CN111449629B - Optical coherence elastography method and device - Google Patents
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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 measured to generate a first elastic wave and a second elastic wave with vertical propagation directions, so that when the first elastic wave and the second elastic wave are imaged by utilizing the optical coherence elastography method, imaging results containing elastic information in the first direction and the second direction can be obtained, and therefore 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 can be obtained according to the imaging results, the purpose of measuring the axial direction and the lateral direction elastic information of the sample to be measured is achieved, and the purpose of comprehensively and accurately evaluating the anisotropic elastic characteristics of the sample to be measured is achieved.
Description
Technical Field
The present disclosure relates to the field of imaging technologies, and in particular, to an optical coherence elastography method and apparatus.
Background
The difference of the elastomechanical characteristics of the biological tissues is derived from the difference of components, structures and interactions of biological molecules, cells and sample levels, and the elastomehc measurement of the biological tissues has important significance for evaluating the physiological functions of the samples, and can be used for diagnosing diseases of parts such as eyeballs, cardiovascular diseases, mammary glands, livers and the like. Age-related macular degeneration (Age-related macular degeneration, AMD), a degenerative disease of the pigment epithelium of the macular region of the retina, is one of the major causes of irreversible blindness in people over 60 years of Age. The retina elasticity measurement can be used for risk evaluation and early diagnosis of wet AMD to realize early intervention and treatment, thereby delaying disease progression and improving treatment effect, and has very important clinical application value.
The current mainstream method for elastic measurement of biological tissue is an optical coherence elastography (Optical Coherence Elastography, OCE) method, which is an imaging mode based on an optical coherence tomography (Optical Coherence Tomography, OCT) platform and an elastic measurement principle for analyzing elastic mechanical parameters (such as shear modulus and young's modulus) of biological tissue. Optical coherence tomography (Optical coherence tomography, OCT) is a non-invasive, high-resolution, three-dimensional medical imaging technique with spatial resolution up to about 10 μm, imaging depth of biological tissue of 2-3mm, 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, when the biological tissue is imaged by using the optical coherence elastography method induced by the ultrasonic sound beam in the prior art, only lateral elasticity information of the detected biological tissue perpendicular to the external acting force direction can be obtained, but axial elasticity information of the detected biological tissue parallel to the external acting force direction cannot be obtained, so that anisotropic elasticity characteristics of the biological tissue cannot be comprehensively and accurately estimated.
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 axial and lateral elasticity information of a measured sample and achieve the purpose of comprehensively and accurately evaluating 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 to generate a first elastic wave and a second elastic wave by utilizing an ultrasonic sound beam, 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;
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 an imaging result.
Optionally, the inducing the sample to be tested to generate the first elastic wave and the second elastic wave by using the ultrasonic sound beam includes:
and forming a plurality of vibration sources in the sample to be tested by utilizing a plurality of ultrasonic sound beams, wherein the vibration sources induce the surface and/or the inside of the sample to be tested 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 a surface rayleigh wave and a longitudinal shear wave respectively.
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 longitudinal shear wave and transverse shear wave, respectively.
Optionally, the imaging the first elastic wave and the second elastic wave by using an optical coherence tomography method, and obtaining 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 the elastic information of the surface of the sample to be detected in a first direction and the elastic information of the surface of the sample to be detected in a second direction according to imaging results;
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 the elastic information of the surface of the sample to be detected in a first direction and the elastic information of the surface of the sample to be detected in a second direction according to imaging results.
An optical coherence elastography system, comprising: an imaging unit and an acoustic radiation force excitation unit; wherein,,
the sound radiation force excitation unit is used for forming a plurality of ultrasonic sound beams to be transmitted 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, 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 a 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 an imaging result.
Optionally, the method further comprises: a coupling unit;
the coupling unit comprises an acoustic reflecting surface and a light incident surface, wherein the acoustic reflecting surface has optical transparency and acoustic reflection characteristics;
the detection light beam is incident through the light incidence surface and transmitted to the sample to be detected through the sound reflection surface, and the ultrasonic sound beam is transmitted to the sample to be detected along the same direction or a similar direction with the detection light beam after being reflected by the sound reflection surface.
