Photoacoustic coupling myopia regulation and control device and regulation and control method

Abstract

The invention discloses a photoacoustic coupling myopia regulation and control device and a regulation and control method. The device comprises a controller, a laser regulation and control module, a pulse transmitter, a multi-channel delay control unit and an ultrasonic transducer, the controller is used for generating laser parameters, pulse parameters and delay parameters according to preset regulation and control requirements; the laser regulation and control module is used for exciting laser spots emitted to the fundus posterior pole part according to the laser parameters; the pulse transmitter is used for generating a pulse signal according to the pulse parameter and transmitting the pulse signal to the multi-channel delay control unit; the multi-channel delay control unit is used for generating multiple paths of delay ultrasonic signals according to the delay parameter and the pulse signal and transmitting the multiple paths of delay ultrasonic signals to the ultrasonic transducer; and the ultrasonic transducer is used for forming a dynamic focusing sound field according to the multiple paths of delay ultrasonic signals, so that the dynamic focusing sound field continuously moves along a preset path to realize full coverage of the retropolar part of the eye ground, thereby realizing synchronous regulation and control of laser and ultrasonic and completing accurate local mechanical stimulation and metabolism regulation and control.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a photoacoustic coupling myopia control device and control method. Background Technology

[0002] Myopia, a globally prevalent refractive error, is primarily characterized by scleral tissue remodeling, manifested as increased transdifferentiation of scleral fibroblasts into myofibroblasts and decreased collagen production, leading to axial elongation. In recent years, non-invasive modulatory technologies (such as low-intensity red light therapy and ultrasound biomechanical modulation) have shown promise in ophthalmology. Low-intensity red light therapy uses low-energy red light of a specific wavelength (typically 650nm) to irradiate the eye, increasing choroidal metabolic rate and blood circulation, enhancing choroidal oxygen supply, and improving scleral hypoxia, thereby inhibiting collagen breakdown and excessive axial elongation caused by scleral hypoxia. Currently, ultrasound modulation stimulates corneal or scleral collagen fibers through mechanical vibration, affecting their structural arrangement and thus altering refractive power. However, the current synergistic ability of laser and ultrasound in achieving precise and coordinated regulation of scleral metabolism and biomechanical state is insufficient, making it difficult to effectively achieve precise local mechanical stimulation and metabolic regulation. Summary of the Invention

[0003] This invention provides a photoacoustic coupling myopia control device and method to solve the technical problem that existing laser and ultrasound technologies are insufficient in their ability to achieve precise and coordinated regulation of scleral metabolism and biomechanical state, making it difficult to effectively coordinate and achieve precise local mechanical stimulation and metabolic regulation.

[0004] This invention provides a photoacoustic coupled myopia control device, comprising: an ultrasonic control module, a controller, and a laser control module;

[0005] The ultrasonic control module includes a pulse transmitter, a multi-channel delay control unit, and an ultrasonic transducer.

[0006] The controller is connected to the laser control module, the pulse transmitter, and the multi-channel delay control unit, respectively, and is used to generate laser parameters, pulse parameters, and delay parameters according to preset control requirements; send the laser parameters to the laser control module, send the pulse parameters to the pulse transmitter, and send the delay parameters to the multi-channel delay control unit;

[0007] The laser control module is used to excite a laser spot directed toward the posterior pole of the fundus according to the laser parameters.

[0008] The pulse transmitter is used to generate a pulse signal according to the pulse parameters and transmit the pulse signal to the multi-channel delay control unit;

[0009] The multi-channel delay control unit is used to generate multiple delayed ultrasonic signals according to the delay parameters and the pulse signal, and transmit the multiple delayed ultrasonic signals to the ultrasonic transducer;

[0010] The ultrasonic transducer is connected to the multi-channel delay control unit and is used to form a dynamic focused sound field based on multiple delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

[0011] Optional features also include: a signal acquisition card and an ultrasonic monitoring module;

[0012] The ultrasonic transducer is also used to receive ultrasonic echo signals reflected from the posterior pole of the fundus.

[0013] The signal acquisition card is electrically connected to the ultrasonic transducer and is used to acquire the ultrasonic echo signal and send the ultrasonic echo signal to the ultrasonic monitoring module.

[0014] The ultrasound monitoring module is used to monitor and analyze the ultrasound echo signal to obtain physiological monitoring parameters.

[0015] Optionally, the controller is electrically connected to the ultrasound monitoring module and is used to determine whether the physiological monitoring parameters exceed a preset monitoring threshold; if they do, the preset control requirements are adjusted.

