An ultrasonic phantom, a measuring device and a method for measuring sound pressure within an ultrasonic phantom

Abstract

The application provides an ultrasonic phantom, which comprises a plurality of elongated columnar phantom units, the phantom units are arranged in parallel and uniformly, the phantom units comprise a measuring section for converting sound pressure into light intensity and a transmission section for conducting light waves of the measuring section, the measuring sections of the respective phantom units are equal in length, same in direction and flush in end face, and the transmission sections of the respective phantom units are equal in length, same in direction and flush in end face. The application also provides a measuring device and a measuring method for measuring the sound pressure inside the ultrasonic phantom. Through the design of the structure of the ultrasonic phantom, the ultrasonic phantom can reflect the internal sound pressure distribution by converting different sound pressures into corresponding light intensities through the phantom units; the distribution of the sound pressure on the corresponding cross section of the measuring section of the ultrasonic phantom can be preliminarily reflected through the measuring device; and the sound pressure distribution of different positions on different cross sections of the measuring section of the ultrasonic phantom can be truly reflected through the measuring device and the measuring method.

Description

Technical Field

[0001] This invention relates to the field of ultrasound medical technology, specifically to an ultrasound phantom, a measuring device for measuring the sound pressure within the ultrasound phantom, and a method thereof. Background Technology

[0002] With the development and advancement of acoustics, ultrasound technology is being widely applied in various medical and engineering fields, including medical imaging and treatment, non-invasive detection, flow sensing, ultrasonic cleaning and extraction. Because ultrasound waves have excellent penetrating power through most materials, they are widely used to study and probe the internal structural details of objects, which requires a sufficient understanding of the distribution of ultrasonic sound pressure.

[0003] Currently, ultrasound technology is used in human treatment, such as focused ultrasound ablation surgery for tumor treatment. However, how ultrasound propagates further within the human body after passing through skin, fat, and muscle remains a challenging technical problem. Human models are typically used for experiments, utilizing biomimetic materials to simulate human tissue. Even so, measuring the sound pressure inside these biomimetic materials is a significant technical hurdle. This is because conventional sound pressure measurement methods, such as microphones or hydrophones, are only suitable for gaseous or liquid environments and cannot be used to measure the sound pressure distribution within solid biomimetic materials. Therefore, this presents a challenge for the development of ultrasound medical devices, requiring a technical means to simultaneously simulate the propagation process of ultrasound within the human body and measure the sound pressure distribution within biomimetic materials. Summary of the Invention

[0004] I. Technical problems to be solved To address the shortcomings of existing technologies, this invention provides an ultrasonic phantom, a measuring device and method for measuring the sound pressure inside the ultrasonic phantom, thus solving the technical problem that existing technologies cannot measure the sound pressure distribution inside biomimetic materials.

[0005] II. Technical Solution To achieve the above objectives, the present invention provides the following technical solution: An ultrasonic phantom, the key feature of which is: it includes multiple slender columnar phantom units, the phantom units are arranged in parallel and uniformly close together, the phantom unit includes a measuring segment for converting sound pressure into light intensity and a transmission segment for transmitting the light wave of the measuring segment, the measuring segments of each phantom unit are of equal length, in the same direction and with flush end faces, and the transmission segments of each phantom unit are of equal length, in the same direction and with flush end faces.

[0006] Optionally, the measurement section includes a first light guide made of a light-guiding material and pressure-sensitive phosphors uniformly distributed within the first light guide with a particle diameter of 5-50 micrometers; the transmission section includes a second light guide made of a light-guiding material.

[0007] Optionally, the sides of the phantom units are coated with an adhesive layer with a refractive index lower than that of the light guide, and the phantom units are bonded and arranged together through the adhesive layer.

[0008] Optionally, the radial cross-section of the phantom unit is a regular hexagon, and the phantom units are arranged in a honeycomb pattern.

[0009] Optionally, the circumscribed circle diameter of the phantom unit is 0.5~3mm; And / or the transmission segment length of the phantom unit is 1 to 2 times the measurement segment length.

[0010] Optionally, the area formed by the arrangement of the phantom units can be increased or decreased depending on the required test range.