Optionally, the coupling unit includes: a first dielectric structure, an intermediate dielectric structure, and a second dielectric structure; wherein,,
the intermediate medium structure is arranged between the first medium structure and the second medium structure, and the first medium structure comprises the light incidence surface;
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, the difference between the optical refractive index of the first medium structure, the optical refractive index of the second medium structure and the optical refractive index of the intermediate medium structure is smaller than a first preset difference;
the difference between the acoustic impedance of the second medium structure and the acoustic impedance of the intermediate medium structure is greater than a second preset difference.
Optionally, the first medium structure and the second medium structure are prisms, and the intermediate medium structure is a silicon oil layer or a water layer;
or (b)
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 saline layer, and the middle medium structure is a glass layer.
As can be seen from the foregoing technical solutions, the embodiments of the present application provide an optical coherence elastography method and an apparatus, where the optical coherence elastography method uses an ultrasonic beam to induce a sample to be measured to generate a first elastic wave and a second elastic wave with perpendicular propagation directions, so that when the first elastic wave and the second elastic wave are imaged by using the optical coherence tomography method, an imaging result including elastic information in two directions, i.e., a first direction and a second direction, can be obtained, so that 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 can be obtained according to the imaging result, thereby achieving the purpose of measuring axial and lateral elastic information of the sample to be measured, and achieving the purpose of comprehensively and accurately evaluating anisotropic elastic characteristics of the sample to be measured.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings that are required to be used in the embodiments or the description of the prior art will be briefly described below, and it is obvious that the drawings in the following description are only embodiments of the present application, and that other drawings may be obtained according to the provided drawings without inventive effort to a person skilled in the art.
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 an optical coherence elastography method according to an embodiment of the present application;
FIG. 3 is a schematic diagram of an array arrangement of an array type ultrasonic transducer;
FIG. 4 is a schematic diagram of induced compression and shear waves when two point vibration sources act inside a sample to be tested;
FIG. 5 is a schematic diagram of induced compression 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 an M-B scan;
FIG. 7 is a schematic diagram of an optical coherence elastography system according to an embodiment of the present application;
fig. 8 is a schematic structural view 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 view of an imaging unit according to still another embodiment of the present application;
FIG. 11 is a schematic structural view 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 ultrasonic acoustic beam induced optical coherence elastography method of the prior art images biological tissue, only lateral elasticity information of the biological tissue to be measured perpendicular to the external force direction can be obtained, but axial elasticity information of the biological tissue to be measured parallel to the external force direction cannot be obtained, and specific reasons thereof will be explained below.
When the biological tissue is subjected to elasticity measurement, an external force is firstly used for inducing the elastic wave in the tissue, then the propagation of the elastic wave is detected through the imaging platform, and finally the elastic modulus in the propagation direction of the elastic wave is calculated according to the propagation speed of the elastic wave. Therefore, in the elastic measurement of anisotropic biological tissue, the construction of an elastic wave imaging platform is the basis of the measurement, while an elastic wave that induces both axial propagation along the external force and lateral propagation perpendicular to the external force is the key to the measurement.
In the prior art, referring to fig. 1, during imaging, an ultrasonic sound beam is utilized to induce a sample to be measured to generate micro vibration, after the vibration amplitude of the sample is measured by an OCT imaging technology, the propagation of an elastic wave is reconstructed, the propagation speed of the elastic wave is calculated, and the elastic mechanical 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 lateral elasticity information analysis of the vertical external acting 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 in directions perpendicular to the direction of the external force, and can only measure the modulus of elasticity in the lateral direction (perpendicular to the external force). Although the compression wave is a longitudinal wave, its propagation direction is parallel to the direction of the external force, but the propagation speed of the compression wave in the biological tissue is too fast (about 1500 m/s), the current OCT technology cannot capture the propagation process of the compression wave and calculate its propagation speed due to the imaging frame rate limitation. Therefore, in most studies, biological tissues are assumed to be isotropic materials, and only lateral elastic modulus is measured to characterize the elastic properties of biological tissues in all directions, and axial elastic modulus cannot be measured, so that anisotropic elastic characteristics of samples cannot be comprehensively and accurately estimated.
