Method and device for measuring elasticity of transparent biological tissue

Abstract

The invention relates to the technical field of optical imaging, in particular to a transparent biological tissue elasticity measuring method and device.The method comprises the steps that M-mode images at different excitation depths are collected at the same lateral position of the tissue surface based on excitation of an excitation source at different depths in a transparent tissue, and comparing the time difference of the elastic waves generated at different excitation depths reaching the same depth in the imaging area on the tissue surface, and calculating the propagation velocity of the elastic waves in the transparent tissue to obtain the elastic modulus in the transparent tissue. Therefore, the problems that in the related technology, due to the fact that the surface of the transparent tissue has special tissue structure characteristics or optical characteristics, optical imaging can only conduct imaging on the position near the surface of the transparent tissue, the interior of the transparent tissue cannot be observed, and propagation of elastic waves in the transparent tissue cannot be detected are solved; the elastic information in the transparent tissue cannot be obtained, so that the medical diagnosis result is influenced.

Description

Technical Field

[0001] The present application relates to the field of optical imaging technology, and in particular to a method and device for measuring the elasticity of transparent biological tissue. Background Art

[0002] Among the related technologies, OCE (Optical Coherence Elastography) technology based on OCT (Optical Coherence Tomography) technology is an emerging technology for measuring the biomechanics of transparent tissues. It has the characteristics of non-invasiveness, real-time and high sensitivity. It has been used to measure the elasticity of some optically scattering tissues, such as the retina, cornea and blood vessels.

[0003] However, in the related technology, due to the transparent characteristics of tissue, optical imaging can only image the area near the surface of transparent tissue, but cannot observe the inside of transparent tissue, resulting in the inability to detect the propagation of elastic waves inside transparent tissue and the inability to obtain elastic information inside transparent tissue, which in turn affects the results of medical diagnosis and urgently needs to be improved. Summary of the invention

[0004] The present application provides a method and device for measuring the elasticity of transparent biological tissues to solve the problem in related technologies that, due to the special tissue structural features or optical properties on the surface of transparent tissues, optical imaging can only image the area near the surface of transparent tissues, but cannot observe the inside of transparent tissues, resulting in the inability to detect the propagation of elastic waves inside transparent tissues, and the inability to obtain elastic information inside transparent tissues, which in turn affects the results of medical diagnosis.

[0005] The first aspect of the present application provides a method for measuring the elasticity of transparent biological tissue, comprising the following steps: based on an excitation source exciting at different depths inside the transparent tissue, collecting M-mode images at different excitation depths at the same lateral position on the tissue surface; based on the M-mode image, comparing the time difference of elastic waves generated at different excitation depths reaching the same depth in the imageable area on the tissue surface; and calculating the elastic wave propagation speed inside the transparent tissue based on the time difference to obtain the elastic modulus inside the transparent tissue.

[0006] Through the above technical scheme, the embodiment of the present application can comprehensively detect the elastic information of different layers inside the tissue by exciting at different depths inside the transparent tissue and collecting M images at the same lateral position on the tissue surface, breaking through the limitation that the traditional method can only obtain surface information; by comparing the time difference of elastic waves at different excitation depths reaching the same depth on the tissue surface, a reliable basis is provided for accurately calculating the propagation speed of internal elastic waves, and then the elastic modulus inside the transparent tissue is accurately obtained, thereby realizing the quantitative evaluation of the elastic properties inside the transparent tissue, which helps to deeply understand the mechanical state inside the transparent tissue and improve the accuracy and reliability of medical diagnosis results.

[0007] Optionally, in one embodiment of the present application, the M-mode images collected at different excitation depths at the same lateral position on the tissue surface include: recording scanning data along the depth direction at different times during each excitation process at the same lateral position; and reconstructing multiple scanning data along the depth direction at the same lateral position into a timing diagram of the vibration signal at the lateral position changing with depth and time.

[0008] Through the above technical solution, the embodiment of the present application can collect M-mode images at different excitation depths at the same lateral position on the tissue surface, and can accurately capture the structural and characteristic changes at different depths inside the tissue by recording the scanning data along the depth direction at different times during each excitation process. Reconstructing multiple scanning data along the depth direction into a time series diagram can intuitively present the changes of the vibration signal with depth and time, which is helpful for in-depth analysis of the dynamic response of the tissue at different depths and time dimensions.