[0016] Optionally, the ultrasonic transducer has a grid-shaped structure design; the ultrasonic transducer includes a ring array, an x-axis array, and a y-axis array;

[0017] The x-axis array is arranged laterally inside the annular array, and the y-axis array is arranged longitudinally inside the annular array;

[0018] A central through hole is provided between the x-axis array and the y-axis array;

[0019] The ring array is used to emit a low-frequency focused ultrasound beam and receive low-frequency ultrasound echoes reflected from the posterior pole of the fundus; the x-axis array is used to emit a high-frequency focused ultrasound beam and receive high-frequency ultrasound echoes reflected from the posterior pole of the fundus; the y-axis array is used to emit a mid-frequency focused ultrasound beam and receive mid-frequency ultrasound echoes reflected from the posterior pole of the fundus.

[0020] Optionally, the laser control module includes a laser, a beam expander, and a homogenizer;

[0021] The laser is used to excite a laser beam and direct the laser beam toward the beam expander;

[0022] The laser beam is expanded by the beam expander and homogenized by the homogenizer in sequence to form a laser spot; the laser spot is directed toward the posterior pole of the fundus through the central through-hole.

[0023] Optionally, the ring array is a ring-shaped 256 array, the x-axis array is an x-axis linear 128 array, and the y-axis array is a y-axis linear 64 array.

[0024] Optionally, the ring array is a ring-shaped 256 array, the x-axis array is an x-axis linear 128 array, and the y-axis array is a y-axis linear 128 array;

[0025] Both the x-axis array and the y-axis array are made of transparent piezoelectric material.

[0026] The present invention also provides a photoacoustic coupled posterior pole of the fundus in myopia, wherein the modulation method is implemented based on any of the aforementioned myopia modulation devices, and the modulation method includes:

[0027] Generate laser parameters, pulse parameters, and delay parameters according to preset control requirements;

[0028] The laser control module excites a laser spot directed toward the posterior pole of the fundus according to the laser parameters;

[0029] A pulse signal is generated by a pulse transmitter according to the pulse parameters, and multiple delayed ultrasonic signals are generated by a multi-channel delay control unit according to the pulse signal and the delay parameters.

[0030] An ultrasonic transducer is used to form a dynamic focused sound field based on the multi-channel delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

[0031] Optionally, the control method further includes:

[0032] Ultrasonic echo signals reflected from the posterior pole of the fundus were acquired using an ultrasonic transducer.

[0033] The physiological monitoring parameters are obtained by monitoring and analyzing the ultrasound echo signals; it is determined whether the physiological monitoring parameters have preset monitoring thresholds; if they exceed the thresholds, the preset control requirements are adjusted.

[0034] Optionally, the step of acquiring the physiological monitoring parameters includes:

[0035] Eye imaging is performed using the high-frequency ultrasound echo in the ultrasound echo signal to extract the axial length and the location of the fovea region of the posterior pole of the fundus.

[0036] Based on the high-frequency ultrasound echo in the ultrasound echo signal, the retinal aortic vessel flow velocity is calculated by Doppler spectrum shift;

[0037] Based on the intermediate frequency ultrasound echo in the ultrasound echo signal, the scleral elasticity is calculated using ultrasound elastography.

[0038] Based on the high-frequency ultrasound echo in the ultrasound echo signal, the choroidal vessel flow velocity is calculated by Doppler spectrum shift.

[0039] Scleral backscattering is detected based on the high-frequency ultrasonic echo in the ultrasonic echo signal to obtain scleral backscattering characteristics.

[0040] As can be seen from the above technical solutions, the present invention has the following advantages:

[0041] This invention provides a photoacoustic coupling myopia control device and method, wherein the device includes: an ultrasound control module, a controller, and a laser control module; the ultrasound control module includes a pulse transmitter, a multi-channel delay control unit, and an ultrasound transducer; the controller is connected to the laser control module, the pulse transmitter, and the multi-channel delay control unit respectively, and is used to generate laser parameters, pulse parameters, and delay parameters according to preset control requirements; send the laser parameters to the laser control module, the pulse parameters to the pulse transmitter, and the delay parameters to the multi-channel delay control unit; the laser control module is used to excite a laser spot directed towards the posterior pole of the fundus according to the laser parameters; the pulse transmitter is used to generate a pulse signal according to the pulse parameters and send the pulse signal to the multi-channel delay control unit; the multi-channel delay control unit is used to generate multiple delayed ultrasound signals according to the delay parameters and the pulse signal and send the multiple delayed ultrasound signals to the ultrasound transducer; the ultrasound transducer is connected to the multi-channel delay control unit and is used to form a dynamic focused sound field according to the multiple delayed ultrasound signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