In view of this, an embodiment of the present application provides an optical coherence elastography method, including:
inducing a sample to be detected to generate a first elastic wave and a second elastic wave by utilizing an ultrasonic sound beam, 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;
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 an imaging result.
The optical coherence elastography method utilizes ultrasonic sound beams to induce a sample to be tested to generate a first elastic wave and a second elastic wave with vertical propagation directions, so that when the first elastic wave and the second elastic wave are imaged by utilizing the optical coherence elastography method, imaging results containing elastic information in the first direction and the second direction can be obtained, and therefore the elastic information of the sample to be tested in the first direction and the elastic information of the sample to be tested in the second direction can be obtained according to the imaging results, the purpose of measuring axial and lateral elastic information of the sample to be tested is achieved, and the purpose of comprehensively and accurately evaluating anisotropic elastic characteristics of the sample to be tested is achieved.
The following description of the embodiments of the present application will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all, of the embodiments of the present application. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present disclosure.
The embodiment of the application provides an optical coherence elastography method, as shown in fig. 2, including:
s101: inducing a sample to be detected to generate a first elastic wave and a second elastic wave by utilizing an ultrasonic sound beam, 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;
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 an imaging result.
In step S101 of the present 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 force, and the lateral direction refers to a direction perpendicular to the external force.
In step S101, the purpose of inducing the elastic wave of the sample to be measured in the first direction and the elastic wave of the sample to be measured in the second direction may be achieved by forming multiple vibration sources in the sample to be measured.
Specifically, one possible implementation procedure of step S101 includes:
s1011: and forming a plurality of vibration sources in the sample to be tested by utilizing a plurality of ultrasonic sound beams, wherein the vibration sources induce the surface and/or the inside of the sample to be tested to generate the first elastic wave and the second elastic wave.
When a plurality of ultrasonic sound beams are generated by using equipment such as an acoustic radiation force excitation unit and are incident to a sample to be tested, the ultrasonic sound beams generate multi-point mechanical driving in the sample to be tested, so that a multi-point vibration source is formed.
The acoustic radiation force excitation unit comprises a waveform generator, an amplifier, an array ultrasonic transducer and other structures, wherein the waveform generator generates high-frequency sine waves, square waves or triangular waves synchronized with OCT, and the array ultrasonic transducer is excited to generate multi-point acoustic radiation force after the high-frequency sine waves, square waves or triangular waves are amplified by the amplifier. 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, and the effective area array size of the ultrasonic transducer is 10.5×10.5mm. The subsequent parameter designs such as the number and the interval of the array elements are optimized according to the theoretical analysis of the elastic wave and the regulation and control method of the array elements. The acoustic radiation force is the interaction between an acoustic wave and an obstacle on its transmission path, and the acoustic radiation force amplitude |f| at a given position in space can be estimated by the following formula:
where α represents the attenuation coefficient of ultrasound in the tissue, related to the ultrasound frequency, I represents the average intensity of the sound beam at the location to be measured, related to the sound field of the ultrasound transducer, and c represents the propagation velocity of ultrasound in the tissue. Thus, the ultrasound radiation force increases with an increase in tissue attenuation coefficient and ultrasound intensity. By controlling the distance between the ultrasound transducer and the tissue, the focus position of the acoustic radiation force on the sample is varied, so that the acoustic radiation force can be focused on the tissue surface or inside the tissue.
When two point sources of vibration act simultaneously on tissue, each point source of vibration induces independently compression 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 spot vibration source, thin solid arrows indicate the vibration direction, dashed circles indicate the position of the wave surface at this moment, and left and right line segments respectively indicate that they come from two different spot vibration sources. Where two transverse shear waves meet, a shear wave whose vibration direction is parallel to the propagation direction is generated due to superposition of the waves, and is therefore called a longitudinal shear wave.