[0009] Optionally, in one embodiment of the present application, the calculation formula for the elastic wave propagation velocity inside the transparent tissue is:

[0010]

[0011] Among them, V S is the velocity of elastic waves propagating between different excitation depths, ΔD is the depth difference of excitation sources at different depths inside the transparent tissue, and ΔT is the time difference for the elastic waves generated at different excitation depths to reach the same depth in the imageable area on the surface of the transparent tissue.

[0012] Through the above-mentioned technical scheme, the embodiment of the present application can reduce human judgment and errors based on measurable physical quantities, provide a reliable method for accurately obtaining the propagation speed of elastic waves inside transparent tissue, and help to more accurately evaluate the mechanical state inside transparent tissue, thereby providing a strong quantitative basis for the diagnosis, disease monitoring and formulation of treatment plans for transparent tissue-related diseases.

[0013] Optionally, in one embodiment of the present application, the elastic modulus is obtained by calculating the propagation speed of the elastic wave.

[0014] Through the above technical solution, the embodiment of the present application can establish a direct correlation between the elastic modulus and the elastic wave propagation velocity for calculation, providing a direct and effective way to quantitatively evaluate the mechanical properties of transparent tissue, avoiding the uncertainty caused by relying on subjective judgment or other indirect methods, thereby improving the accuracy of transparent tissue elasticity measurement.

[0015] The second aspect of the present application provides a device for measuring the elasticity of transparent biological tissue, including: an acquisition module, which is used to acquire M-mode images at different excitation depths at the same lateral position on the tissue surface when an excitation source excites at different depths inside the transparent tissue; a comparison module, which is used to compare the time difference of elastic waves generated at different excitation depths reaching the same depth in the imageable area of ​​the tissue surface based on the M-mode image; and a calculation module, which is used to calculate the propagation speed of the elastic wave inside the transparent tissue based on the time difference to obtain the elastic modulus inside the transparent tissue.

[0016] Through the above technical solution, the embodiment of the present application can excite at different depths inside the transparent tissue and collect M images at the same lateral position on the tissue surface, comprehensively detect the elastic information of different layers inside the tissue, and break through the limitation that the traditional method can only obtain surface information; by comparing the time difference of elastic waves reaching the same depth on the tissue surface at different excitation depths, a reliable basis is provided for accurately calculating the propagation speed of internal elastic waves, and then the elastic modulus inside the transparent tissue is accurately obtained, and the quantitative evaluation of the elastic properties inside the transparent tissue is realized, which helps to deeply understand the mechanical state inside the transparent tissue and improve the accuracy and reliability of medical diagnosis results. Optionally, in one embodiment of the present application, the acquisition module includes: a recording unit for recording the scanning data along the depth direction at different times during each excitation process at the same lateral position; a reconstruction unit for reconstructing multiple scanning data along the depth direction into a time series diagram of the vibration signal at the lateral position changing with depth and time.

[0017] Optionally, in one embodiment of the present application, the acquisition module includes: a recording unit for recording scanning data along the depth direction at different times during each excitation process at the same lateral position; a reconstruction unit for reconstructing multiple scanning data along the depth direction at the same lateral position into a timing diagram of the vibration signal at the lateral position changing with depth and time.

[0018] Through the above technical solution, the embodiment of the present application can collect M-mode images at different excitation depths at the same lateral position on the tissue surface, and can accurately capture the structural and characteristic changes at different depths inside the tissue by recording the scanning data along the depth direction at different times during each excitation process. Reconstructing multiple scanning data along the depth direction into a time series diagram can intuitively present the changes of the vibration signal with depth and time, which is helpful for in-depth analysis of the dynamic response of the tissue at different depths and time dimensions.

[0019] Optionally, in one embodiment of the present application, the calculation formula for the elastic wave propagation velocity inside the transparent tissue is:

[0020]

[0021] Among them, V S is the velocity of elastic waves propagating between different excitation depths, ΔD is the depth difference of excitation sources at different depths inside the transparent tissue, and ΔT is the time difference for the elastic waves generated at different excitation depths to reach the same depth in the imageable area on the surface of the transparent tissue.

[0022] Through the above-mentioned technical scheme, the embodiment of the present application can reduce human judgment and errors based on measurable physical quantities, provide a reliable method for accurately obtaining the propagation speed of elastic waves inside transparent tissue, and help to more accurately evaluate the mechanical state inside transparent tissue, thereby providing a strong quantitative basis for the diagnosis, disease monitoring and formulation of treatment plans for transparent tissue-related diseases.

[0023] Optionally, in one embodiment of the present application, the elastic modulus is obtained by calculating the propagation speed of the elastic wave.