[0042] In this invention, the laser spot can regulate the scleral biomechanical network to inhibit abnormal axial elongation, while the ultrasound control module can focus the ultrasound sound field at different positions in the posterior pole of the fundus to achieve coverage of the key area of ​​the posterior pole. This enables synchronous control of laser and ultrasound, achieving precise local mechanical stimulation and metabolic regulation. This solves the technical problem that existing laser and ultrasound technologies are insufficient in their ability to precisely and synergistically regulate scleral metabolism and biomechanical state, making it difficult to effectively achieve precise local mechanical stimulation and metabolic regulation. Attached Figure Description

[0043] To more clearly illustrate the technical solutions in the embodiments of the present invention 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 the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0044] Figure 1A schematic diagram of a photoacoustic coupling myopia control device provided in this application;

[0045] Figure 2 Schematic diagrams of the two ultrasonic transducers provided in this application;

[0046] Figure 3 This application provides an exploded structural diagram of an ultrasonic transducer.

[0047] Figure 4 A flowchart illustrating the steps of a photoacoustic coupling myopia control method provided in this application;

[0048] The attached figures are labeled as follows:

[0049] Laser 1, beam expander 2, homogenizer 3, ultrasonic transducer 4, pulse emitter 5, multi-channel delay control unit 6, rear electrode 7, signal acquisition card 8, controller 9, ring array 10, x-axis array 11, y-axis array 12, backing layer 13, negative electrode layer 14, wafer layer 15, positive electrode layer 16, and matching layer 17. Detailed Implementation

[0050] This invention provides a photoacoustic coupling myopia control device and method to address the technical problem that existing laser and ultrasound technologies lack the ability to precisely and synergistically regulate scleral metabolism and biomechanical state, making it difficult to effectively coordinate and achieve precise local mechanical stimulation and metabolic regulation.

[0051] To make the objectives, features, and advantages of this invention more apparent and understandable, the technical solutions of the embodiments of this invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the embodiments described below are only some embodiments of this invention, and not all embodiments. Based on the embodiments of this invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this invention.

[0052] In the description of this invention, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing the invention and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the invention. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0053] Unless otherwise explicitly specified and limited, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to fixed connections, detachable connections, or integral connections; they can refer to mechanical connections or electrical connections; they can refer to direct connections or indirect connections through an intermediate medium; and they can refer to the internal connection between two components. Those skilled in the art will understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0054] Please see Figure 1 This application provides an embodiment of a photoacoustic coupled myopia control device, comprising: an ultrasonic control module, a controller 9, and a laser control module;

[0055] The ultrasonic control module includes a pulse transmitter 5, a multi-channel delay control unit 6, and an ultrasonic transducer 4;

[0056] The controller 9 is connected to the laser control module, the pulse transmitter 5 and the multi-channel delay control unit 6 respectively. It is used to generate laser parameters, pulse parameters and delay parameters according to preset control requirements; send the laser parameters to the laser control module, the pulse parameters to the pulse transmitter 5 and the delay parameters to the multi-channel delay control unit 6.

[0057] The laser control module is used to excite a laser spot directed toward the posterior pole of the fundus 7 according to the laser parameters;

[0058] The pulse transmitter 5 is used to generate a pulse signal according to the pulse parameters and transmit the pulse signal to the multi-channel delay control unit 6;

[0059] The multi-channel delay control unit 6 is used to generate multiple delayed ultrasonic signals according to the delay parameters and pulse signals and transmit the multiple delayed ultrasonic signals to the ultrasonic transducer 4;

[0060] The ultrasonic transducer 4 is connected to the multi-channel delay control unit 6, which is used to form a dynamic focused sound field based on the multi-channel delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along the preset path to achieve full coverage of the posterior pole of the fundus 7.

[0061] It is understandable that laser parameters include laser wavelength, laser power density, and focusing size; pulse parameters include center frequency, pulse duty cycle, and pulse frequency; and delay parameters include emission delay and focusing coordinates for different channels.

[0062] In the ultrasonic control module, the pulse duty cycle is set to 20%, the spatial peak time average sound intensity (ISPTA) is 300mW / cm², the ultrasonic transducer 4 transmits signals through the pulse transmitter 5, and the multi-channel delay control unit 6 applies different delays to each array element in the ultrasonic transducer 4 array, so that the focal point moves continuously along the predetermined path, thereby achieving full coverage of the rear pole 7 region.

[0063] In this embodiment, the laser spot excited by the laser modulation module is targeted to the entire posterior pole region 7 of the retina. The laser spot can modulate the scleral biomechanical network to inhibit abnormal axial elongation. The controller 9 controls the pulse transmitter 5 to emit pulse signals, and the multi-channel delay control unit 6 applies different delayed ultrasonic signals to the array of ultrasonic transducers 4, causing the acoustic field focusing point of the ultrasonic transducers 4 to focus on different positions in the posterior pole region 7 of the fundus, thereby achieving synchronous modulation with the laser. This invention, through the synergistic modulation of laser and ultrasound, achieves precise local mechanical stimulation and metabolic regulation without requiring multiple stimulations of the target area.