When the spot vibration sources are located inside the sample to be measured, each spot vibration source induces compression and shear waves inside the tissue, as shown at 4. Where the transverse shear waves induced by the two point vibration sources meet, longitudinal shear waves with vibration directions parallel to the propagation directions are generated due to superposition of the waves, and propagate up and down to the vibration sources respectively. And simultaneously, transverse shear waves perpendicular to the vibration direction of the vibration source are generated and propagated to the two sides of the vibration source. Namely, when the first elastic wave and the second elastic wave are positioned in the sample to be detected, the first elastic wave and the second elastic wave are respectively a longitudinal shear wave and a transverse shear wave.
When the point vibration source is positioned on the surface of the sample to be measured, the Rayleigh waves induced by the point vibration source are transmitted to the two sides of the vibration source, the transmission direction is perpendicular to the direction of the external force, and the transmission depth is in the range of about 1 wavelength from the tissue surface, 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 propagates 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 detected, the first elastic wave and the second elastic wave are respectively surface Rayleigh waves and longitudinal shear waves. The tissue in fig. 4 and 5 is the sample to be measured.
Correspondingly, the 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 the elastic information of the surface of the sample to be detected in a first direction and the elastic information of the surface of the sample to be detected in a second direction according to imaging results;
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 the elastic information of the surface of the sample to be detected in a first direction and the elastic information of the surface of the sample to be detected in a second direction according to imaging results.
The elastic wave reconstruction process in the optical coherence tomography process is described below.
In order to capture the rapidly propagating elastic wave at the maximum frame rate, an OCT (optical coherence tomography ) data acquisition method based on M-B scanning can be employed, the principle of which is shown in fig. 6. B scanning refers to combining a plurality of processed signal lines in the depth direction which are arranged side by side in space into an anatomical image (namely OCT B mode image) of a two-dimensional plane, which reflects the internal fault section of a measured object. M scanning refers to sampling at the same lateral position of a sample for multiple times, and expanding sampled signal lines in time sequence to form a one-dimensional time sequence chart (namely OCT M mode image). In the process of repeatedly inducing elastic waves by ultrasound, the OCT unit acquires 1M-mode time sequence chart at each lateral position, and then reconstructs the M-mode time sequence charts at different lateral positions into a B-mode two-dimensional plane image which changes with time. For example, in a system employing a 100kHz swept source, the frame rate of the M-B scanning method for elastography may be maximized, about 100000 frames/sec.
In order to detect minute vibrations in a sample to be measured with high sensitivity using an OCT unit, to realize propagation imaging of a weak-amplitude elastic wave, a vibration measurement method based on phase analysis may be employed. First, the interference signal with the change of wavelength collected by the OCT unit is transformed into a complex signal with the change of depth by fast fourier transform (Fast Fourier Transformation, FFT), and the complex signal is band-pass filtered to remove low frequency noise. OCT complex signal
Comprising amplitude A (x, y, z, t) part and phase +.>
Part, where (x, y, z) represents the spatial position of the scan and t represents the sampling instant. The phase change of the OCT signal can be used to calculate the vibration velocity and displacement of the scattering particles in the sample according to Doppler (Doppler) principles. Velocity V of scattering particles in sample within time interval Δt and OCT phase variation +.>
The relationship is as follows:
wherein n represents the optical refractive index of the sample, λ represents the center wavelength of light in vacuum, θ represents the angle between the direction of particle motion and the probe beam, v×cos (θ) represents the velocity component of the particle in the direction of the probe beam, and the phase varies
Can be calculated from the OCT complex signal as follows:
wherein F is x，y，z，t And F x，y，z，t+1 Respectively expressed in differentTime (T and t+1 times), the OCT complex signal at the same position (lateral position x, y and depth position z) is time-spaced at time T and t+1 times at Δt.
