CN111449629A - Optical coherence elastography method and device - Google Patents

Optical coherence elastography method and device Download PDF

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CN111449629A
CN111449629A CN202010348860.XA CN202010348860A CN111449629A CN 111449629 A CN111449629 A CN 111449629A CN 202010348860 A CN202010348860 A CN 202010348860A CN 111449629 A CN111449629 A CN 111449629A
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elastic wave
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CN111449629B (en
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朱疆
樊凡
祝连庆
杨强
王重阳
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Beijing Information Science and Technology University
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4488—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer the transducer being a phased array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/488—Diagnostic techniques involving Doppler signals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/84—Systems specially adapted for particular applications
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/04—Analysing solids
    • G01N29/041—Analysing solids on the surface of the material, e.g. using Lamb, Rayleigh or shear waves

Abstract

The application discloses an optical coherence elastography method and device, wherein the optical coherence elastography method utilizes ultrasonic beams to induce a sample to be detected to generate a first elastic wave and a second elastic wave which are vertical to each other in a propagation direction, so that when the first elastic wave and the second elastic wave are imaged by an optical coherence tomography method, an imaging result containing elastic information in a first direction and a second direction can be obtained, the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction can be obtained according to the imaging result, the purpose of measuring the axial elastic information and the lateral elastic information of the sample to be detected is achieved, and the purpose of comprehensively and accurately evaluating the anisotropic elastic characteristics of the sample to be detected is achieved.

Description

Optical coherence elastography method and device
Technical Field
The present application relates to the field of imaging technologies, and in particular, to an optical coherence elastography method and apparatus.
Background
The elastic mechanical property difference of the biological tissue comes from different components, structures and interactions of biomolecules, cells and sample levels, and the elasticity measurement of the biological tissue has important significance for evaluating the physiological function of the sample and can be used for diagnosing diseases of eyeball, cardiovascular, mammary gland, liver and other parts. Age-related macular degeneration (AMD), a degenerative change of pigment epithelium in macular region, is one of the main causes of irreversible blindness in people over 60 years old. The retinal elasticity measurement can be used for risk assessment and early diagnosis of wet AMD to realize early intervention and treatment, thereby delaying disease progression and improving treatment effect, and has important clinical application value.
The mainstream method for measuring elasticity of biological tissue at present is Optical Coherence Elastography (OCE), which is an imaging mode for analyzing biomechanical parameters (such as shear modulus and young's modulus) of biological tissue based on an Optical Coherence Tomography (OCT) platform and an elasticity measurement principle. Optical Coherence Tomography (OCT) is a non-invasive, high-resolution, three-dimensional medical imaging technique with spatial resolution up to about 10 μm, biological tissue imaging depth of 2-3mm, and imaging field of view up to about 1cm, and can be used for structural imaging, angiographic imaging, and elastography of biological tissue, in combination with different computational methods and measurement principles.
However, in the prior art, when a biological tissue is imaged by using an ultrasonic acoustic beam induced optical coherence elastography method, only lateral elasticity information of the measured biological tissue perpendicular to the direction of the external acting force can be obtained, but axial elasticity information of the measured biological tissue parallel to the direction of the external acting force cannot be obtained, so that the anisotropic elasticity characteristics of the biological tissue cannot be comprehensively and accurately evaluated.
Disclosure of Invention
In order to solve the technical problems, the application provides an optical coherence elastography method and an optical coherence elastography device, so as to achieve the purpose of measuring the axial and lateral elasticity information of a measured sample and achieve the purpose of comprehensively and accurately evaluating the anisotropic elasticity characteristics of the measured sample.
In order to achieve the technical purpose, the embodiment of the application provides the following technical scheme:
an optical coherence elastography method, comprising:
inducing a sample to be detected by using an ultrasonic sound beam to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is vertical to the second direction;
and imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
Optionally, the inducing, by using an ultrasonic sound beam, a sample to be measured to generate a first elastic wave and a second elastic wave includes:
and forming a multipoint vibration source in the sample to be detected by using the plurality of ultrasonic sound beams, wherein the multipoint vibration source induces the surface and/or the interior of the sample to be detected to generate the first elastic wave and the second elastic wave.
Optionally, when the first elastic wave and the second elastic wave are located on the surface of the sample to be measured, the first elastic wave and the second elastic wave are respectively a surface rayleigh wave and a longitudinal shear wave.
Optionally, when the first elastic wave and the second elastic wave are located inside the sample to be measured, the first elastic wave and the second elastic wave are a longitudinal shear wave and a transverse shear wave, respectively.
Optionally, the imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and acquiring the elastic information of the sample to be measured in the first direction and the elastic information of the sample to be measured in the second direction according to the imaging result includes:
imaging the first elastic wave and the second elastic wave on the surface of the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result;
and imaging the first elastic wave and the second elastic wave in the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result.