[0011] A measuring device for measuring the sound pressure inside an ultrasonic phantom is also provided, the key feature of which is that it includes: The box is filled with biomimetic fluid; The ultrasonic phantom shown in any of the above examples is housed within the box; A light source charging device forms a planar light beam perpendicular to the axis of the ultrasonic phantom and moves along the axis of the ultrasonic phantom to provide supplemental light energy for segmented irradiation of the measurement section. An ultrasonic transducer is disposed inside the housing and faces the end face of the ultrasonic phantom measurement section; A dielectric layer is disposed within the housing and located between the ultrasonic transducer and the ultrasonic phantom; A light emission recording device is positioned facing the end face of the ultrasonic phantom transmission section and is used to detect and record the light emission status of the end face of the transmission section.

[0012] Optionally, the light source charging device includes a laser that generates a beam parallel to the axial direction of the ultrasonic phantom, a reflector for reflecting the laser beam, and a cylindrical mirror for converting the reflected light from the reflector into a beam perpendicular to the planar beam. The reflector and the cylindrical mirror are mounted on a guide device and move along the axial direction of the ultrasonic phantom.

[0013] Optionally, the medium layer may be a biomimetic tissue or an ex vivo biological tissue used to simulate the cavity wall of a biological organism.

[0014] A measurement method for the measuring device shown in any of the above examples is also provided, characterized by comprising the following steps: Step 1: After the simulation environment of the measuring device is prepared, turn on the light source charging device. The planar beam of the light source charging device is aligned with the end face of the ultrasonic phantom measurement section and serves as the starting cutting plane. Step 2: After the planar beam irradiates the section area of ​​the ultrasonic phantom measurement segment for 1 minute, it is charged to saturation. The light source charging device is turned off, and the light emission recording device is turned on to record the light emission process of the end face of the ultrasonic phantom transmission segment. After waiting for 30 seconds, the ultrasonic transducer is turned on, and the light emission change process of the entire end face of the transmission segment is recorded by the light emission recording device. After 10 seconds, the ultrasonic transducer is turned off until the ultrasonic phantom stops emitting fluorescence. Step 3: The planar beam moves along the axis of the ultrasonic phantom towards the other end. After the z-interval, repeat step two and record the test information after each movement using a light-emitting recording device until the entire ultrasonic phantom measurement segment test is completed. Step 4: The light emission information of the transmission section end face tested by the light emission recording device is used to obtain the light emission status of the measurement section through data processing, thereby obtaining the sound pressure distribution inside the measurement section.

[0015] Optionally, the formula for the data processing is: I`=α a- z β b I ; Where a is the total length of the ultrasound phantom measurement section, b is the total length of the ultrasound phantom transmission section, α is the attenuation coefficient of the ultrasound phantom measurement section, and β is the attenuation coefficient of the ultrasound phantom transmission section. z is the distance between any cutting surface of the measurement segment and the starting cutting surface, I is the light intensity at any point on the end face of the transmission segment recorded by the light-emitting recording device, and I' is the light intensity at the corresponding point on the cutting surface of the measurement segment.

[0016] III. Beneficial Effects 1. By designing the structure of the ultrasonic phantom itself, different sound pressures are converted into corresponding light intensities by phantom units at different locations, enabling the ultrasonic phantom to reflect the internal sound pressure distribution.

[0017] 2. After the ultrasonic waves emitted by the ultrasonic transducer pass through the dielectric layer, they are transmitted to the measurement section of the ultrasonic phantom. The measurement section converts the sound pressure into light intensity, and the light intensity is recorded by the light-emitting recording device. This allows for a preliminary reflection of the sound pressure distribution on the corresponding cross-sectional surface of the ultrasonic phantom's measurement section.

[0018] 3. The measuring device, in conjunction with the measuring method, can systematically measure and record the measurement segments of the ultrasonic phantom. With the aid of data processing techniques, it can accurately reflect the sound pressure distribution at different points on different cross-sections of the ultrasonic phantom measurement segment, thereby reflecting the overall sound pressure distribution inside the ultrasonic phantom measurement segment. Attached Figure Description

[0019] Figure 1 This is a schematic diagram of the structure of the ultrasonic phantom of the present invention; Figure 2 for Figure 1 Schematic diagram of the structure of the middle phantom unit; Figure 3 This is an end view of the phantom unit; Figure 4 This is a schematic diagram of the measuring device of the present invention; Figure 5 for Figure 4 Schematic diagram of the structure of the ultrasound phantom; Figure 6 This is a fluorescence intensity curve of the ultrasonic phantom of the present invention after irradiation-charge-ultrasonic irradiation; Wherein: 1-ultrasonic phantom; 101-phantom unit; 1011-measuring section; 1012-transmission section; 102-adhesive layer; 2-box; 3-light source charging device; 301-laser; 302-reflector; 303-cylindrical mirror; 4-ultrasonic transducer; 5-dielectric layer; 6-luminescent recording device; 7-bionic fluid; 8-planar beam; 9-initial cutting surface; 10-guiding device. Detailed Implementation

[0020] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0021] Unless otherwise specified, all raw materials used in this invention can be obtained commercially, and the equipment used in this invention can be conventional equipment in the relevant field or refer to existing technology in the relevant field.