[0064] In a preferred embodiment, it further includes: a signal acquisition card 8 and an ultrasound monitoring module; the ultrasound transducer 4 is also used to receive ultrasound echo signals reflected from the posterior pole of the fundus 7;

[0065] The signal acquisition card 8 is electrically connected to the ultrasonic transducer 4 and is used to acquire ultrasonic echo signals and send them to the ultrasonic monitoring module. The ultrasonic monitoring module is used to monitor and analyze the ultrasonic echo signals to obtain physiological monitoring parameters.

[0066] It should be noted that the ultrasonic transducer 4 provided in this embodiment has the functions of transmitting and receiving ultrasound. When the ultrasonic sound field is focused on different positions of the posterior pole of the fundus 7, the acoustic impedance of different tissues of the eyeball to the ultrasonic sound wave is different, which causes the sound wave to be reflected (refracted) during propagation, thereby forming an ultrasonic echo. The ultrasonic echo signal reflected from the posterior pole of the fundus 7 is then received by the ultrasonic transducer 4. The ultrasonic echo carries information about the various tissues of the eyeball.

[0067] The ultrasonic transducer 4 receives ultrasonic echo signals and uploads them to the ultrasonic monitoring module via the signal acquisition card 8. The signal acquisition card 8 can preprocess the ultrasonic echo signals, such as filtering and analog-to-digital conversion, and can also buffer ultrasonic echo signals acquired at different times.

[0068] In this preferred embodiment, the ultrasound monitoring module integrates ultrasound Doppler blood flow imaging and ultrasound microscopy functions to acquire key physiological monitoring parameters such as axial length, location of the posterior pole fovea region, scleral elasticity, blood flow velocity in the choroidal microvessels and aorta, and scleral backscattering characteristics. The scleral backscattering characteristics include the equivalent scatterer diameter and acoustic concentration.

[0069] The ultrasound monitoring module described above obtains physiological monitoring parameters in the following ways:

[0070] 1) Using four ultrasonic transducers to image the eye, extract the axial length and the location of the fovea region in the posterior pole of the macula;

[0071] 2) Calculate scleral elasticity using ultrasonic elastography;

[0072] 3) Calculate choroidal vessel flow velocity and retinal aortic vessel flow velocity by Doppler spectrum shift;

[0073] 4) Calculate the scleral backscattering coefficient, calculate the frequency-dependent backscattering coefficient spectrum of the scleral tissue, and fit the BSC-f curve based on the Gaussian scattering model to indirectly derive the tissue microstructure parameters, namely the equivalent scatterer diameter and acoustic concentration.

[0074] In addition, once medical staff obtain physiological monitoring parameters, they can comprehensively assess the user's degree of myopia based on physiological monitoring parameters such as axial length, position of the fovea region in the posterior pole, scleral elasticity, blood flow velocity of choroidal microvessels and aorta, and scleral backscattering characteristics.

[0075] In a preferred embodiment, the controller 9 is electrically connected to the ultrasound monitoring module to determine whether the physiological monitoring parameters exceed the preset monitoring threshold; if they do, the preset control requirements are adjusted.

[0076] It should be noted that, in order to protect the user's eye health, during the control process, the controller 9 dynamically adjusts the ultrasound energy based on the physiological monitoring parameters monitored in real time by the ultrasound monitoring module. When the physiological monitoring parameters exceed the preset monitoring threshold, the ultrasound power, duration of action, or focusing path are dynamically adjusted to achieve timely intervention and safe control.

[0077] For example, blood flow velocity monitoring thresholds are established for choroidal microvessels (diameter 50–200 μm) and central retinal artery (diameter 160–200 μm); changes in blood flow velocity are monitored in real time during the control process, and when the detection result changes by more than 20% compared with the blood flow velocity monitoring threshold, the controller 9 automatically adjusts the ultrasound output energy (adjustment range is ±10%~20%).

