scanning mechanism 4. The two-dimensional scanning mechanism 4 deflects the beam to make the laser focus scan rapidly on the target biological sample. At the same time, the target biological sample absorbs the pulsed laser to generate a photoacoustic signal, namely the target photoacoustic signal.

[0055] The photoacoustic signal processing module is used to perform signal processing operations on the target photoacoustic signal to obtain an optimized photoacoustic signal. The signal processing operations include amplification.

[0056] Furthermore, the photoacoustic signal processing module includes a transparent ultrasonic transducer 8, a water tank 9, a signal amplifier 10, and a high-speed data acquisition card 11;

[0057] Transparent ultrasonic transducer 8 is used to convert the target photoacoustic signal into the target electrical signal;

[0058] Signal amplifier 10 is used to amplify the target electrical signal;

[0059] The high-speed data acquisition card 11 is used to convert the amplified target electrical signal into a digital signal to obtain an optimized photoacoustic signal.

[0060] Furthermore, the transparent ultrasonic transducer 8 is immersed in the water tank 9 and is located directly below the two-dimensional scanning mechanism 4;

[0061] Furthermore, an imaging port is provided at the bottom of the water tank 9, which is filled with deionized water as a coupling liquid;

[0062] The imaging port is sealed with a single layer of transparent film.

[0063] The transparent ultrasonic transducer 8, the signal amplifier 10, and the high-speed data acquisition card 11 are electrically connected in sequence.

[0064] The photoacoustic signal processing module is mainly used to convert and amplify the acquired signals. If there are further signal processing requirements, relevant processing devices can be added. This implementation is not limited to one or two signal processing methods.

[0065] Understandably, the photoacoustic signal generated by the target biological sample attached to the transparent film passes through the coupling liquid in the water tank 9 to the transparent ultrasonic transducer 8 for the first signal conversion. It is then amplified by the signal amplifier 10, followed by a second signal conversion to obtain the optimized photoacoustic signal. The high-speed data acquisition card 11 acquires this optimized photoacoustic signal. Similarly, the installation positions of these devices can correspond one-to-one with the photoacoustic signal processing sequence; any reasonable installation is acceptable, and specific details will not be elaborated here.

[0066] The target area localization analysis module is used to construct a first three-dimensional photoacoustic image and a second three-dimensional photoacoustic image based on the optimized photoacoustic signals before and after ultrasound modulation, and to perform differential calculations to obtain the target area localization image.

[0067] The optimized photoacoustic signals before and after ultrasound modulation refer to the optimized photoacoustic signals obtained before and after irradiation of the target biological sample using the ultrasound brain modulation module. The former is simply the signal generated after pulsed laser irradiation, while the latter is the signal generated after pulsed laser irradiation due to increased temperature. In other words, the two signals are acquired under different temperature conditions before and after brain modulation. Because the target area temperature increases after brain modulation, the absorption Grindelwald coefficient increases, resulting in enhanced photoacoustic signals in the target area upon subsequent signal acquisition. Differential calculations can then be performed to determine the three-dimensional localization image of the target area, i.e., the target area localization image. Since the target area localization image possesses three-dimensional depth information, it is more accurate and reliable than existing technologies, and photoacoustic imaging has the advantages of high resolution and high contrast.

[0068] Furthermore, it also includes: a synchronization control module;

[0069] The synchronization control module includes an analog voltage output card 12, which is electrically connected to the pulsed laser 1, the scanning mechanism and the high-speed data acquisition card 11 to achieve timing synchronization.

[0070] The analog voltage output card 12 is electrically connected to the pulsed laser 1, the scanning mechanism and the high-speed data acquisition card 11, respectively, and is used to control the timing synchronization of these devices.

[0071] Please see Figure 1 The device for visualizing ultrasound brain modulation target localization in this embodiment includes a pulsed laser 1, a collimating lens group 2, a focusing lens 3, and a two-dimensional scanning mechanism 4; an ultrasound transducer 5, an acoustic holographic lens 6, and a transparent acoustic reflector 7 in the ultrasound brain modulation module; a transparent ultrasound transducer 8, a water tank 9, a signal amplifier 10, and a high-speed data acquisition card 11 in the photoacoustic signal processing module; an analog voltage output card 12 in the synchronous control module; and a computer 13 for target localization analysis.