[0022] Figure 1 This is a schematic diagram of the structure of an ultrasonic phantom as an exemplary embodiment of the present invention.

[0023] like Figure 1 As shown: The present invention provides an ultrasonic phantom, comprising multiple slender columnar phantom units 101. Each phantom unit 101 includes a measurement segment 1011 for converting sound pressure into light intensity and a transmission segment 1012 for transmitting the light waves of the measurement segment 1011. The measurement segment 1011 includes a first light guide made of a light-guiding material and pressure-sensitive phosphors uniformly distributed within the first light guide with a particle diameter of 5-50 micrometers. The transmission segment 1012 includes a second light guide made of a light-guiding material.

[0024] Material selection and preparation instructions for ultrasound phantoms: 1. Light guiding material: Transparent hydrogel is used. The hydrogel meets the requirements of simulating the acoustic characteristics of human soft tissue. Therefore, transparent hydrogel is preferred as the light guiding material. The refractive index of the transparent hydrogel is between 1.46 and 1.56. Transparent hydrogel with a high refractive index is preferred.

[0025] 2. Pressure-sensitive fluorescent materials possess two important physical properties: First, upon irradiation with a specific wavelength (usually high-frequency blue or ultraviolet light), some electrons around the atomic nucleus transition from their original ground-state orbitals to higher-energy orbitals, such as from the ground state to the first or second excited singlet state. These first or second excited singlet states are unstable and gradually return to the ground state over time. When the electrons transition back to the ground state, energy is released in the form of light, thus producing fluorescence. Second, their pressure-sensitive properties exhibit fluorescence quenching or enhancement response characteristics to externally applied pressure.

[0026] For example, BaSi2O2N2:Eu 2+ This material is typically in the form of microparticle powder. When excited by light in the wavelength range of 310nm-460nm, it can continuously emit visible light with a center wavelength of 496nm. By uniformly mixing these fluorescent particles into some substrate materials, such as the transparent gel mentioned above, pressure-sensitive fluorescent materials of arbitrary shapes can be formed. After blue light irradiation, it can uniformly emit fluorescence, and the fluorescence intensity will gradually decrease. When ultrasonic waves irradiate the material, the fluorescence intensity will rise rapidly, reach a peak, and then continue to decrease (e.g., ...). Figure 6 (As shown). The higher the sound pressure level, the greater the peak value of enhanced fluorescence intensity, and vice versa.

[0027] Therefore, by utilizing the aforementioned properties of pressure-sensitive fluorescent materials and combining them with transparent hydrogels that simulate human tissue to create an ultrasonic phantom, and then placing the phantom in the area to be detected, the intensity signal of sound pressure can be converted into a light intensity signal. By detecting the light signal, the intensity distribution of sound pressure can be deduced.

[0028] 3. Preparation of the ultrasonic phantom: Prepare a hollow mold with a cavity having the same cross-sectional shape as the corresponding phantom unit 101 of the ultrasonic phantom. The phantom unit 101 can be other regular cross-sectional shapes. Preferably, the phantom unit 101 has a regular hexagonal cross-section. The phantom unit 101 is prepared using a hollow mold with a regular hexagonal cavity. To prevent the phantom unit 101 from being too large and affecting the test resolution, the circumscribed circle diameter of the phantom unit 101 can be selected within the range of 0.5~3mm. In this example, the circumscribed circle diameter of the regular hexagonal phantom unit 101 is preferably 1mm.

[0029] The transmission segment length of the phantom unit is 1.5 times the measurement segment length. Of course, the transmission segment length can also be 1 or 2 times the measurement segment length. On the one hand, this prevents the light intensity from being severely attenuated due to an excessively long transmission segment. On the other hand, it prevents light intensity interference due to an excessively short transmission segment.

[0030] Pressure-sensitive phosphor is mixed into a liquid transparent hydrogel at a weight ratio of (0.5~1):1. This ratio ensures that the pressure-sensitive phosphor can be converted into sufficient light intensity while preventing excessive attenuation of light transmission due to excessive phosphor content. After the pressure-sensitive phosphor and hydrogel are thoroughly mixed, the mixture is poured into a mold and solidified to form the measuring segment 1011. Then, the liquid transparent hydrogel is poured into the mold and solidified to form the transmission segment 1012, which is connected to the measuring segment 1011 during molding.