[0078] In a preferred embodiment, the ultrasonic transducer 4 is designed in a grid pattern; the ultrasonic transducer 4 includes a ring array 10, an x-axis array 11 and a y-axis array 12;

[0079] The x-axis array 11 is arranged laterally inside the annular array 10, and the y-axis array 12 is arranged longitudinally inside the annular array 10; a central through hole is provided between the x-axis array 11 and the y-axis array 12;

[0080] The ring array 10 is used to transmit a low-frequency focused ultrasound beam and receive the low-frequency ultrasound echo reflected from the posterior pole of the fundus 7; the x-axis array 11 is used to transmit a high-frequency focused ultrasound beam and receive the high-frequency ultrasound echo reflected from the posterior pole of the fundus 7; the y-axis array 12 is used to transmit a medium-frequency focused ultrasound beam and receive the medium-frequency ultrasound echo reflected from the posterior pole of the fundus 7.

[0081] In the actual design, the ultrasonic transducer 4 adopts a grid-shaped structure layout with a central circular through hole (2mm in diameter). The laser spot can reach the posterior pole of the fundus 7 without obstruction through the central through hole, while the ultrasonic spiral scanning can fully cover the target area.

[0082] Combined with the monitoring and analysis of the ultrasound monitoring module, the ring array 10 mainly performs the control function of low-frequency ultrasound; the x-array 11 is used for high-frequency ultrasound biological tissue microscopic imaging, thereby realizing the monitoring of axial length, the position of the posterior pole fovea region and the retinal aortic blood vessel velocity; the y-array 12 realizes the imaging of the eyeball based on mid-frequency ultrasound, thereby realizing the detection of choroidal blood vessel velocity, scleral elasticity and scleral backscattering characteristics.

[0083] In a preferred embodiment, the laser control module includes a laser 1, a beam expander 2, and a homogenizer 3;

[0084] Laser 1 is used to excite a laser beam and direct the laser beam toward beam expander 2; the laser beam is expanded by beam expander 2 and homogenized by homogenizer 3 in sequence to form a laser spot; the laser spot is directed toward the posterior pole of the fundus 7 through the central through hole.

[0085] In this preferred embodiment, the laser beam is specifically low-intensity red light (wavelength 650nm, laser power density 0.7mW / cm²). The laser 1, beam expander 2, and homogenizer 3 are sequentially arranged behind the ultrasonic transducer 4. After passing through the beam expander (3mm in diameter) and homogenizer 3, the laser beam forms a 4mm spot. Then, the laser spot is perpendicularly incident on the posterior pole of the fundus 7 through the central through-hole of the ultrasonic transducer 4 and uniformly covers the posterior pole of the fundus 7.

[0086] Furthermore, considering that in existing non-invasive modulation techniques (such as low-intensity red light therapy and ultrasound biomechanical modulation), low-intensity red light therapy, by irradiating the eye with low-energy red light of a specific wavelength (usually 650nm), can increase the metabolic rate and blood circulation of the choroid, enhance the oxygen supply capacity of the choroid, and improve the hypoxic state of the sclera, thereby inhibiting collagen decomposition and excessive axial elongation of the sclera caused by hypoxia. However, due to the high absorption of light waves by the retinal pigment epithelium, the depth of action is limited, and the existing light spot coverage is small and the energy distribution is uneven, making it difficult to accurately regulate the activity of deep scleral fibroblasts. Therefore, this invention provides two types of ultrasound transducers 4 that can transmit wide-area light. Both types of ultrasound transducers 4 are used to perform functions such as monitoring choroidal blood flow velocity and scleral backscattering coefficient in the monitoring module, and the only difference between them is their structure.

[0087] In a preferred embodiment, the ring array 10 is a ring-shaped 256 array, the x-axis array 11 is an x-axis linear 128 array, and the y-axis array 12 is a y-axis linear 64 array.

[0088] It should be noted that the ultrasonic transducer 4 is typically composed of a backing layer 13, a negative electrode layer 14, a wafer layer 15, a positive electrode layer 16, and a matching layer 17; please refer to [link to relevant documentation]. Figure 2 (a) and Figure 3 In the ultrasonic transducer 4 with the first structure provided in this preferred embodiment, the structure is improved by changing the probe backing layer 13, the positive electrode and the matching layer 17, and the y-direction linear array to 64 elements for processing a large area of ​​light transmission.

[0089] In the actual design, the ring array 10 has a center frequency of 8MHz, 192 elements, a ring length of 5mm, and an overall diameter of 15mm, and is used for ultrasound modulation. The x-array 11 has a center frequency of 20MHz, 128 elements, an overall length of 12mm, and a width of 3mm, and is used to measure axial length, the position of the posterior pole 7 fovea region, and retinal aortic vessel flow velocity. The y-array 12 has a center frequency of 40MHz, 64 elements, an overall length of 6mm, and a width of 3mm, and is used to detect choroidal vessel flow velocity, scleral elasticity, and scleral backscattering characteristics.