[0072] Specifically, the pulsed laser 1, collimating lens group 2, focusing lens 3, and the light inlet of the two-dimensional scanning mechanism 4 are all arranged coaxially. The pulsed laser 1 emits a laser beam, which is collimated by the collimating lens group 2 to obtain a parallel beam. The beam is focused by the focusing lens 3 and enters the light inlet of the two-dimensional scanning mechanism 4. The light outlet of the two-dimensional scanning mechanism 4, the transparent acoustic reflector 7, and the transparent ultrasonic transducer 8 are arranged coaxially. The transparent ultrasonic transducer 8 is directly below the two-dimensional scanning mechanism 4, and the transparent acoustic reflector 7 is between the two. The beam comes out from the light outlet of the two-dimensional scanning mechanism 4, passes through the transparent acoustic reflector 7 and the transparent ultrasonic transducer 8, and then focuses on the target biological sample under the water tank 8 to generate a photoacoustic signal.

[0073] The transparent ultrasonic transducer 8, signal amplifier 10, high-speed data acquisition card 11, and computer 13 are electrically connected in sequence. The transparent ultrasonic transducer 8 is immersed in the water tank 9. The photoacoustic signal passes through the thin film at the bottom of the water tank 9, is transmitted through deionized water, and is received by the transparent ultrasonic transducer 8. The signal passes through the signal amplifier 10 and the high-speed data acquisition card 11 in sequence, is stored in the computer 13, and is reconstructed. The analog voltage output card 12 is electrically connected to the pulsed laser 1, the two-dimensional scanning mechanism 4, and the high-speed data acquisition card 11, respectively. The analog voltage output card 11 also needs to be electrically connected to the computer 13. The computer 13 controls the voltage output of the analog voltage card 12 to complete the timing synchronization of laser light output, scanning mechanism scanning, and data acquisition.

[0074] The ultrasonic transducer 5, the acoustic holographic lens 6, and the transparent acoustic reflector 7 at a 45° angle are arranged coaxially. The ultrasonic transducer 5 emits ultrasonic waves, which are focused by the acoustic holographic lens 6 and then reflected by the transparent acoustic reflector 7 to the sample target area for control. After the control is completed, the system performs another photoacoustic imaging before the heat dissipates. The computer 13 saves the data and performs a difference with the previous imaging data to obtain a three-dimensional positioning image of the target area. If there is a deviation in the position of the controlled target area, the acoustic holographic lens 6 can be replaced to adjust the position of the target area.

[0075] It should be noted that in this embodiment, the pulsed laser 1 has a wavelength of 532nm, a maximum repetition frequency of 100kHz, and a laser pulse width of less than 10ns; the focusing lens 3 is 30mm × 9.7mm in size and has a focal length of 100mm; the two-dimensional scanning mechanism 4 uses a two-dimensional scanning galvanometer, allowing a maximum beam diameter of 10mm, accepting differential analog voltage input from -10V to +10V, and a maximum optical scanning angle of ±20°; the transparent acoustic reflector 7 has a light transmittance of 98%. The transparent ultrasonic transducer 8 uses LiNbO3 as the piezoelectric single crystal material, with a window size of 20 × 20mm. 2 It has a transmittance of over 72% for 532nm wavelength light and a center frequency of 10MHz; the bottom of the water tank 9 has an imaging port, which is filled with deionized water as the coupling liquid, and the imaging port is sealed with a transparent film; the signal amplifier 10 has an amplification gain of 54dB.

[0076] The visualization device for ultrasound-guided brain modulation target localization provided in this application, based on the Grinesen relaxation effect, determines the location information of the ultrasound focus by increasing the temperature of the target area, thereby enhancing the photoacoustic signal. This allows for visualization of the ultrasound-guided brain modulation target area. Furthermore, two optimized photoacoustic signals acquired before and after ultrasound modulation can be used to construct two three-dimensional photoacoustic images. The target localization image determined using a differential calculation method has the advantages of high resolution and high contrast in photoacoustic imaging, and it includes three-dimensional information about the location of the ultrasound focus. Therefore, this application solves the technical problems of existing technologies that cannot determine target depth information and have low resolution target localization images, resulting in poor practical application effects.

[0077] For easier understanding, please refer to Figure 2 This application also provides an embodiment of a method for visualizing ultrasound brain modulation target localization, including:

[0078] Step 201: Project the pulsed laser generated by the pulsed laser onto the target biological sample, and simultaneously collect the first target photoacoustic signal generated by the target sample.

[0079] Step 202: After processing the photoacoustic signal of the first target, construct the first three-dimensional photoacoustic image;

[0080] Step 203: The ultrasonic waves generated by the ultrasonic transducer are emitted to the target biological sample, causing the temperature of the target area of ​​the target biological sample to rise.