An optical coherent elastography system, comprising: an imaging unit and an acoustic radiation force excitation unit; wherein the content of the first and second substances,
the acoustic radiation force excitation unit is used for forming a plurality of ultrasonic sound beams and transmitting the ultrasonic sound beams to a sample to be detected so that the ultrasonic sound beams induce the sample to be detected to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is perpendicular to the second direction;
the imaging unit is used for transmitting the detection light beam to the sample to be detected, receiving the detection light beam reflected and scattered by the sample to be detected, imaging the first elastic wave and the second elastic wave according to the reflected and scattered detection light beam by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
Optionally, the method further includes: a coupling unit;
the coupling unit includes an acoustic reflection surface having an optical transparency characteristic and an acoustic reflection characteristic, and a light incident surface;
the probe beam is incident through the light incidence surface and is transmitted to a sample to be detected through the acoustic reflection surface, and the ultrasonic acoustic beam is transmitted to the sample to be detected along the same direction or the similar direction after being reflected by the acoustic reflection surface.
Optionally, the coupling unit includes: a first dielectric structure, an intermediate dielectric structure, and a second dielectric structure; wherein the content of the first and second substances,
the intermediate dielectric structure is disposed between the first dielectric structure and the second dielectric structure, the first dielectric structure including the light entrance face;
the second medium structure comprises an acoustic incidence surface, and the contact surface of the intermediate medium structure and the second medium structure is the acoustic reflection surface.
Optionally, a difference between the optical refractive index of the first dielectric structure, the optical refractive index of the second dielectric structure, and the optical refractive index of the intermediate dielectric structure is smaller than a first preset difference;
and the difference value of the acoustic impedance of the second dielectric structure and the acoustic impedance of the middle dielectric structure is larger than a second preset difference value.
Optionally, the first medium structure and the second medium structure are both prisms, and the intermediate medium structure is a silicon oil layer or a water layer;
or
The first medium structure and the second medium structure are both a silicon oil layer or a water layer or a phosphate buffer salt solution layer or a physiological salt solution layer, and the middle medium structure is a glass layer.
It can be seen from the foregoing technical solutions that, in the optical coherence elastography method, an ultrasonic beam is used to induce a to-be-detected sample to generate a first elastic wave and a second elastic wave with perpendicular propagation directions, so that when an optical coherence tomography method is used to image the first elastic wave and the second elastic wave, an imaging result including elastic information in both a first direction and a second direction can be obtained, and thus the elastic information of the to-be-detected sample in the first direction and the elastic information of the to-be-detected sample in the second direction can be obtained according to the imaging result, so as to achieve a purpose of measuring axial and lateral elastic information of the to-be-detected sample, and achieve a purpose of comprehensively and accurately evaluating an anisotropic elastic characteristic of the to-be-detected sample.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly introduced below, it is obvious that the drawings in the following description are only embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the provided drawings without creative efforts.
FIG. 1 is a schematic diagram of a measurement principle of optical coherence elastography in the prior art;
FIG. 2 is a schematic flow chart of a method of optical coherence elastography provided in an embodiment of the present application;
FIG. 3 is a schematic diagram of an array layout of an array type ultrasonic transducer;
FIG. 4 is a schematic diagram of two point vibration sources acting inside a sample to be measured to induce compressional waves and shear waves;
FIG. 5 is a schematic diagram of induced compressional waves and shear waves when two point vibration sources act on the surface of a sample to be measured;
FIG. 6 is a schematic diagram of M-B scanning;
FIG. 7 is a schematic diagram of an optical coherence elastography system provided in an embodiment of the present application;
fig. 8 is a schematic structural diagram of an imaging unit according to an embodiment of the present application;
fig. 9 is a schematic structural view of an imaging unit according to another embodiment of the present application;
fig. 10 is a schematic structural diagram of an imaging unit according to still another embodiment of the present application;
FIG. 11 is a schematic diagram of an acoustic radiation force excitation unit according to an embodiment of the present application;
fig. 12 is a schematic structural diagram of a coupling unit according to an embodiment of the present application;
fig. 13 is a schematic structural diagram of a coupling unit according to another embodiment of the present application;
fig. 14 is a schematic structural diagram of a coupling unit according to still another embodiment of the present application.
Detailed Description
As described in the background art, when the ultrasound beam induced optical coherence elastography method in the prior art images a biological tissue, only the lateral elasticity information of the measured biological tissue perpendicular to the direction of the external acting force can be obtained, but the axial elasticity information of the measured biological tissue parallel to the direction of the external acting force cannot be obtained, and the specific reason is explained below.