[0024] Through the above technical solution, the embodiment of the present application can establish a direct correlation between the elastic modulus and the elastic wave propagation velocity for calculation, providing a direct and effective way to quantitatively evaluate the mechanical properties of transparent tissue, avoiding the uncertainty caused by relying on subjective judgment or other indirect methods, thereby improving the accuracy of transparent tissue elasticity measurement.

[0025] The third aspect of the present application provides an electronic device, comprising: a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the method for measuring the elasticity of transparent biological tissue as described in the above embodiment.

[0026] A fourth aspect of the present application provides a computer-readable storage medium, which stores a computer program that, when executed by a processor, implements the above-mentioned method for measuring the elasticity of transparent biological tissue.

[0027] The fifth aspect of the present application provides a computer program product, including a computer program, which, when executed, is used to implement the above-mentioned method for measuring the elasticity of transparent biological tissue.

[0028] The embodiments of the present application can comprehensively detect elastic information of different internal layers by exciting at different depths inside the transparent tissue and collecting M images at the same lateral position on the surface, compare the time difference when elastic waves at different excitation depths reach the same depth, accurately calculate the propagation speed of the internal elastic waves, and then accurately derive the internal elastic modulus to achieve quantitative evaluation, which is helpful for in-depth understanding of the internal mechanical state, improves the accuracy and reliability of medical diagnosis, and reduces human judgment errors based on measurable physical quantities; by recording scanning data along the depth direction at different times when collecting M-mode images, accurately capturing changes in internal structural characteristics, reconstructing the time series to intuitively present changes in vibration signals, and helping to analyze dynamic responses at different depths and time dimensions; by directly correlating the elastic modulus with the elastic propagation speed, a direct and effective approach is provided for quantitatively evaluating the mechanical properties of transparent tissues, avoiding uncertainty, and improving the accuracy of elasticity measurements.

[0029] Additional aspects and advantages of the present application will be given in the description below, and some will become apparent from the description below, or will be learned through practice of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] The above and / or additional aspects and advantages of the present application will become apparent and easily understood from the following description of the embodiments in conjunction with the accompanying drawings, in which:

[0031] Figure 1 A flow chart of a method for measuring elasticity of transparent biological tissue provided according to an embodiment of the present application;

[0032] Figure 2 Schematic diagram of the structure of an optical coherence elastic imaging system based on swept source OCT according to one embodiment of the present application;

[0033] Figure 3 is a schematic diagram of an M-mode OCT data acquisition method according to an embodiment of the present application;

[0034] Figure 4 A schematic diagram of an excitation method according to a specific embodiment of the present application;

[0035] Figure 5 It is a schematic diagram of a method for measuring elastic wave velocity inside a lens according to a specific embodiment of the present application;

[0036] Figure 6 It is a flow chart of a method for measuring elastic wave velocity inside a lens according to a specific embodiment of the present application;

[0037] Figure 7 A schematic diagram of the structure of a transparent biological tissue elasticity measuring device provided according to an embodiment of the present application;

[0038] Figure 8 The figure is a structural example diagram of an electronic device provided according to an embodiment of the present application. DETAILED DESCRIPTION

[0039] Embodiments of the present application are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are intended to be used to explain the present application, and should not be construed as limiting the present application.

[0040] The following describes the transparent biological tissue elasticity measurement method and device of the embodiment of the present application with reference to the accompanying drawings. In view of the related art mentioned in the above background technology, due to the special tissue structure characteristics or optical characteristics on the surface of the transparent tissue, optical imaging can only image the transparent tissue surface, but cannot observe the inside of the transparent tissue, which leads to the problem that the inside of the transparent tissue cannot be observed, and the elastic information inside the transparent tissue cannot be obtained, which further affects the medical diagnosis results. The present application provides a transparent biological tissue elasticity measurement method, in which the elastic information of different layers inside the tissue can be fully detected by exciting at different depths inside the transparent tissue and collecting M images at the same lateral position on the tissue surface, breaking through the limitation that the traditional method can only obtain surface information; by comparing the time difference of elastic waves at different excitation depths reaching the same depth on the tissue surface, a reliable basis is provided for accurately calculating the propagation speed of the internal elastic wave, and then the elastic modulus inside the transparent tissue is accurately obtained, and the quantitative evaluation of the elastic characteristics inside the transparent tissue is realized, which helps to deeply understand the mechanical state inside the transparent tissue and improve the accuracy and reliability of the medical diagnosis results. Thereby, a problem in related technologies is solved that, due to the special tissue structural features or optical properties on the surface of transparent tissue, optical imaging can only image the surface of transparent tissue but cannot observe the inside of the transparent tissue, resulting in the inability to detect the propagation of elastic waves inside the transparent tissue and the inability to obtain the elastic information inside the transparent tissue, which in turn affects the results of medical diagnosis.