[0090] In a preferred embodiment, the ring array 10 is a ring-shaped 256 array, the x-axis array 11 is an x-axis linear 128 array, and the y-axis array 12 is a y-axis linear 128 array; both the x-axis array 11 and the y-axis array 12 are made of transparent piezoelectric material.

[0091] Please see Figure 2In (b) of the preferred embodiment, the ultrasonic transducer 4 with the second structure is made of transparent piezoelectric material (such as lithium niobate single crystal, PIN-PMN-PT, etc.) for both the x-axis array 11 and the y-axis array 12, so that the entire internal area of ​​the ultrasonic transducer 4 can be transparent, thereby achieving maximum area light transmission under the limitations of the transducer structure.

[0092] In the actual design, the ring array 10 has a center frequency of 8MHz, 192 elements, a ring length of 5mm, and an overall diameter of 15mm, and is used for ultrasound modulation. The x-array 11 has a center frequency of 20MHz, 128 elements, an overall length of 12mm, and a width of 3mm, and is used to measure axial length, the position of the posterior pole fovea region, and retinal aortic flow velocity. The y-array 12 has a center frequency of 40MHz, 128 elements, an overall length of 12mm, and a width of 3mm, and is used to detect choroidal vessel flow velocity, scleral elasticity, and scleral backscattering characteristics.

[0093] This invention provides a photoacoustic coupled myopia control device that integrates optical control, acoustic biological effects, and intelligent monitoring functions. It is particularly suitable for myopic users aged 12-17 to slow vision decline and provides early warning for those with myopia trends. This device has the following advantages:

[0094] 1. Photo-acoustic dual-modal synergy: Combining low-intensity red light (targeting scleral biomechanical regulation) with ultrasound (mechanical effect enhances phototherapy penetration) to cover key areas of the posterior pole, ensuring the effectiveness of regulation and achieving precise local mechanical stimulation and metabolic regulation.

[0095] 2. Dynamic monitoring and real-time assessment: Integrating ultrasound Doppler flow imaging (DFI) and high-frequency UBM functions, it simultaneously acquires multi-dimensional physiological monitoring parameters such as axial length, choroidal blood vessel velocity, scleral elasticity, and scleral scattering coefficient, quantitatively assesses the intervention effect, and dynamically adjusts the treatment plan.

[0096] 3. Wide-area light modulation: By designing the structure of the ultrasonic transducer, two types of ultrasonic transducers that can transmit wide-area light are provided, so that the laser spot can directly cover the entire macular area without modulation, avoiding the risk of fundus inflammation caused by repeated stimulation.

[0097] Please see Figure 4 This application also provides a photoacoustic coupled posterior pole of the myopic fundus, wherein the modulation method is implemented based on any myopia modulation device, and the modulation method includes:

[0098] Step 101: Generate laser parameters, pulse parameters, and delay parameters according to preset control requirements.

[0099] It should be noted that, based on user needs, preset control requirements can be divided into myopia measurement and assessment requirements and myopia treatment coordination requirements, etc. Among them, laser parameters include laser wavelength, laser power density and focal size, etc.; pulse parameters include center frequency, pulse duty cycle and pulse frequency, etc.; delay parameters include emission delay and focal coordinates of different channels, etc.

[0100] Step 102: The laser control module excites a laser spot directed toward the posterior pole of the fundus according to the laser parameters.

[0101] Understandably, the laser spot excited by the laser modulation module is targeted to the entire posterior pole region of the retina, and the laser spot can modulate the scleral biomechanical network to inhibit abnormal axial elongation.

[0102] Step 103: A pulse signal is generated by a pulse transmitter based on pulse parameters, and multiple delayed ultrasonic signals are generated by a multi-channel delay control unit based on the pulse signal and delay parameters.

[0103] Step 104: Using an ultrasonic transducer, a dynamic focused sound field is formed based on multiple delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

[0104] It should be noted that by transmitting signals through a pulse transmitter and applying different delays to each array element in the ultrasonic transducer by a multi-channel delay control unit, the sound field focus point moves continuously along a predetermined path, achieving full coverage of the rear pole region, thereby realizing synchronous control of laser and ultrasound.

[0105] To improve the accuracy of ultrasound imaging and avoid damage to the user's eyes, this method also includes:

[0106] Step 105: Use an ultrasound transducer to collect ultrasound echo signals reflected from the posterior pole of the fundus; perform monitoring and analysis based on the ultrasound echo signals to obtain physiological monitoring parameters; determine whether the physiological monitoring parameters have preset monitoring thresholds; if they exceed the thresholds, adjust the preset control requirements.

[0107] It should be noted that the high-frequency ultrasound echo signal reflected from the posterior pole of the fundus is acquired by the x-axis array based on the ultrasound transducer, and the mid-frequency ultrasound echo signal reflected from the posterior pole of the fundus is acquired by the y-axis array based on the ultrasound transducer.