When the elasticity of biological tissues is measured, firstly, an external force is used for inducing elastic waves in the tissues, then, the propagation of the elastic waves is detected through an imaging platform, and finally, the elastic modulus in the propagation direction of the elastic waves is calculated according to the propagation speed of the elastic waves. Therefore, in the elastic measurement of anisotropic biological tissues, the construction of an elastic wave imaging platform is the basis of the measurement, and the simultaneous induction of elastic waves propagating along the axial direction of the external force and perpendicular to the lateral direction of the external force is the key of the measurement.
In the prior art, referring to fig. 1, during imaging, an ultrasonic beam is used to induce a sample to be measured to generate micro vibration, and after measuring the vibration amplitude of the sample by an OCT imaging technique, propagation of an elastic wave is reconstructed, the propagation velocity of the elastic wave is calculated, and the elastomechanical property of the sample to be measured in the propagation direction of the elastic wave is analyzed. In fig. 1, a transverse shear wave is induced using an acoustic radiation force, and the propagation direction of the transverse shear wave is perpendicular to the vibration direction. Because, through the wave velocity measurement of the transverse shear wave, the analysis of the lateral elastic information of the vertical external force in the sample can be realized. In fig. 1, the OCT converging lens is a component of the optical coherence tomography unit, and the OCT incident beam is a probe beam emitted from the optical coherence tomography unit.
Conventional OCE techniques rely on the detection of transverse shear waves and surface Rayleigh waves, which propagate perpendicular to the direction of the external force, and only measure the lateral (perpendicular to the external force) modulus of elasticity. Although the compression wave is a longitudinal wave, and the propagation direction of the compression wave is parallel to the direction of the external force, the propagation speed of the compression wave in the biological tissue is too fast (about 1500m/s), and the current OCT technology cannot capture the propagation process of the compression wave and calculate the propagation speed of the compression wave due to the limitation of the imaging frame rate. Therefore, in most studies, biological tissues are assumed to be isotropic materials, and only the lateral elastic modulus is measured to characterize the elastic properties of the biological tissues in all directions, and the axial elastic modulus cannot be measured, so that the anisotropic elastic characteristics of the sample cannot be comprehensively and accurately evaluated.
In view of this, an embodiment of the present application provides an optical coherence elastography method, including:
inducing a sample to be detected by using an ultrasonic sound beam to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is vertical to the second direction;
and imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
The optical coherence elastography method induces a sample to be detected to generate a first elastic wave and a second elastic wave which are vertical to the propagation direction by using an ultrasonic sound beam, so that when the first elastic wave and the second elastic wave are imaged by using the optical coherence tomography method, an imaging result containing elastic information in the first direction and the second direction can be obtained, the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction can be obtained according to the imaging result, the purpose of measuring the axial elastic information and the lateral elastic information of the sample to be detected is realized, and the purpose of comprehensively and accurately evaluating the anisotropic elastic characteristics of the sample to be detected is realized.
The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
The embodiment of the present application provides an optical coherence elastography method, as shown in fig. 2, including:
s101: inducing a sample to be detected by using an ultrasonic sound beam to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is vertical to the second direction;
s102: and imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
In step S101 of this embodiment, the first direction and the second direction are two directions perpendicular to each other, and in general, the first direction and the second direction may be an axial direction and a lateral direction, respectively, and further, the axial direction refers to a direction parallel to the external acting force, and the lateral direction refers to a direction perpendicular to the external acting force.
In step S101, the elastic waves of the sample to be measured in the first direction and the elastic waves of the sample to be measured in the second direction may be induced by forming vibration sources at multiple points in the sample to be measured.
Specifically, one possible implementation of step S101 includes:
s1011: and forming a multipoint vibration source in the sample to be detected by using the plurality of ultrasonic sound beams, wherein the multipoint vibration source induces the surface and/or the interior of the sample to be detected to generate the first elastic wave and the second elastic wave.
When a plurality of ultrasonic sound beams generated by equipment such as an acoustic radiation force excitation unit are incident on a sample to be tested, the ultrasonic sound beams generate multipoint mechanical drive in the sample to be tested to form a multipoint vibration source.
The array form of the array type ultrasonic transducer is shown in fig. 3, for example, the array type ultrasonic transducer comprises 8 × 8 array elements, each array element is an ultrasonic transducer, the distance between the centers of the array elements is 1.5mm, the effective area array size of the ultrasonic transducer is 10.5 × 10.5.5 mm, the subsequent parameter design such as the number of the array elements and the distance is optimized according to the theoretical analysis of elastic waves and the regulation and control method of the array elements, the acoustic radiation force is the interaction between acoustic waves and obstacles on the transmission path of the acoustic radiation force, and the amplitude of the acoustic radiation force | F | at a given position in space can be evaluated by the following formula:
Figure BDA0002471144790000071
wherein α represents the attenuation coefficient of ultrasound in tissue, which is related to the ultrasound frequency, I represents the average intensity of the sound beam at the position to be measured, which is related to the sound field of the ultrasound transducer, and c represents the propagation speed of ultrasound in tissue.