[0081] Step 204: Collect the second target photoacoustic signal generated after the target sample is heated, and construct a second three-dimensional photoacoustic image based on the second target photoacoustic signal;

[0082] Step 205: Perform differential calculation between the first three-dimensional photoacoustic image and the second three-dimensional photoacoustic image to obtain the target area localization image.

[0083] It should be noted that some necessary preliminary preparations need to be completed before sample testing. For example, the biological sample, after being anesthetized and with its head treated by hair removal and skin removal, is placed on the imaging stage. After applying coupling agent to the head, it is placed tightly against the membrane at the imaging port of the water tank. The water tank is filled with deionized water to couple the photoacoustic signals. Other necessary operations can be added as needed, and are not limited here. Once brain modulation is initiated, the operation can be completed according to the method described in this embodiment.

[0084] Based on the visualization ultrasound brain modulation target area localization device mentioned in the above embodiment, localization analysis is performed. The pulsed laser emits pulsed laser light, which passes through the collimating lens group, focusing lens, two-dimensional scanning mechanism, transparent acoustic reflector, and transparent ultrasonic transducer in sequence before irradiating the sample to generate a target photoacoustic signal. The target photoacoustic signal passes through the thin film at the bottom of the water tank in the form of a mechanical wave and enters the water tank. It is transmitted to the transparent ultrasonic transducer by deionized water to generate an electrical signal, namely the first target photoacoustic signal. The high-speed data acquisition card then acquires and transmits the first target photoacoustic signal to the computer for image reconstruction to obtain the first three-dimensional photoacoustic image.

[0085] The ultrasound transducer in the ultrasound brain modulation module emits ultrasound waves, which are focused by an acoustic holographic lens and reflected by an acoustic mirror onto the target biological sample's target area. As the target area is modulated, its temperature continuously rises, allowing the acquisition of a second target photoacoustic signal and the construction of a second three-dimensional photoacoustic image. Understandably, the second target photoacoustic signal also requires the same signal processing as the first target photoacoustic signal, which will not be elaborated here. Furthermore, the acquisition of the second target photoacoustic signal must be completed before the target area's heat dissipates; only then is the signal valid.

[0086] The temperature rise causes the amplitude of the photoacoustic signal in the target area of ​​the second three-dimensional photoacoustic image to increase. Therefore, by performing differential calculations using the first three-dimensional photoacoustic image and the second three-dimensional photoacoustic image, the positioning information of the control target area can be determined, i.e., the target area positioning image.

[0087] Further, step 202 includes:

[0088] The photoacoustic signal of the first target is sequentially processed by signal conversion and amplification to obtain an optimized photoacoustic signal;

[0089] The first three-dimensional photoacoustic image is constructed based on the optimized photoacoustic signal.

[0090] It should be noted that the signal conversion process in this embodiment includes two steps: first, the target photoacoustic signal is converted into an electrical signal; second, the electrical signal is converted into a digital signal. Amplification is performed between the two signal conversions. Other operations on the signal can also be performed if necessary, as long as a reliable signal for image reconstruction can be obtained.

[0091] Furthermore, step 201 also includes:

[0092] Optical path shaping is performed on the pulsed laser generated by the pulsed laser to obtain a collimated and focused beam.

[0093] Collimation and focusing of the beam can be achieved through specific functional circuits. In this embodiment, a collimating lens group and a focusing lens are used. The specific method is not limited here and can be designed according to the actual situation.

[0094] It should be noted that the visualization ultrasound brain modulation target localization device mentioned in the above embodiment also has another imaging method, which requires the injection of a biocompatible contrast agent into the biological sample donor; the photoacoustic signal amplitude at different temperatures is normalized to obtain... Figure 3 The image shown is from Figure 3 As can be seen, after injecting the contrast agent, the photoacoustic signal amplitude becomes more sensitive to temperature changes, with a larger amplitude change per degree Celsius increase in temperature. Therefore, after sample conditioning, injecting the contrast agent results in a greater increase in the photoacoustic signal amplitude of the target area compared to not injecting it. This leads to a better signal-to-noise ratio in the target area localization image. For imaging samples that do not reject the contrast agent, injecting the contrast agent can bring better imaging results. For the specific imaging process, please refer to the device imaging operation process described above; it will not be repeated here.

[0095] In the several embodiments provided in this application, it should be understood that the disclosed apparatus and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative; for instance, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be through some interfaces; the indirect coupling or communication connection between apparatuses or units may be electrical, mechanical, or other forms.