[0031] Please see the appendix Figure 2 and 3 The phantom unit 101 has a radial cross-section of a regular hexagon. The sides of the phantom unit 101 are coated with an adhesive layer 102 with a refractive index lower than that of the light guide. The phantom units 101 are arranged in parallel and are tightly packed in a honeycomb pattern through the adhesive layer 102, forming a seamless solid. The measuring segments 1011 of each phantom unit 101 are of equal length, oriented in the same direction, and have flush end faces. The transmission segments 1012 of each phantom unit 101 are of equal length, oriented in the same direction, and have flush end faces. For example, the adhesive layer 102 is made of UV-curable adhesive, also known as shadowless adhesive or ultraviolet light curing adhesive. The refractive index of the shadowless adhesive is approximately 1.36, lower than that of transparent hydrogel. This improves total internal reflection of light within the phantom unit 101, thereby forming an optical channel within the phantom unit 101 to facilitate the transmission of small-angle light.

[0032] It should also be noted that the area formed by the arrangement of the phantom units 101 increases or decreases depending on the required test range. The required test range depends on the size of the simulated object.

[0033] Figure 4 This is a schematic diagram of the structure of a measuring device for measuring the sound pressure inside an ultrasonic phantom according to the present invention.

[0034] like Figure 4 As shown, a measuring device for measuring the sound pressure inside an ultrasonic phantom includes a housing 2, an ultrasonic phantom 1 as shown in any of the above examples, a light source charging device 3, an ultrasonic transducer 4, a dielectric layer 5, and a light emission recording device 6.

[0035] The housing 2 is filled with biomimetic fluid 7, and the ultrasonic phantom 1 is housed within the housing 2. The ultrasonic transducer 4 is located within the housing 2 and faces the end face of the measuring section 1011 of the ultrasonic phantom 1. The luminescent recording device 6 faces the end face of the transmission section 1012 of the ultrasonic phantom 1 and is used to detect and record the luminescence of the end face of the transmission section 1012. The housing 2 is made of transparent glass to facilitate the installation of the luminescent recording device 6 and to avoid it occupying installation space within the housing 2. The light source charging device 3 is used to provide supplemental light energy to the measuring section 1011 of the ultrasonic phantom 1 by segmental irradiation. The dielectric layer 5 is located within the housing 2 and between the ultrasonic transducer 4 and the ultrasonic phantom 1; the dielectric layer 5 is made of biomimetic tissue or ex vivo biological tissue used to simulate the cavity wall of a biological organism.

[0036] In detail, the light source charging device 3 includes a laser 301 that generates a beam parallel to the axis of the ultrasonic phantom 1, a reflector 302 for reflecting the beam of the laser 301, and a cylindrical mirror 303 for converting the reflected light from the reflector 302 into a planar beam 8. The reflector 302 and the cylindrical mirror 303 are mounted on the guide device 10 and move along the axis of the ultrasonic phantom 1, so that the planar beam 8 is perpendicular to the axis of the ultrasonic phantom 1 and moves along the axis of the ultrasonic phantom 1, for segmented irradiation of the measurement section 1011 to supplement light energy.

[0037] Assembly and Usage Instructions: The housing 2 is filled with an appropriate amount of water as biomimetic fluid 7, simulating the external environment during ultrasound therapy. The ultrasound transducer 4 is fixed to one end of the housing 2. A piece of ex vivo biological tissue simulating the wall of a human body cavity is fixed in front of the ultrasound transducer 4. The measuring segment 1011 of the ultrasound phantom 1 faces the ex vivo biological tissue. The end face of the measuring segment 1011 is selected as the starting cutting surface 9. A laser optical path is installed above the housing 2. A laser 301 with a center wavelength of 310~460nm is selected as the excitation source. The beam diameter and divergence angle of the excitation source are kept as small as possible. The direction of the light is changed by reflecting the light using a reflector 302, pointing it towards the ultrasound phantom 1. Then, the cylindrical laser beam is converted into a fan-shaped planar beam 8 by a cylindrical mirror 303, similar to the shape of a thin blade. The beam guiding device 10 adopts a linear guide rail arranged along the axis of the ultrasonic phantom 1. The reflector 302 and cylindrical mirror 303 can move linearly along the linear guide rail. Every time the reflector 302 and cylindrical mirror 303 move a certain distance, the planar beam 8 can charge the corresponding section of the ultrasonic phantom 1 measurement segment 1011 that it is irradiated. After charging, the ultrasonic transducer 4 is turned on. The ultrasonic phantom 1 measurement segment 1011 receives the sound pressure and converts the sound pressure into light intensity. The light intensity is transmitted through the transmission segment 1012 of the ultrasonic phantom 1 and the distribution is reflected on the end face of the transmission segment 1012. A camera is selected as the light emission recording device 6 to record the light emission change process of the entire transmission segment 1012 end face, thereby reflecting the sound pressure distribution of each section inside the ultrasonic phantom 1 measurement segment 1011.