When two point sources are simultaneously applied to tissue, each point source independently induces compressional and shear waves within the tissue. Classical compressional waves are longitudinal waves, with a direction of propagation parallel to the direction of vibration, while shear waves are transverse waves, with a direction of propagation perpendicular to the direction of vibration. In fig. 4, thin dashed arrows indicate the propagation direction of transverse shear waves induced by the point sources, thin solid arrows indicate the direction of vibration, dashed circles indicate the position of the wave surface at this moment, and line segments on the left and right indicate that they are from two different point sources, respectively. Where two transverse shear waves merge, a shear wave whose vibration direction is parallel to the propagation direction is generated by the superposition of the waves, and is therefore referred to as a longitudinal shear wave.
When a point source is located inside the sample to be measured, each point source induces compressional and shear waves inside the tissue, as shown in fig. 4. At the place where the transverse shear waves induced by the two point vibration sources are converged, longitudinal shear waves with vibration directions parallel to the propagation direction are generated due to the superposition of the waves and are respectively propagated up and down to the vibration sources. Meanwhile, transverse shear waves perpendicular to the vibration direction of the vibration source are generated and spread to the two sides of the vibration source. Namely, when the first elastic wave and the second elastic wave are located inside the sample to be measured, the first elastic wave and the second elastic wave are respectively longitudinal shear wave and transverse shear wave.
When the point vibration source is located on the surface of the sample to be measured, the surface rayleigh waves induced by the point vibration source are transmitted to two sides of the vibration source, the transmission direction is vertical to the direction of the external force, and the transmission depth is within the range of about 1 wavelength from the surface of the tissue, as shown in fig. 5. Meanwhile, the point vibration source induces longitudinal shear waves and compression waves on the surface layer of the tissue, and the longitudinal shear waves and the compression waves are transmitted along the axial direction of the external force. Namely, when the first elastic wave and the second elastic wave are positioned on the surface of the sample to be measured, the first elastic wave and the second elastic wave are respectively a surface rayleigh wave and a longitudinal shear wave. The tissue in fig. 4 and 5 is the sample to be tested.
Correspondingly, step S102 specifically includes:
s1021: imaging the first elastic wave and the second elastic wave on the surface of the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result;
s1022: and imaging the first elastic wave and the second elastic wave in the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result.
The following describes an elastic wave reconstruction process in the optical coherence tomography process.
In order to capture fast-propagating elastic waves at the maximum frame rate, an OCT (Optical coherence tomography) data acquisition method based on M-B scanning may be employed, the principle of which is shown in fig. 6. The B-scan is an "anatomical image" (i.e. OCT B-mode image) that combines a plurality of processed signal lines in the depth direction, which are spatially arranged side by side, into a two-dimensional plane and reflects a tomographic section inside the object to be measured. M-scan refers to sampling multiple times at the same lateral position of the sample, and spreading out the sampled signal lines in time sequence to form a one-dimensional timing chart (i.e., an OCT M-mode image). During the repeated ultrasonic induced elastic wave process, the OCT unit collects 1M-mode time sequence chart at each lateral position, and then reconstructs the M-mode time sequence charts of different lateral positions into a B-mode two-dimensional plane image which changes along with time. For example, in a system using a 100kHz swept source, the frame rate of elastic wave imaging by M-B scanning can be maximized at about 100000 frames/sec.
In order to detect the micro-vibration in the sample to be detected with high sensitivity by using the OCT unit and realize the propagation imaging of the weak-amplitude elastic wave, a vibration measuring method based on phase analysis can be adopted. First, an interference signal collected by the OCT unit, which varies with wavelength, is transformed into a complex signal, which varies with depth, by Fast Fourier Transform (FFT), and the complex signal is band-pass filtered to remove low-frequency noise. OCT complex signals
Figure BDA0002471144790000091
Comprising an amplitude A (x, y, z, t) component and a phase
Figure BDA0002471144790000092
Where (x, y, z) represents the spatial position of the scan and t represents the sampling instant. The change in phase of the OCT signal can be used to calculate the vibrational velocity and displacement of scattering particles in the sample according to the Doppler (Doppler) principle. Velocity V and OCT phase variation of scattering particles in sample within time interval Delta T
Figure BDA0002471144790000093
The relationship is as follows:
Figure BDA0002471144790000094
where n denotes the optical refractive index of the sample, λ denotes the central wavelength of the light in vacuum, θ denotes the angle between the particle motion direction and the probe beam, V × cos (θ) denotes the velocity component of the particle in the probe beam direction, the phase change
Figure BDA0002471144790000095
Can be calculated from the OCT complex signal as follows:
Figure BDA0002471144790000096
wherein, Fx，y，z，tAnd Fx，y，z，t+1Respectively representing the OCT complex signal at the same position (lateral position x, y and depth position z) at different instants (instants T and T + 1), the time interval at instants T and T +1 being Δ T.