Calculation of elastic modulus:
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 propagation velocity of transverse shear waves versus young's modulus E can be expressed using the following formula:
wherein ρ represents the sample density, V Shear The propagation velocity of the transverse shear wave is represented, and v represents the poisson's ratio of the biological tissue. Incompressible biological soft sample density ρ is 1000kg/m 3 The biological tissue poisson ratio v is about 0.5.
Since the formation of the longitudinal shear wave results from the superposition of the transverse shear wave, 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 therefore, 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.
Surface Rayleigh waves typically propagate in a range of about 1 wavelength from the surface, and therefore, the lateral Young's modulus near the surface of a sample can be measured by Rayleigh waves, which is calculated as follows:
wherein V is Rayleigh Representing the propagation velocity of the rayleigh wave.
The following describes an optical coherence elastography system provided in the embodiments of the present application, and the optical coherence elastography system described below may be referred to correspondingly to the optical coherence elastography method described above.
Accordingly, an embodiment of the present application provides an optical coherence elastography system, as shown in fig. 7, including: an imaging unit 100 and an acoustic radiation force excitation unit 200; wherein,,
the acoustic radiation force excitation unit 200 is configured to form a plurality of ultrasonic sound beams for transmitting to the sample a10 to be tested, so that the plurality of ultrasonic sound beams induce the sample a10 to be tested to generate a first elastic wave and a second elastic wave, 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 100 is configured to transmit a probe beam to the sample a10 to be detected, receive the 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 acquire 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 includes: 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 incidence surface;
the detection light beam is incident through the light incidence surface, is transmitted to the sample to be detected through the sound reflection surface, and returns to the imaging light path through the sound reflection surface after being reflected and scattered by the sample; after being reflected by the sound reflecting surface, the ultrasonic sound beam and the detection light beam are transmitted to the sample to be detected along the same direction or a similar direction.
Alternatively, referring to fig. 8, the imaging unit 100 includes: a light source 110, an optical coupler 150, a reference arm 120, a sample arm 140, and an imaging device 130; wherein,,
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 the probe beam, and receiving the reference beam reflected by the reference arm 120 and the probe beam reflected and scattered by the sample a10 to be measured; the reference beam reflected by the reference arm 120 and the probe beam reflected and scattered by the sample a10 to be measured interfere in the optical coupler 150;
the imaging device 130 is configured to perform 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 light source 111, or may be an optical coherence tomography unit 100 based on a continuous spectrum light source 113, that is, the light source 110 may be a swept light 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 an optical coherence tomography unit 100 based on a swept light source 111, and fig. 10 is a schematic structural diagram of the optical coherence tomography unit 100 based on a continuous spectrum light source 113.
In the structure shown in fig. 9, the light to be processed (usually weak coherent light) output by the swept laser light source 111 passes through the polarization controller 112 and then enters the optical coupler 150 to be split, 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. After passing through the lens 141 of the sample arm 140, the probe beam 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, and structural imaging and vibration measurement of the sample a10 to be measured are realized after detection 131 and signal processing by the photodetector.
In the structure shown in fig. 10, after the light to be processed outputted from the continuous spectrum light source 113 passes through the optical isolator 114, the light 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. After passing through the polarization controller and the lens 141, the probe beam 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 reflecting 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 the interference light is photoelectrically converted on the camera 135 after passing through the other 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.
For the acoustic radiation force excitation unit 200, referring to fig. 11, fig. 11 shows a possible structure of the acoustic radiation force excitation unit 200, the acoustic radiation force excitation 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 array of ultrasonic transducers 230.