[0041] Specifically, Figure 1 A schematic flow chart of a method for measuring elasticity of transparent biological tissue provided in an embodiment of the present application.

[0042] like Figure 1 As shown, the method for measuring the elasticity of transparent biological tissue comprises the following steps:

[0043] In step S101 , based on the excitation of an excitation source at different depths inside a transparent tissue, M-mode images at different excitation depths are collected at the same lateral position on the tissue surface.

[0044] It should be understood by those skilled in the art that the optical coherence elastic imaging system includes an ARF (Acoustic Radiation Force) excitation unit and an OCT imaging unit. Figure 2 The OCT unit can use spectral domain OCT or swept source OCT.

[0045] Specifically, the swept source OCT system mainly includes a swept source, a coupler, a reference optical path, a sample optical path, and a photodetector. The swept source OCT uses a swept laser light source. The light from the light source is divided into two beams by coupler A, one part of which enters the sample arm and the other part enters the reference arm. The light in the reference arm is reflected by the reflector and interferes with the backscattered light from the sample arm in coupler B. The interference light signal is converted into an electrical signal and enters the high-speed acquisition card. After the signal is processed, tissue imaging is achieved.

[0046] Furthermore, the ultrasonic excitation system includes a signal generator, an amplifier and an ultrasonic transducer. In the ultrasonic excitation unit, the signal output by the signal generator is amplified by the amplifier, and then drives the ultrasonic transducer to output ultrasonic waves. The ultrasonic waves induce tissue vibration and generate elastic waves in the tissue.

[0047] Optionally, in one embodiment of the present application, M-mode images at different excitation depths are collected at the same lateral position on the tissue surface, including: recording scanning data along the depth direction at different times during each excitation process at the same lateral position; and reconstructing multiple scanning data along the depth direction into a time series diagram of the vibration signal at the lateral position changing with depth and time.

[0048] Specifically, the present invention adopts an OCT data acquisition method based on M-scan, the principle of which is as follows: Figure 3 As shown in the figure. M scanning refers to taking multiple samples at the same lateral position of the sample, and expanding the sampled signal lines in time sequence to form a one-dimensional timing diagram (i.e., the M-mode image of OCT). As the ultrasound moves down and repeatedly excites to induce elastic waves, the OCT unit collects multiple M-mode timing diagrams at different excitation depths at the same lateral position.

[0049] The following is a specific example of measuring the elasticity of the lens to explain in detail the method for measuring the elasticity of transparent biological tissue of the present application (in the specific example, the lens and the transparent tissue have an equivalent interpretation relationship).

[0050] In the actual implementation process, Figure 4As shown, the ultrasonic transducer excites the lens from the side, and OCT images the surface of the lens at the front of the eyeball, that is, the light beam is detected from the front of the lens, and the sound beam is excited from the side of the transparent biological tissue. The angle between the sound beam and the light beam can be approximately 90 degrees, or between 0-90, so as to detect the elastic waves propagating from the inside of the lens to the surface of the lens.

[0051] The embodiments of the present application can achieve a comprehensive detection of the elastic properties inside the lens by exciting at different depths inside the lens and collecting M-mode images at the same lateral position on the tissue surface, thereby providing an accurate data basis for the subsequent accurate calculation of the elastic wave propagation velocity.

[0052] In step S102, based on the M-mode image, the time difference of the elastic waves generated at different excitation depths reaching the same depth in the imageable area of ​​the tissue surface is compared.

[0053] It is understandable that according to the M-scan OCT data acquisition method in step S101, in the M-scan mode, the same lateral position will record N (N≥2) A-line scan data at different times (i.e., 1 M-mode scan), and analyze the change of phase over time at different depths of this lateral position, thereby analyzing the tissue vibration at this position. The ultrasonic transducer will continuously output the excitation signal between the nth to n+kth A-line scans, 1≤n≤n+k≤N.

[0054] Specifically, elastic waves are essentially the propagation of vibrations, and phase-sensitive Doppler optical coherence tomography methods can be used to detect elastic vibrations, or variance analysis or decorrelation analysis optical coherence tomography methods can be used to detect elastic vibrations. The embodiment of the present application uses a Doppler variance method to detect elastic vibrations, detects displacements to obtain elastic vibrations by analyzing and comparing the differences between continuous scanning signals, reconstructs the propagation of elastic waves through the propagation of vibrations in space, and then uses parameters such as the attenuation of elastic wave amplitudes, group velocity, and phase velocity to measure the elastic information of the lens.