[0038] A measurement method for the measuring device shown in the above example, in conjunction with the appendix Figure 5 As shown, proceed with the following steps: Step 1: Inject the biomimetic fluid 7 into the transparent box 2, and select a suitable medium layer 5 such as ex vivo biological tissue. When the simulation environment of the measuring device is ready, turn on the light source charging device 3. The planar beam 8 of the light source charging device 3 is aligned with the end face of the measuring section 1011 of the ultrasonic phantom 1, and serves as the starting cutting surface 9. Step 2: The planar beam 8 irradiates and charges the section area of ​​the measurement segment 1011 of the ultrasonic phantom 1 until saturation. The light source charging device 3 is turned off, and the light emission recording device 6 is turned on to record the light emission process of the end face of the transmission segment 1012 of the ultrasonic phantom 1. Then, the ultrasonic transducer 4 is turned on, and the light emission change process of the entire end face of the transmission segment 1012 is recorded by the light emission recording device 6. Then, the ultrasonic transducer 4 is turned off until the ultrasonic phantom 1 stops emitting fluorescence. Step 3: The planar beam 8 moves along the axis of the ultrasonic phantom 1 to the other end. After the z-interval, repeat step two and record the test information after each movement using the light-emitting recording device 6 until the entire ultrasound phantom 1 measurement segment 1011 test is completed. Step 4: The light emission information of the transmission section 1012 end face tested by the light emission recording device 6 is used to obtain the light emission status of the measurement section 1011 through data processing, thereby obtaining the sound pressure distribution inside the measurement section 1011.

[0039] In the ultrasonic phantom 1 test section, the luminescence of the pressure-sensitive phosphor, dispersed within the material and not transparent, is complex. However, in each experiment, the irradiated and excited area is a cross-sectional region where the fluorescent particles emit the strongest light. When irradiated by ultrasound, due to the pressure-sensitive characteristics, the fluorescence intensity in this region is increased rapidly, with a greater increase in areas of higher sound pressure. Based on the existence of the optical channel within the ultrasonic phantom 1, small-angle fluorescence is trapped within the channel and does not diffuse, while large-angle fluorescence escapes the channel and is dissipated by various random scatterings, preventing propagation within the channel. Therefore, the light at the transmission section 1012 end face of the ultrasonic phantom 1 can be considered as the result of the attenuation of small-angle light emitted from the measurement section 1011 cross-section within the optical channel. The attenuation law is similar to that of optical fiber attenuation, exhibiting exponential attenuation. The attenuation coefficient can be experimentally measured by irradiating the phantom with a single light source and measuring the light intensity at both ends.

[0040] Therefore, the following data processing calculation formula is adopted: I`=α a- z β b I ; Where a is the total length of the measurement section 1011 of the ultrasound phantom 1, b is the total length of the transmission section 1012 of the ultrasound phantom 1, α is the attenuation coefficient of the measurement section 1011 of the ultrasound phantom 1, and β is the attenuation coefficient of the transmission section 1012 of the ultrasound phantom 1. z is the distance between any cutting surface of the measurement segment 1011 and the starting cutting surface 9, I is the light intensity at any point on the end face of the transmission segment 1012 recorded by the light-emitting recording device 6, and I' is the light intensity at the corresponding point on the cutting surface of the measurement segment 1011.

[0041] In this way, the actual luminescence of each section surface is inferred from the luminescence recorded by the luminescence recording device 6 when the planar beam 8 illuminates it. After several scans, the spatial luminescence of the entire phantom test section can be restored, thereby obtaining the spatial distribution of sound pressure inside the ultrasonic phantom 1 measurement section 1011.