[0108] In this embodiment, the physiological monitoring parameters include axial length, location of the foveal region in the posterior pole, scleral elasticity, choroidal microvascular and aortic blood flow velocity, and scleral backscattering characteristics. The scleral backscattering characteristics include the equivalent scatterer diameter and acoustic concentration.

[0109] The process of acquiring physiological monitoring parameters includes steps S1S~S14:

[0110] S10. Eye imaging is performed using high-frequency ultrasound echoes in the ultrasound echo signal to extract the axial length of the eye and the location of the fovea region of the posterior pole of the fundus.

[0111] S11. Based on the high-frequency ultrasound echo in the ultrasound echo signal, the retinal aortic blood flow velocity is calculated by Doppler spectrum shift.

[0112] S12. Based on the intermediate frequency ultrasound echo in the ultrasound echo signal, calculate the scleral elasticity using ultrasound elastography.

[0113] S13. Based on the high-frequency ultrasound echo in the ultrasound echo signal, the choroidal blood vessel velocity is calculated by shifting the Doppler spectrum.

[0114] S14. Based on the high-frequency ultrasonic echo in the ultrasonic echo signal, scleral backscattering is detected to obtain the scleral backscattering characteristics.

[0115] In step S14, the process of obtaining scleral backscattering characteristics includes: using a multi-band fusion algorithm to perform bandpass filtering on the received ultrasound echo signal in 3-5 frequency bands, calculating the backscattering integral (BSC) value for each frequency band signal, fitting the BSC-f curve using a Gaussian scattering model with weighted least squares, dynamically adjusting the weighting coefficients according to the signal-to-noise ratio, and calculating and deriving the tissue microstructure parameters based on the slope and intercept of the fitted curve, namely the equivalent diameter D of the scatterer (range 50-200nm) and the acoustic concentration parameter C (relative value 0.1-1.0).

[0116] More specifically, this invention makes intelligent judgments based on the combined monitoring results of key physiological monitoring data such as blood flow velocity, scattering parameters, and scleral elasticity, and triggers a control strategy when any of the following conditions are met:

[0117] 1) The blood flow velocity in the choroidal or retinal vessels changes by more than 20% compared to the baseline value;

[0118] 2) The equivalent diameter D of the scatterer or the acoustic concentration C changes by more than 20% compared to the reference value;

[0119] 3) The scleral elasticity changes by more than 20% compared to the baseline value.

[0120] The control strategy involves adjusting preset control requirements to dynamically adjust ultrasonic power, duration of action, or focusing path.

[0121] For example, blood flow velocity monitoring thresholds are established for choroidal microvessels (diameter 50–200 μm) and central retinal artery (diameter 160–200 μm); changes in blood flow velocity are monitored in real time during treatment, and when the detection result changes by more than 20% compared with the blood flow velocity monitoring threshold, the ultrasound output energy is automatically adjusted (adjustment range is ±10%~20%) to achieve timely intervention and safe control.

[0122] Based on the real-time changing trends of the scatterer's equivalent diameter D and acoustic concentration C, the output parameters of the ultrasound control module are dynamically adjusted. When the change in D or C compared to the pre-treatment baseline exceeds 20%, a feedback mechanism is triggered: if D and C increase significantly, the ultrasound power is automatically reduced or the treatment duration is shortened; if D and C decrease significantly, the ultrasound energy is increased or the treatment time is extended to enhance tissue response and ensure the adaptability and safety of the treatment effect.

[0123] Scleral elasticity measurement is based on the calculation of shear wave propagation velocity using a time-domain cross-correlation algorithm to establish a baseline elastic modulus. The elastic modulus is monitored in real time during treatment, and the ultrasound output energy is automatically adjusted when the detection result changes by more than 20% compared to the monitoring threshold.

[0124] The above-described embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit it. Although the present invention 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 the present invention.

Claims

1. A photoacoustic coupled myopia control device, characterized in that, include: Ultrasonic control module, controller, and laser control module; The ultrasonic control module includes a pulse transmitter, a multi-channel delay control unit, and an ultrasonic transducer. The controller is connected to the laser control module, the pulse transmitter, and the multi-channel delay control unit, respectively, and is used to generate laser parameters, pulse parameters, and delay parameters according to preset control requirements; send the laser parameters to the laser control module, send the pulse parameters to the pulse transmitter, and send the delay parameters to the multi-channel delay control unit; The laser control module is used to excite a laser spot directed toward the posterior pole of the fundus according to the laser parameters. The pulse transmitter is used to generate a pulse signal according to the pulse parameters and transmit the pulse signal to the multi-channel delay control unit; The multi-channel delay control unit is used to generate multiple delayed ultrasonic signals according to the delay parameters and the pulse signal, and transmit the multiple delayed ultrasonic signals to the ultrasonic transducer; The ultrasonic transducer is connected to the multi-channel delay control unit and is used to form a dynamic focused sound field based on multiple delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