Calculation of the modulus of elasticity:
after measuring the propagation velocities of the longitudinal shear wave, the transverse shear wave and the surface rayleigh wave, we will calculate the young's modulus in the propagation direction of the elastic wave. The relationship between the propagation velocity of the transverse shear wave and the Young's modulus E can be expressed using the following equation:
Figure BDA0002471144790000101
where ρ represents the sample density, VShearRepresents the propagation velocity of a transverse shear wave, and v represents the poisson's ratio of biological tissue. The density rho of the incompressible biological soft sample is 1000kg/m3The poisson's ratio v of biological tissue is about 0.5.
Since the formation of the longitudinal shear wave results from the superposition of the transverse shear waves, the relationship between the propagation velocity of the longitudinal shear wave and the young's modulus can also be expressed using the above formula, and thus after the propagation velocity of the longitudinal shear wave is measured, the young's modulus in the axial direction can be calculated using the above.
The surface rayleigh wave typically propagates in a range of about 1 wavelength from the surface, and therefore, the lateral young's modulus near the surface of the sample can be measured by the rayleigh wave by the calculation method shown below:
Figure BDA0002471144790000102
wherein, VRayleighRepresenting the propagation velocity of the rayleigh wave.
The following describes an optical coherent elastography system provided in an embodiment of the present application, and the optical coherent elastography system described below may be referred to in correspondence with the optical coherent elastography method described above.
Accordingly, an embodiment of the present application provides an optical coherent elastography system, as shown in fig. 7, including: an imaging unit 100 and an acoustic radiation force excitation unit 200; wherein the content of the first and second substances,
the acoustic radiation force excitation unit 200 is configured to form a plurality of ultrasonic sound beams and transmit the ultrasonic sound beams to a sample a10 to be measured, so that the plurality of ultrasonic sound beams induce the sample a10 to be measured to generate a first elastic wave and a second elastic wave, where a propagation direction of the first elastic wave is a first direction, a propagation direction of the second elastic wave is a second direction, and the first direction is perpendicular to the second direction;
the imaging unit 100 is configured to transmit a probe beam to the sample a10 to be detected, receive a probe beam reflected by the sample a10 to be detected, image the first elastic wave and the second elastic wave according to the reflected probe beam by using an optical coherence tomography method, and obtain elastic information of the sample to be detected in a first direction and elastic information of the sample to be detected in a second direction according to an imaging result.
Optionally, still referring to fig. 7, the optical coherence elastography system further comprises: a coupling unit 300;
the coupling unit 300 includes an acoustic reflection surface having an optical transparency characteristic and an acoustic reflection characteristic, and a light incident surface;
the detection light beam enters through the light incidence surface and is transmitted to a sample to be detected through the acoustic reflection surface, and after the detection light beam is reflected and scattered by the sample, the detection light beam returns to an imaging light path through the acoustic reflection surface; and after being reflected by the sound reflection surface, the ultrasonic sound beam and the detection light beam are transmitted to the sample to be detected along the same direction or the similar direction.
Alternatively, referring to fig. 8, the imaging unit 100 includes: light source 110, optical coupler 150, reference arm 120, sample arm 140, and imaging device 130; wherein the content of the first and second substances,
the light source 110 is used for providing light to be processed;
the optical coupler 150 is used for dividing the light to be processed into a reference beam and a probe beam, and for receiving the reference beam reflected by the reference arm 120 and the probe beam reflected and scattered by the sample to be measured A10; the reference beam reflected by the reference arm 120 and the probe beam reflected and scattered by the sample to be measured a10 interfere in the optical coupler 150;
the imaging device 130 is used for performing structural imaging and vibration measurement on the sample A10 to be measured according to the interference signal.
The imaging unit 100 may be an optical coherence tomography unit 100 based on a swept-source 111, or an optical coherence tomography unit 100 based on a continuous-spectrum light source 113, that is, optionally, the light source 110 is a swept-source 111 unit or a continuous-spectrum light source 113 unit.
Referring to fig. 9 and 10, fig. 9 is a schematic structural diagram of the optical coherence tomography unit 100 based on the swept-frequency light source 111, and fig. 10 is a schematic structural diagram of the optical coherence tomography unit 100 based on the continuous-spectrum light source 113.
In the configuration shown in fig. 9, the light to be processed (usually weak coherent light) output from the swept-frequency laser source 111 passes through the polarization controller 112 and then enters the optical coupler 150 for light splitting, a part of the light to be processed enters the reference arm 120 as a reference beam, and a part of the light to be processed enters the sample arm 140 as a probe beam. The reference beam passes through a lens 121 of the reference arm 120 and is reflected by a mirror 122. The probe beam passes through the lens 141 of the sample arm 140 and is focused on the sample a10 to be measured. The scattered light (i.e. the probe beam reflected and scattered by the sample a 10) and the reflected light (i.e. the reference beam reflected by the mirror) returned by the sample arm 140 and the reference arm 120 interfere in the optical coupler 150, and after being detected 131 by the photodetector and processed by the signal processing, the structural imaging and vibration measurement of the sample a10 are realized.