[0055] In actual implementation, the principle of Doppler optical coherence tomography is to combine the Doppler principle with OCT and use phase-resolved Doppler OCT to extract phase information from the OCT data. At the i-th position of the depth position of the j-th A-line, calculate the phase shift between the same A-line at t and t+τ. Where τ is the time interval between two A lines, and the elastic vibration velocity V along the OCT beam direction is i,j (t) The formula is as follows:

[0056]

[0057] Where λ0 is the central wavelength of the OCT light source and n is the refractive index of the sample.

[0058] In some cases, the phase-sensitive Doppler optical coherence tomography method is sensitive to displacements parallel to the OCT beam, but cannot detect displacements perpendicular to the OCT beam. When orthogonal ARF excitation is used, the vibration of the lens is perpendicular to the OCT beam. Therefore, the OCT-based Doppler variance method is used to detect vibrations perpendicular to the OCT beam. On the jth A line, the depth position is the Doppler variance at the ith position. It can be determined from OCT data using the following formula:

[0059]

[0060] Among them, F j,i and F j+1,i The OCT signals at time t and t+τ are respectively. The Doppler variance method is more sensitive to lateral vibration and will not be distorted by overall motion and phase wrapping, so data processing will be simpler and faster.

[0061] In the actual implementation process, Figure 5 As shown, the focus of the ultrasonic beam is moved to the inside of the lens, inducing elastic waves inside the lens that propagate upward and downward with the focus as the vibration source. If the focus of the ultrasonic transducer is moved downward at a fixed step size, the time of the elastic wave detected on the surface of the lens will be delayed; if the focus of the ultrasonic transducer is moved upward at a fixed step size, the time of the elastic wave detected on the surface of the lens will be advanced. When the ultrasonic transducer is focused on the surface of the lens, move the focus of the transducer downward until the first elastic wave propagating upward from the transducer focus position to the surface of the lens appears, and mark this excitation position as position 1. Then move the focus of the ultrasonic transducer downward multiple times with known step sizes, record the time when the elastic wave induced by the subsequent ultrasonic radiation force reaches the surface of the lens, and mark them as T in turn. n .

[0062] The embodiments of the present application can accurately obtain the time series of elastic waves arriving at the same depth under different excitation depths through marking and recording, thereby facilitating the calculation of time differences, and use the Doppler variance method to accurately detect elastic vibrations, thereby accurately determining the time when the elastic waves arrive at the same depth in the imageable area of ​​the tissue surface.

[0063] In step S103, the propagation velocity of the elastic wave inside the transparent tissue is calculated according to the time difference to obtain the elastic modulus inside the transparent tissue.

[0064] It can be understood that Young's modulus is a physical quantity that describes the ability of solid materials to resist deformation, also known as tensile modulus. It means that within the elastic limit of the object, the stress and strain received by the object are proportional, and the ratio between them is called the Young's modulus of the material. As a physical quantity that characterizes the properties of a material, the size of the Young's modulus depends only on the physical properties of the object itself. The size of the Young's modulus indicates the elasticity of the material. The larger the Young's modulus, the less likely an object is to deform. Therefore, the characteristics of the elastic waves propagating in the lens can be measured and ultimately converted into the Young's modulus to characterize the tissue elasticity of the area.

[0065] According to step S102, the change in ultrasound focus depth is divided by the time difference of the elastic wave appearing on the lens surface, and the propagation speed of the elastic wave inside the lens can be obtained, and the elasticity inside the lens can be calculated. Figure 6 As shown:

[0066] Step S601: focusing the focus of the ultrasonic transducer inside the lens.

[0067] The coordinate positioning algorithm can be used to determine the ideal position coordinates of the target focal point inside the lens. The determination of the coordinates takes into account multiple factors such as the geometric center of the lens, the optical and acoustic properties of different areas, and subsequent measurement requirements.

[0068] Step S602: The elastic wave that propagates upward is marked as position 1.

[0069] When the focus of the ultrasonic transducer is successfully focused inside the lens and starts working, elastic waves are induced inside the lens. These elastic waves start from the focus of the ultrasonic transducer and propagate in all directions inside the lens. Among them, the upward propagating elastic waves need to be specially marked because their propagation direction is related to the direction of subsequent analysis and measurement.

[0070] Step S603: The ultrasonic transducer moves downward with a known step length.