2. The myopia control device according to claim 1, characterized in that, Also includes: Signal acquisition card and ultrasonic monitoring module; The ultrasonic transducer is also used to receive ultrasonic echo signals reflected from the posterior pole of the fundus. The signal acquisition card is electrically connected to the ultrasonic transducer and is used to acquire the ultrasonic echo signal and send the ultrasonic echo signal to the ultrasonic monitoring module. The ultrasound monitoring module is used to monitor and analyze the ultrasound echo signal to obtain physiological monitoring parameters.

3. The myopia control device according to claim 2, characterized in that, The controller is electrically connected to the ultrasound monitoring module and is used to determine whether the physiological monitoring parameters exceed the preset monitoring threshold; if they do, the preset control requirements are adjusted.

4. The myopia control device according to claim 2, characterized in that, The ultrasonic transducer has a grid-shaped structure design; the ultrasonic transducer includes a ring array, an x-axis array, and a y-axis array; The x-axis array is arranged laterally inside the annular array, and the y-axis array is arranged longitudinally inside the annular array; A central through hole is provided between the x-axis array and the y-axis array; The ring array is used to emit a low-frequency focused ultrasound beam and receive low-frequency ultrasound echoes reflected from the posterior pole of the fundus; the x-axis array is used to emit a high-frequency focused ultrasound beam and receive high-frequency ultrasound echoes reflected from the posterior pole of the fundus; the y-axis array is used to emit a mid-frequency focused ultrasound beam and receive mid-frequency ultrasound echoes reflected from the posterior pole of the fundus.

5. The myopia control device according to claim 4, characterized in that, The laser control module includes a laser, a beam expander, and a homogenizer. The laser is used to excite a laser beam and direct the laser beam toward the beam expander; The laser beam is expanded by the beam expander and homogenized by the homogenizer in sequence to form a laser spot; the laser spot is directed toward the posterior pole of the fundus through the central through-hole.

6. The myopia control device according to claim 4, characterized in that, The ring array is a ring-shaped 256 array, the x-axis array is an x-axis linear 128 array, and the y-axis array is a y-axis linear 64 array.

7. The myopia control device according to claim 4, characterized in that, The ring array is a ring-shaped 256 array, the x-axis array is an x-axis linear 128 array, and the y-axis array is a y-axis linear 128 array. Both the x-axis array and the y-axis array are made of transparent piezoelectric material.

8. A photoacoustic coupling method for myopia control, characterized in that, The control method is implemented based on the myopia control device according to any one of claims 1-7, and the control method includes: Generate laser parameters, pulse parameters, and delay parameters according to preset control requirements; The laser control module excites a laser spot directed toward the posterior pole of the fundus according to the laser parameters; A pulse signal is generated by a pulse transmitter according to the pulse parameters, and multiple delayed ultrasonic signals are generated by a multi-channel delay control unit according to the pulse signal and the delay parameters. An ultrasonic transducer is used to form a dynamic focused sound field based on the multi-channel delayed ultrasonic signals, so that the dynamic focused sound field moves continuously along a preset path to achieve full coverage of the posterior pole of the fundus.

9. The control method according to claim 8, characterized in that, The control method also includes: Ultrasonic echo signals reflected from the posterior pole of the fundus were acquired using an ultrasonic transducer. The physiological monitoring parameters are obtained by monitoring and analyzing the ultrasound echo signals; it is determined whether the physiological monitoring parameters have preset monitoring thresholds; if they exceed the thresholds, the preset control requirements are adjusted.

10. The control method according to claim 9, characterized in that, The steps for obtaining the physiological monitoring parameters include: Eye imaging is performed using the high-frequency ultrasound echo in the ultrasound echo signal to extract the axial length and the location of the fovea region of the posterior pole of the fundus. Based on the high-frequency ultrasound echo in the ultrasound echo signal, the retinal aortic vessel flow velocity is calculated by Doppler spectrum shift; Based on the intermediate frequency ultrasound echo in the ultrasound echo signal, the scleral elasticity is calculated using ultrasound elastography. Based on the high-frequency ultrasound echo in the ultrasound echo signal, the choroidal vessel flow velocity is calculated by Doppler spectrum shift. Scleral backscattering is detected based on the high-frequency ultrasonic echo in the ultrasonic echo signal to obtain scleral backscattering characteristics.

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