In the configuration shown in fig. 10, after passing through the optical isolator 114, the light to be processed output from the continuous spectrum light source 113 is split by the optical coupler 150, and a part of the light enters the sample arm 140 as a probe beam and another part of the light enters the reference arm 120 as a reference beam. The reference beam passes through the polarization controller and the lens 121, and is reflected by the mirror 122. The probe beam passes through the polarization controller and the lens 141 and is focused on the sample a10 to be measured. The scattered light (i.e. the probe beam reflected and scattered by the sample a10 to be measured) and the reflected light (i.e. the reference beam reflected by the mirror) returned by the sample arm 140 and the reference arm 120 interfere in the optical coupler 150, the interference signal is split by the grating 133 after passing through the converging lens 132, the interference light with different wavelengths is spatially separated, and is subjected to photoelectric conversion on the camera 135 after passing through another converging lens 134 again, and the signal on the camera 135 is processed to realize structural imaging and vibration measurement of the sample a10 to be measured.
Referring to fig. 11 for the acoustic radiation force exciting unit 200, fig. 11 shows a structure of a possible acoustic radiation force exciting unit 200, the acoustic radiation force exciting unit 200 including: a waveform generator 210, an amplifier 220, and an ultrasonic transduction unit;
the ultrasonic transduction unit is an ultrasonic transducer 230 or an ultrasonic transducer 230 array.
The waveform generator 210 generates a high-frequency sine wave, a square wave or a triangular wave according to the control information of the upper computer, and the high-frequency sine wave, the square wave or the triangular wave is amplified by the amplifier 220 to drive the ultrasonic transducer 230 to work, so that the remote mechanical excitation of the sample A10 to be detected is realized. The ultrasonic beam output by the ultrasonic transducer 230 enters the sample a10 to be measured through the ultrasonic coupling material (water or ultrasonic glue), and forms an acoustic radiation force field on the sample a10 to induce the micro-vibration of the tissue. The acoustic radiation force has the advantages of being non-invasive, non-contact, remotely focused and the like.
Still referring to fig. 7, the coordinate system in fig. 7 is an XZ coordinate system established with the propagation direction of the probe beam emitted from the imaging unit 100 as the Z axis and the direction perpendicular to the Z axis and parallel to the paper as the X axis. . In the structure shown in fig. 7, the propagation direction of the probe beam emitted from the imaging unit 100 is parallel to the Z axis, the propagation direction of the ultrasonic beam formed by the acoustic radiation force excitation unit 200 is parallel to the X axis, the light incident surface is optionally perpendicular to the Z axis, so that the probe beam can directly enter the light incident surface perpendicularly without changing the beam propagation direction, and the normal direction of the acoustic reflection surface is optionally parallel to the XZ plane and is disposed at an angle, which is optionally equal to 45 °, with respect to the ultrasonic beam, so that the ultrasonic beam can enter the sample a10 to be measured in a parallel manner with the probe beam after being reflected by the acoustic reflection surface.
The mode that the ultrasonic sound beam and the detection light beam are incident in parallel can directly induce the elastic vibration parallel to the direction of the detection light beam, and compared with the mode that the ultrasonic sound beam is excited in oblique incidence, the sensitivity of the system to vibration detection is improved. Compared with the mode of back incidence or orthogonal incidence, the mode of parallel incidence of the ultrasonic sound beam and the probe beam can be conveniently applied to clinical detection (such as fundus tissue elastography).
A possible structure of the coupling unit 300 in the optical coherence elastography device provided in the embodiment of the present application is specifically described below.
On the basis of the above embodiments, in an embodiment of the present application, the coupling unit 300 includes: a first dielectric structure 310, an intermediate dielectric structure 330, and a second dielectric structure 320; wherein the content of the first and second substances,
the intermediate media construction 330 is disposed between the first media construction 310 and the second media construction 320, the first media construction 310 including a light entrance face;
the second dielectric structure 320 includes an acoustic incident surface, and the contact surface between the intermediate dielectric structure 330 and the second dielectric structure 320 is the acoustic reflection surface.
The difference between the optical refractive index of the first dielectric structure 310, the optical refractive index of the second dielectric structure 320 and the optical refractive index of the intermediate dielectric structure 330 is smaller than a first preset difference;
the difference between the acoustic impedance of the second dielectric structure 320 and the acoustic impedance of the intermediate dielectric structure 330 is greater than a second predetermined difference.