[0071] The operation of moving the ultrasonic transducer downward with a known step length provides a reliable basis for the change of spatial coordinates for accurately measuring the propagation of elastic waves at different depths inside the lens.

[0072] Step S604: Use OCT to observe the time it takes for elastic waves generated at different depths to reach the lens surface.

[0073] Through detailed analysis of the light signal in the time dimension, the instant when the light signal changes due to the elastic wave reaching the surface of the lens can be accurately captured, thereby determining the exact time when the elastic wave propagates from different depths inside the lens to the surface.

[0074] Step S605: Calculate the elastic wave velocity by dividing the step length of the ultrasound focus downward movement by the time delay of the elastic wave reaching the lens surface, and analyze its elastic modulus.

[0075] The elastic wave velocity is calculated by dividing the step length of the ultrasound focus downward by the time delay from the elastic wave to the lens surface. Then, according to the formula related to the lens material and the known density, the velocity is substituted into the elastic modulus to calculate the elastic properties of the lens, providing a basis for the diagnosis and treatment of related diseases. The elastic wave velocity calculation formula is:

[0076]

[0077] Among them, V S is the velocity of elastic waves propagating between different excitation depths, ΔD is the depth difference of excitation sources at different depths inside the transparent tissue, and ΔT is the time difference for the elastic waves generated at different excitation depths to reach the same depth in the imageable area on the surface of the transparent tissue.

[0078] When the elastic wave inside the lens is a shear wave, according to the relationship between the shear modulus and Young's modulus, the relationship between the Young's modulus inside the lens and the shear wave velocity is as follows:

[0079]

[0080] In summary, the embodiments of the present application can use ARF-OCE to measure the elastic information inside the lens, thereby overcoming the transparent characteristic of the lens and successfully extending the biomechanical measurement of the lens to a place outside the OCT imaging range.

[0081] According to the method for measuring the elasticity of transparent biological tissue proposed in the embodiment of the present application, by exciting at different depths inside the transparent tissue and collecting M images at the same lateral position on the tissue surface, the elastic information of different layers inside the tissue can be comprehensively detected, breaking through the limitation that traditional methods can only obtain surface information; by comparing the time difference when elastic waves at different excitation depths reach the same depth on the tissue surface, a reliable basis is provided for accurately calculating the propagation speed of internal elastic waves, and then the elastic modulus inside the transparent tissue is accurately obtained, thereby realizing a quantitative evaluation of the elastic properties inside the transparent tissue, which helps to gain a deeper understanding of the mechanical state inside the transparent tissue and improve the accuracy and reliability of medical diagnosis results.

[0082] Next, a transparent biological tissue elasticity measuring device proposed in an embodiment of the present application will be described with reference to the accompanying drawings.

[0083] Figure 7 It is a block diagram of a device for measuring elasticity of transparent biological tissue according to an embodiment of the present application.

[0084] like Figure 7As shown, the transparent biological tissue elasticity measuring device 10 includes: a collection module 100 , a comparison module 200 and a calculation module 300 .

[0085] Specifically, the detection module 100 is used for collecting M-mode images at different excitation depths at the same lateral position on the tissue surface when an excitation source excites at different depths inside the transparent tissue.

[0086] The comparison module 200 is used to compare the time difference of the elastic waves generated at different excitation depths reaching the same depth in the imageable area of ​​the tissue surface based on the M-mode image.

[0087] The calculation module 300 is used to calculate the propagation speed of the elastic wave inside the transparent tissue according to the time difference to obtain the elastic modulus inside the transparent tissue.

[0088] Optionally, in one embodiment of the present application, the acquisition module 100 includes: a recording unit and a reconstruction unit.

[0089] The recording unit is used to record the scanning data along the depth direction at different times during each excitation process at the same lateral position.

[0090] The reconstruction unit is used to reconstruct a plurality of scanning data along the depth direction at the same lateral position into a time sequence diagram of the vibration signal at the lateral position changing with depth and time.

[0091] Optionally, in one embodiment of the present application, the calculation formula for the elastic wave propagation velocity inside the transparent tissue is:

[0092]

[0093] Among them, V S is the velocity of elastic waves propagating between different excitation depths, ΔD is the depth difference of excitation sources at different depths inside the transparent tissue, and ΔT is the time difference for the elastic waves generated at different excitation depths to reach the same depth in the imageable area on the surface of the transparent tissue.

[0094] Optionally, in one embodiment of the present application, the elastic modulus is obtained by calculating the propagation speed of the elastic wave.