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 as to realize remote mechanical excitation of the sample A10 to be tested. The ultrasonic beam output by the ultrasonic transducer 230 enters the sample a10 to be measured through an ultrasonic coupling material (water or ultrasonic gel), and an acoustic radiation force field is formed on the sample a10 to be measured to induce micro vibration of tissues. The acoustic radiation force has the advantages of non-invasive, non-contact, remote focusing 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 with the direction perpendicular to the Z axis and parallel to the paper surface 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 may be perpendicular to the Z axis, so that the probe beam may directly enter the light incident surface perpendicularly, the propagation direction of the beam is not changed, the normal direction of the acoustic reflection surface may be parallel to the XZ plane and may be set at an angle with the ultrasonic beam, and the angle may be equal to 45 ° so that the ultrasonic beam may 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 ultrasonic sound beam and probe beam are parallel to each other can directly induce the elastic vibration parallel to the direction of the probe beam, and compared with the mode that ultrasonic sound beam is obliquely incident and excited, the sensitivity of the system to vibration detection is improved. Compared with a back incidence or normal incidence mode, the parallel incidence mode of the ultrasonic sound beam and the detection beam can be very conveniently applied to clinical detection (such as fundus tissue elastography and the like).
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 one 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 intermediate dielectric structure 330 is disposed between the first dielectric structure 310 and the second dielectric structure 320, and the first dielectric structure 310 includes a light incident surface;
the second medium structure 320 includes an acoustic incident surface, and the contact surface between the intermediate medium structure 330 and the second medium structure 320 is the acoustic reflecting surface.
The difference between the optical refractive index of the first medium structure 310, the optical refractive index of the second medium structure 320, and the optical refractive index of the intermediate medium 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, where 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 probe light beam, and the probe light beam is not excessively reflected, thereby reducing the loss of the probe light beam passing through the coupling unit 300;
however, there is a larger mismatch of acoustic impedances 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 transparency to the probe beam and simultaneously realizing reflection of the ultrasonic beam.
Optionally, referring to fig. 12, the first medium structure 310 and the second medium 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 is filled with optically index matched, low acoustic impedance, and non-volatile silicone oil to form the silicone layer. Silicone oil and glass have good optical refractive index matching (optical refractive index of silicone oil is 1.4, optical refractive index of glass is about 1.5), but have large acoustic impedance mismatch (acoustic impedance of silicone oil is 0.74×10) 5 g/(cm 2 S) with an acoustic impedance of 12.1X10% for glass 5 g/(cm 2 S)) and therefore the silicone layer is optically transparent, but can act as an ultrasound reflector.
In fig. 12, since the frequency of the ultrasonic beam is generally above 1MHz and cannot propagate in the air, in order to enable the ultrasonic beam to enter the coupling unit 300, a transparent ultrasonic couplant 240 is further filled between the coupling unit 300 and the acoustic radiation force excitation unit 200, and an ultrasonic couplant 240 (water or ultrasonic gel) is also 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 beam.
Referring to fig. 13, optionally, the first dielectric structure 310 and the second dielectric structure 320 are both a silicone oil layer or an aqueous layer or a phosphate buffer salt 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 each a material layer that is optically index-matched to the glass layer and has a low acoustic impedance. Specifically, in one embodiment of the present application, the first medium structure 310 and the second medium structure 320 are both water placed in a water tank, the intermediate medium structure 330 is a glass layer inserted into the water tank, and the structure of the coupling unit 300 is water-glass-water, and the contact surface of the glass layer and the water is the acoustic reflection surface.
Based on 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 includes an acoustic incident surface and an attaching surface forming a preset angle with the transmission direction of the ultrasonic beam;
the impedance mismatch film 350 is attached to the attachment surface.
Wherein a 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 optical refractive indexes of the third dielectric structure 340 and the impedance mismatch film 350 are matched, but the acoustic impedances are mismatched, so that the impedance mismatch film 350 and the coupling unit 300 formed by the third dielectric structure 340 have optically transparent characteristics, and the impedance mismatch film 350 and the third dielectric structure 340 form an acoustic reflection surface capable of reflecting an ultrasonic sound beam.
In this embodiment, when the probe beam is incident from the upper side of the impedance matching film 350 and the ultrasonic beam is incident from the left side of the third dielectric structure 340, the contact surface between the impedance mismatch film 350 and the third dielectric structure 340 is the acoustic reflection surface.