In this embodiment, the coupling unit 300 is a "sandwich structure" in which the intermediate medium structure 330 is sandwiched between the first medium structure 310 and the second medium structure 320, wherein the difference between the optical refractive indexes of the first medium structure 310, the second medium structure 320 and the intermediate medium structure 330 is smaller than a first preset difference, that is, the optical refractive indexes of the first medium structure 310, the second medium structure 320 and the intermediate medium structure 330 are matched, so that the whole coupling unit 300 is optically transparent to the detection beam, the detection beam is not excessively reflected, and the loss of the detection beam through the coupling unit 300 is reduced;
however, a large acoustic impedance mismatch exists between the intermediate medium structure 330 and the second medium structure 320, so that the intermediate medium structure 330 can cooperate with the second medium structure 320 to form the acoustic reflection surface, thereby realizing the transparency of the probe beam and the reflection of the ultrasonic acoustic beam.
Optionally, referring to fig. 12, the first dielectric structure 310 and the second dielectric structure 320 are prisms;
the intermediate dielectric structure 330 is a silicon oil layer or a water layer.
Specifically, in one embodiment of the present application, the first dielectric structure 310 and the second dielectric structure 320 are prisms, the intermediate dielectric structure 330 is a silicone oil layer, and the coupling unit 300 is a prism-silicone oil-prism structure, the gap between the two prisms is about 0.1-1mm, and the silicone oil layer is formed by filling the gap with silicone oil having optical refractive index matching, lower acoustic impedance, and non-volatility, and the silicone oil and the glass have good optical refractive index matching (the optical refractive index of the silicone oil is 1.4, and the optical refractive index of the glass is about 1.5), but have large mismatch (the acoustic impedance of the silicone oil is 0.74 × 10)5g/(cm2S), the acoustic impedance of the glass is 12.1 × 105g/(cm2S)), the silicone oil layer is thus optically transparent, but can act as an ultrasound reflector.
In fig. 12, since the frequency of the ultrasonic sound beam is generally above 1MHz and cannot propagate in air, in order to enable the ultrasonic sound beam to enter the coupling unit 300, a transparent ultrasonic couplant 240 is filled between the coupling unit 300 and the acoustic radiation force excitation unit 200, and an ultrasonic couplant 240 (water or ultrasonic gel) is filled between the coupling unit 300 and the sample a10 to be measured, and the purpose of filling the ultrasonic couplant 240 in these gaps is to provide a propagation medium of the ultrasonic sound beam.
Referring to fig. 13, optionally, the first dielectric structure 310 and the second dielectric structure 320 are both a silicon oil layer or a water layer or a phosphate buffer saline solution layer or a physiological saline layer;
the intermediate dielectric structure 330 is a glass layer.
In the structure shown in fig. 13, the intermediate dielectric structure 330 is a glass layer, and the first dielectric structure 310 and the second dielectric structure 320 are both material layers that are optically index-matched to the glass layer and have lower acoustic impedance. Specifically, in one embodiment of the present application, the first dielectric structure 310 and the second dielectric structure 320 are both water placed in a water tank, the intermediate dielectric structure 330 is a glass layer inserted into the water tank, and in this case, the coupling unit 300 is a water-glass-water structure, and the contact surface of the glass layer and the water is used as the sound reflection surface.
On the basis of the above embodiments, another embodiment of the present application provides another possible structure of the coupling unit 300.
Referring to fig. 14, the coupling unit 300 includes: a third dielectric structure 340 and an impedance mismatch film 350;
the third medium structure 340 comprises an acoustic incidence surface and an attachment surface forming a preset angle with the transmission direction of the ultrasonic sound beam;
the mismatch impedance film 350 is attached to the attachment surface.
Wherein the difference between the optical refractive index of the third dielectric structure 340 and the optical refractive index of the impedance mismatch film 350 is smaller than a first preset difference;
the difference between the acoustic impedance of the third dielectric structure 340 and the acoustic impedance of the impedance mismatch film 350 is greater than a second predetermined difference.
That is, the third dielectric structure 340 and the impedance-mismatched film 350 are matched in optical refractive index and are mismatched in acoustic impedance so that the coupling unit 300 formed by the impedance-mismatched film 350 and the third dielectric structure 340 has the property of being optically transparent, and the impedance-mismatched film 350 and the third dielectric structure 340 form an acoustic reflection surface capable of reflecting an ultrasonic beam.
In this embodiment, when the probe beam is incident from the upper side of the impedance matching film 350 and an ultrasonic sound beam is incident from the left side of the third dielectric structure 340, the contact surface of the impedance mismatching film 350 and the third dielectric structure 340 is the sound reflection surface.
As mentioned above, the preset angle refers to an angle parallel or approximately parallel to the probe beam after reflecting the ultrasonic sound beam, and for example, when the probe beam is parallel to the Z axis and the ultrasonic sound beam is parallel to the X axis, the preset angle may be about 45 °.