[0096] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0097] Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0098] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions for executing all or part of the steps of the methods described in the various embodiments of this application through a computer device (which may be a personal computer, server, or network device, etc.). The aforementioned storage medium includes: USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, optical disks, and other media capable of storing program code.

[0099] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application.

Claims

1. A visual ultrasound brain modulation target localization device, characterized in that, include: The system includes a sonic brain modulation module, a photoacoustic signal excitation module, a photoacoustic signal processing module, and a target area localization and analysis module. The ultrasound brain modulation module is used to generate focused ultrasound waves and emit the focused ultrasound waves to the target biological sample to achieve ultrasound modulation. The ultrasound brain modulation module includes an ultrasound transducer, an acoustic holographic lens and a transparent acoustic reflector. The ultrasonic transducer, the acoustic holographic lens, and the transparent acoustic reflector are arranged coaxially; The photoacoustic signal excitation module includes a pulsed laser and a scanning mechanism, which is used to focus the pulsed laser generated by the pulsed laser onto the target biological sample through the scanning mechanism to generate a target photoacoustic signal. The photoacoustic signal excitation module also includes a collimating lens group and a focusing lens. The scanning mechanism is a two-dimensional scanning mechanism. The pulsed laser, the collimating lens group, the focusing lens, and the two-dimensional scanning mechanism are arranged sequentially on the same axis; The photoacoustic signal processing module is used to perform signal processing operations on the target photoacoustic signal to obtain an optimized photoacoustic signal. The signal processing operations include amplification processing. The photoacoustic signal processing module includes a transparent ultrasonic transducer, a water tank, a signal amplifier, and a high-speed data acquisition card. The transparent ultrasonic transducer is used to convert the target photoacoustic signal into a target electrical signal; The signal amplifier is used to amplify the target electrical signal; The high-speed data acquisition card is used to convert the amplified target electrical signal into a digital signal to obtain an optimized photoacoustic signal. The transparent ultrasonic transducer is immersed in the water tank and located directly below the two-dimensional scanning mechanism; The transparent acoustic reflector is located between the two-dimensional scanning mechanism and the transparent ultrasonic transducer; The transparent ultrasonic transducer, the signal amplifier, and the high-speed data acquisition card are electrically connected in sequence. The target area localization analysis module is used to construct a first three-dimensional photoacoustic image and a second three-dimensional photoacoustic image based on the optimized photoacoustic signals before and after ultrasonic modulation, respectively, and perform differential calculations to obtain the target area localization image.

2. The visual ultrasound brain modulation target localization device according to claim 1, characterized in that, An imaging port is provided at the bottom of the water tank, which is filled with deionized water as a coupling liquid; The imaging port is sealed by a single layer of transparent film.

3. The visualized ultrasound brain modulation target localization device according to claim 1, characterized in that, Also includes: Synchronization control module; The synchronization control module includes an analog voltage output card, which is electrically connected to the pulsed laser, the scanning mechanism, and the high-speed data acquisition card to achieve timing synchronization.

4. A method for visualizing ultrasound brain modulation target localization, used on the device according to any one of claims 1-3, characterized in that, include: The pulsed laser generated by the pulsed laser is projected onto the target biological sample, and the first target photoacoustic signal generated by the target biological sample is collected at the same time. After processing the photoacoustic signal of the first target, a first three-dimensional photoacoustic image is constructed. The ultrasonic transducer generates ultrasonic waves that are emitted to the target biological sample, thereby raising the temperature of the target area of ​​the target biological sample. The second target photoacoustic signal generated after the target sample is heated is collected, and a second three-dimensional photoacoustic image is constructed based on the second target photoacoustic signal; The target area localization image is obtained by performing difference calculation between the first three-dimensional photoacoustic image and the second three-dimensional photoacoustic image.

5. The method for visual ultrasound brain modulation target localization according to claim 4, characterized in that, The step of constructing a first three-dimensional photoacoustic image after processing the first target photoacoustic signal includes: The first target photoacoustic signal is sequentially subjected to signal conversion and amplification processing to obtain an optimized photoacoustic signal; A first three-dimensional photoacoustic image is constructed based on the optimized photoacoustic signal.

6. The method for visual ultrasound brain modulation target localization according to claim 4, characterized in that, The step of projecting pulsed laser light generated by a pulsed laser onto a target biological sample and simultaneously acquiring a first target photoacoustic signal generated by the target biological sample further includes: The pulsed laser generated by the pulsed laser is optically shaped to obtain a collimated and focused beam.

Images