[0095] It should be noted that the above explanations and descriptions of the embodiment of the method for measuring the elasticity of transparent biological tissue are also applicable to the device for measuring the elasticity of transparent biological tissue of this embodiment, and will not be repeated here.

[0096] According to the transparent biological tissue elasticity measurement device proposed in the embodiment of the present application, by exciting at different depths inside the transparent tissue and collecting M images at the same lateral position on the tissue surface, the elastic information of different layers inside the tissue can be comprehensively detected, breaking through the limitation that traditional methods can only obtain surface information; by comparing the time difference when elastic waves at different excitation depths reach the same depth on the tissue surface, a reliable basis is provided for accurately calculating the internal elastic wave propagation speed, and then the elastic modulus inside the transparent tissue is accurately obtained, thereby realizing a quantitative evaluation of the elastic properties inside the transparent tissue, which helps to gain a deeper understanding of the mechanical state inside the transparent tissue and improve the accuracy and reliability of medical diagnosis results.

[0097] Figure 8 A schematic diagram of the structure of an electronic device provided in an embodiment of the present application. The electronic device may include:

[0098] A memory 1001 , a processor 1002 , and a computer program stored in the memory 1001 and executable on the processor 1002 .

[0099] When the processor 1002 executes the program, the method for measuring the elasticity of transparent biological tissue provided in the above embodiment is implemented.

[0100] Furthermore, the electronic device further comprises:

[0101] The communication interface 1003 is used for communication between the memory 1001 and the processor 1002 .

[0102] The memory 1001 is used to store computer programs that can be executed on the processor 1002 .

[0103] The memory 1001 may include a high-speed RAM memory, and may also include a non-volatile memory (non-volatile memory), such as at least one disk memory.

[0104] If the memory 1001, the processor 1002 and the communication interface 1003 are implemented independently, the communication interface 1003, the memory 1001 and the processor 1002 can be connected to each other through a bus and communicate with each other. The bus can be an Industry Standard Architecture (ISA) bus, a Peripheral Component Interconnect (PCI) bus or an Extended Industry Standard Architecture (EISA) bus. The bus can be divided into an address bus, a data bus, a control bus, etc. For ease of representation, Figure 8Only one thick line is used in the diagram, but this does not mean that there is only one bus or only one type of bus.

[0105] Optionally, in a specific implementation, if the memory 1001, the processor 1002 and the communication interface 1003 are integrated on a chip, the memory 1001, the processor 1002 and the communication interface 1003 can communicate with each other through an internal interface.

[0106] The processor 1002 may be a central processing unit (CPU), or an application specific integrated circuit (ASIC), or one or more integrated circuits configured to implement the embodiments of the present application.

[0107] An embodiment of the present application also provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the above-mentioned method for measuring the elasticity of transparent biological tissue.

[0108] An embodiment of the present application also provides a computer program product, including a computer program, which, when executed, is used to implement the above-mentioned method for measuring the elasticity of transparent biological tissue.

[0109] In the description of this specification, the description with reference to the terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" etc. means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present application. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described may be combined in any one or N embodiments or examples in a suitable manner. In addition, those skilled in the art may combine and combine the different embodiments or examples described in this specification and the features of the different embodiments or examples, without contradiction.

[0110] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the features. In the description of this application, "N" means at least two, such as two, three, etc., unless otherwise clearly and specifically defined.

[0111] Any process or method description in a flowchart or otherwise described herein may be understood to represent a module, fragment or portion of code comprising one or N executable instructions for implementing the steps of a custom logical function or process, and the scope of the preferred embodiments of the present application includes alternative implementations in which functions may not be performed in the order shown or discussed, including performing functions in a substantially simultaneous manner or in reverse order depending on the functions involved, which should be understood by technicians in the technical field to which the embodiments of the present application belong.

[0112] The logic and / or steps represented in the flowchart or otherwise described herein, for example, can be considered as an ordered list of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by an instruction execution system, device or apparatus (such as a computer-based system, a system including a processor, or other system that can fetch instructions from an instruction execution system, device or apparatus and execute instructions), or in combination with these instruction execution systems, devices or apparatuses. For the purpose of this specification, "computer-readable medium" can be any device that can contain, store, communicate, propagate or transmit a program for use by an instruction execution system, device or apparatus, or in combination with these instruction execution systems, devices or apparatuses. More specific examples of computer-readable media (a non-exhaustive list) include the following: an electrical connection with one or N wirings (electronic devices), a portable computer disk box (magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable and programmable read-only memory (EPROM or flash memory), a fiber optic device, and a portable compact disk read-only memory (CDROM). In addition, the computer-readable medium may even be paper or other suitable medium on which the program is printed, since the program may be obtained electronically by optically scanning the paper or other medium and then editing, interpreting or processing in other suitable ways as necessary and then storing it in a computer memory.