In summary, the embodiment of the present application provides an optical coherence elastography method and apparatus, where the optical coherence elastography method utilizes an ultrasonic beam to induce a sample to be detected to generate a first elastic wave and a second elastic wave perpendicular to a propagation direction, so that when the optical coherence tomography method is used to image the first elastic wave and the second elastic wave, an imaging result including elastic information in two directions, namely the first direction and the second direction, can be obtained, and thus the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction can be obtained according to the imaging result, so as to achieve a purpose of measuring axial and lateral elastic information of the sample to be detected, and achieve a purpose of comprehensively and accurately evaluating an anisotropic elastic characteristic of the sample to be detected.
The embodiments in the present description are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other.
The previous description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the present application. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the application. Thus, the present application is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims (10)

1. An optical coherence elastography method, comprising:
inducing a sample to be detected by using an ultrasonic sound beam to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is vertical to the second direction;
and imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
2. The method according to claim 1, wherein inducing the sample to be measured to generate the first elastic wave and the second elastic wave by using the ultrasonic sound beam comprises:
and forming a multipoint vibration source in the sample to be detected by using the plurality of ultrasonic sound beams, wherein the multipoint vibration source induces the surface and/or the interior of the sample to be detected to generate the first elastic wave and the second elastic wave.
3. The method according to claim 2, wherein when the first elastic wave and the second elastic wave are located on the surface of the sample to be measured, the first elastic wave and the second elastic wave are a surface rayleigh wave and a longitudinal shear wave, respectively.
4. The method according to claim 2, wherein when the first and second elastic waves are located inside the sample to be measured, the first and second elastic waves are longitudinal shear waves and transverse shear waves, respectively.
5. The optical coherence elastography method according to claim 2, wherein the imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and the obtaining the elasticity information of the sample to be measured in the first direction and the elasticity information of the sample to be measured in the second direction according to the imaging result comprises:
imaging the first elastic wave and the second elastic wave on the surface of the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result;
and imaging the first elastic wave and the second elastic wave in the sample to be detected by using an optical coherence tomography method, and acquiring elastic information of the surface of the sample to be detected in a first direction and elastic information of the surface of the sample to be detected in a second direction according to an imaging result.
6. An optical coherence elastography system, comprising: an imaging unit and an acoustic radiation force excitation unit; wherein the content of the first and second substances,
the acoustic radiation force excitation unit is used for forming a plurality of ultrasonic sound beams and transmitting the ultrasonic sound beams to a sample to be detected so that the ultrasonic sound beams induce the sample to be detected to generate a first elastic wave and a second elastic wave, wherein the propagation direction of the first elastic wave is a first direction, the propagation direction of the second elastic wave is a second direction, and the first direction is perpendicular to the second direction;
the imaging unit is used for transmitting the detection light beam to the sample to be detected, receiving the detection light beam reflected and scattered by the sample to be detected, imaging the first elastic wave and the second elastic wave according to the reflected and scattered detection light beam by using an optical coherence tomography method, and acquiring the elastic information of the sample to be detected in the first direction and the elastic information of the sample to be detected in the second direction according to the imaging result.
7. The optical coherence elastography system of claim 6, further comprising: a coupling unit;
the coupling unit includes an acoustic reflection surface having an optical transparency characteristic and an acoustic reflection characteristic, and a light incident surface;
the probe beam is incident through the light incidence surface and is transmitted to a sample to be detected through the acoustic reflection surface, and the ultrasonic acoustic beam is transmitted to the sample to be detected along the same direction or the similar direction after being reflected by the acoustic reflection surface.
8. The optical coherence elastography system of claim 7, wherein the coupling unit comprises: a first dielectric structure, an intermediate dielectric structure, and a second dielectric structure; wherein the content of the first and second substances,
the intermediate dielectric structure is disposed between the first dielectric structure and the second dielectric structure, the first dielectric structure including the light entrance face;
the second medium structure comprises an acoustic incidence surface, and the contact surface of the intermediate medium structure and the second medium structure is the acoustic reflection surface.
9. The optical coherence elastography system of claim 8, wherein the difference between the optical refractive index of the first dielectric structure, the optical refractive index of the second dielectric structure, and the optical refractive index of the intermediate dielectric structure is less than a first predetermined difference;
and the difference value of the acoustic impedance of the second dielectric structure and the acoustic impedance of the middle dielectric structure is larger than a second preset difference value.
10. The system of claim 9, wherein the first and second dielectric structures are prisms, and the intermediate dielectric structure is a silicone oil layer or a water layer;
or
The first medium structure and the second medium structure are both a silicon oil layer or a water layer or a phosphate buffer salt solution layer or a physiological salt solution layer, and the middle medium structure is a glass layer.
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