[0042] It should be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitations, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0043] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. An ultrasonic phantom, characterized in that: The phantom unit comprises multiple slender, columnar phantom units arranged in parallel and uniformly close together. Each phantom unit includes a measurement segment for converting sound pressure into light intensity and a transmission segment for transmitting light waves from the measurement segment. The measurement segments of each phantom unit are of equal length, oriented in the same direction, and have flush end faces. Similarly, the transmission segments of each phantom unit are of equal length, oriented in the same direction, and have flush end faces.

2. The ultrasonic phantom according to claim 1, characterized in that: The measurement section includes a first light guide made of light-guiding material and pressure-sensitive phosphors uniformly distributed within the first light guide with a particle diameter of 5-50 micrometers; the transmission section includes a second light guide made of light-guiding material.

3. The ultrasonic phantom according to claim 2, characterized in that: The sides of each phantom unit are coated with an adhesive layer with a refractive index lower than that of the light guide, and the phantom units are bonded and arranged together through the adhesive layer.

4. The ultrasonic phantom according to claim 3, characterized in that: The radial cross-section of the phantom unit is a regular hexagon, and the phantom units are arranged in a honeycomb pattern.

5. An ultrasonic phantom according to claim 4, characterized in that: The outer diameter of the phantom unit is 0.5~3mm; And / or the length of the transmission segment of the phantom unit is 1 to 2 times the length of the measurement segment.

6. An ultrasonic phantom according to claim 5, characterized in that: The area formed by the arrangement of the phantom units increases or decreases depending on the required test range.

7. A measuring device for measuring the sound pressure inside an ultrasonic phantom, characterized in that, include: The box is filled with biomimetic fluid; The ultrasonic phantom according to any one of claims 1 to 6 is disposed inside the box; A light source charging device forms a planar light beam perpendicular to the axis of the ultrasonic phantom and moves along the axis of the ultrasonic phantom to provide supplemental light energy for segmented irradiation of the measurement section. An ultrasonic transducer is disposed inside the housing and faces the end face of the measuring section of the ultrasonic phantom; A dielectric layer is disposed within the housing and located between the ultrasonic transducer and the ultrasonic phantom; A light emission recording device is positioned facing the end face of the transmission segment of the ultrasonic phantom and is used to detect and record the light emission of the end face of the transmission segment.

8. The measuring device according to claim 7, characterized in that: The light source charging device includes a laser that generates a beam parallel to the axial direction of the ultrasonic phantom, a reflector for reflecting the laser beam, and a cylindrical mirror for converting the reflected light from the reflector into a beam perpendicular to the planar beam. The reflector and the cylindrical mirror are mounted on a guide device and move along the axial direction of the ultrasonic phantom.

9. The measuring device according to claim 7 or 8, characterized in that: The medium layer is made of biomimetic tissue or ex vivo biological tissue used to simulate the cavity wall of a biological organism.

10. A measurement method using the measuring device according to any one of claims 7 to 9, characterized in that, Follow these steps: Step 1: After the simulation environment of the measuring device is prepared, turn on the light source charging device. The planar beam of the light source charging device is aligned with the end face of the measuring segment of the ultrasonic phantom and serves as the starting cutting plane. Step 2: The planar light beam irradiates and charges the section area of ​​the measurement segment of the ultrasonic phantom until saturation. The light source charging device is turned off, and the light emission recording device is turned on to record the light emission process of the transmission segment end face of the ultrasonic phantom. Then, the ultrasonic transducer is turned on, and the light emission change process of the entire transmission segment end face is recorded by the light emission recording device. Then, the ultrasonic transducer is turned off until the ultrasonic phantom stops emitting fluorescence. Step 3: The planar beam moves along the axis of the ultrasonic phantom towards the other end. After the z-interval, repeat step two to record the test information after each movement using the light-emitting recording device until the test of the measurement segment of the entire ultrasonic phantom is completed; Step 4: The light emission information of the transmission segment end face tested by the light emission recording device is processed to obtain the light emission status of the measurement segment, thereby obtaining the sound pressure distribution inside the measurement segment.

11. The measurement method according to claim 10, characterized in that, The formula for data processing is: I`=α a- z β b I ; Where a is the total length of the ultrasound phantom measurement section, b is the total length of the ultrasound phantom transmission section, α is the attenuation coefficient of the ultrasound phantom measurement section, and β is the attenuation coefficient of the ultrasound phantom transmission section. z is the distance between any cutting surface of the measurement segment and the starting cutting surface, I is the light intensity at any point on the end face of the transmission segment recorded by the light-emitting recording device, and I' is the light intensity at the corresponding point on the cutting surface of the measurement segment.

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