As previously mentioned, the preset angle refers to an angle that is parallel or approximately parallel to the probe beam after the ultrasonic sound beam is reflected, for example, the preset angle may be about 45 ° when the probe beam is parallel to the Z axis and the ultrasonic sound beam is parallel to the X axis.
In summary, the embodiments of the present application provide an optical coherence elastography method and an apparatus, where the optical coherence elastography method uses an ultrasonic beam to induce a sample to be measured to generate a first elastic wave and a second elastic wave with perpendicular propagation directions, so that when the first elastic wave and the second elastic wave are imaged by using the optical coherence tomography method, an imaging result including elastic information in two directions, namely, a first direction and a second direction, can be obtained, so that 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 can be obtained according to the imaging result, thereby achieving the purpose of measuring axial and lateral elastic information of the sample to be measured, and achieving the purpose of comprehensively and accurately evaluating anisotropic elastic characteristics of the sample to be measured.
In the present specification, each embodiment is described in a progressive manner, and each embodiment is mainly described in a different point from other embodiments, and identical and similar parts between the embodiments are all enough to refer 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 (8)
1. An optical coherence elastography system, comprising: an imaging unit, an acoustic radiation force excitation unit, and a coupling unit; wherein,,
the sound radiation force excitation unit is used for forming a plurality of ultrasonic sound beams to be transmitted 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, 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 a 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 a first direction and the elastic information of the sample to be detected in a second direction according to an imaging result;
the coupling unit comprises an acoustic reflecting surface and a light incident surface, wherein the acoustic reflecting surface has optical transparency and acoustic reflection characteristics;
the detection light beam is incident through the light incidence surface and transmitted to the sample to be detected through the sound reflection surface, and the ultrasonic sound beam is transmitted to the sample to be detected along the same direction or a similar direction with the detection light beam after being reflected by the sound reflection surface.
2. The optical coherence elastography system of claim 1, wherein the coupling unit comprises: a first dielectric structure, an intermediate dielectric structure, and a second dielectric structure; wherein,,
the intermediate medium structure is arranged between the first medium structure and the second medium structure, and the first medium structure comprises the light incidence surface;
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.
3. The optical coherence elastography system of claim 2, wherein a difference between an optical refractive index of the first medium structure, an optical refractive index of the second medium structure, and an optical refractive index of the intermediate medium structure is less than a first predetermined difference;
the difference between the acoustic impedance of the second medium structure and the acoustic impedance of the intermediate medium structure is greater than a second preset difference.
4. The optical coherence elastography system of claim 3, wherein the first and second media structures are prisms, and the intermediate media structure is a silicon oil layer or a water layer;
or (b)
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 saline layer, and the middle medium structure is a glass layer.
5. The optical coherence elastography system of claim 1, wherein the inducing the plurality of ultrasonic acoustic beams to induce the sample to be measured to generate a first elastic wave and a second elastic wave comprises:
and forming a plurality of vibration sources in the sample to be tested by utilizing a plurality of ultrasonic sound beams, wherein the vibration sources induce the surface and/or the inside of the sample to be tested to generate the first elastic wave and the second elastic wave.
6. The optical coherence elastography system of claim 5, 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.
7. The optical coherence elastography system of claim 5, wherein when the first elastic wave and the second elastic wave are inside the sample to be measured, the first elastic wave and the second elastic wave are longitudinal shear wave and transverse shear wave, respectively.
8. The optical coherence elastography system of claim 5, wherein the imaging the first elastic wave and the second elastic wave according to the reflected and scattered probe beam by using the optical coherence tomography method, and 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 of the surface of the sample to be detected according to the reflected and scattered detection light beams by using an optical coherence tomography method, and acquiring the elastic information of the surface of the sample to be detected in a first direction and the elastic information of the surface of the sample to be detected in a second direction according to imaging results;
and imaging the first elastic wave and the second elastic wave in the sample to be detected according to the reflected and scattered detection light beams by using an optical coherence tomography method, and acquiring the elastic information of the surface of the sample to be detected in the first direction and the elastic information of the surface of the sample to be detected in the second direction according to imaging results.
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