[0113] It should be understood that the various parts of the present application can be implemented by hardware, software, firmware or a combination thereof. In the above embodiment, the N steps or methods can be implemented by software or firmware stored in a memory and executed by a suitable instruction execution system. If implemented by hardware, as in another embodiment, it can be implemented by any one or a combination of multiple of the following technologies known in the art: a discrete logic circuit having a logic gate circuit for implementing a logic function for a data signal, a dedicated integrated circuit having a suitable combination of logic gate circuits, a programmable gate array (PGA), a field programmable gate array (FPGA), etc.

[0114] A person skilled in the art may understand that all or part of the steps in the method for implementing the above-mentioned embodiment may be completed by instructing related hardware through a program, and the program may be stored in a computer-readable storage medium, which, when executed, includes one or a combination of the steps of the method embodiment.

[0115] In addition, each functional unit in each embodiment of the present application may be integrated into a processing module, or each unit may exist physically separately, or two or more units may be integrated into one module. The above-mentioned integrated module may be implemented in the form of hardware or in the form of a software functional module. If the integrated module is implemented in the form of a software functional module and sold or used as an independent product, it may also be stored in a computer-readable storage medium.

[0116] The storage medium mentioned above may be a read-only memory, a disk or an optical disk, etc. Although the embodiments of the present application have been shown and described above, it can be understood that the above embodiments are exemplary and cannot be understood as limiting the present application. A person of ordinary skill in the art may change, modify, replace and modify the above embodiments within the scope of the present application.

Claims

1. A method for measuring the internal elasticity of a transparent biological tissue, characterized in that: include: Based on the excitation source stimulating at different depths inside the transparent tissue, M-mode images at different excitation depths are collected at the same lateral position on the tissue surface; Based on the M-mode image, comparing the time difference of the elastic waves generated at different excitation depths reaching the same depth in the imageable area of ​​the tissue surface; The propagation velocity of the elastic wave inside the transparent tissue is calculated according to the time difference to obtain the elastic modulus inside the transparent tissue.

2. The method according to claim 1, characterized in that The M-mode images acquired at different excitation depths at the same lateral position on the tissue surface include: Recording scanning data along the depth direction at different times during each excitation process at the same lateral position; A plurality of scanning data along the depth direction at the same lateral position are reconstructed into a time sequence diagram of the vibration signal at the lateral position changing with depth and time.

3. The method according to claim 1, characterized in that: The calculation formula for the elastic wave propagation velocity inside the transparent tissue is: Among them, V S is the velocity of elastic waves propagating between different excitation depths, ΔD is the depth difference of excitation sources at different depths inside the transparent tissue, and ΔT is the time difference for the elastic waves generated at different excitation depths to reach the same depth in the imageable area on the surface of the transparent tissue.

4. The method according to claim 1, characterized in that: The elastic modulus is calculated by the propagation speed of the elastic wave.

5. A device for measuring elasticity of transparent biological tissue, characterized in that: include: An acquisition module, used for acquiring M-mode images at different excitation depths at the same lateral position on the tissue surface when the excitation source excites at different depths inside the transparent tissue; A comparison module, for comparing the time difference of elastic waves generated at different excitation depths reaching the same depth in the imageable area of ​​the tissue surface based on the M-mode image; A calculation module is used to calculate the propagation speed of the elastic wave inside the transparent tissue according to the time difference to obtain the elastic modulus inside the transparent tissue.

6. The device according to claim 5, characterized in that The acquisition module comprises: A recording unit, used for recording the scanning data along the depth direction at different times during each excitation process at the same lateral position; The reconstruction unit is used to reconstruct a plurality of scanning data along the depth direction at the same lateral position into a time sequence diagram of the vibration signal at the lateral position changing with depth and time.

7. The device according to claim 6, characterized in that The elastic modulus is calculated by the propagation speed of the elastic wave.

8. An electronic device, characterized in that: include: A memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the method for measuring the elasticity of transparent biological tissue as described in any one of claims 1 to 4.

9. A computer-readable storage medium having a computer program stored thereon, characterized in that: The program is executed by a processor to implement the method for measuring the elasticity of transparent biological tissue as described in any one of claims 1 to 4.

10. A computer program product, comprising a computer program, characterized in that The computer program is executed to implement the method for measuring elasticity of transparent biological tissue according to any one of claims 1 to 4.

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