CN111261135A - Mie resonance-based double-negative-type acoustic metamaterial for transcranial ultrasonic imaging - Google Patents

Mie resonance-based double-negative-type acoustic metamaterial for transcranial ultrasonic imaging Download PDF

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CN111261135A
CN111261135A CN202010044301.XA CN202010044301A CN111261135A CN 111261135 A CN111261135 A CN 111261135A CN 202010044301 A CN202010044301 A CN 202010044301A CN 111261135 A CN111261135 A CN 111261135A
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黄玉辉
吴勇军
金一铭
陈洁
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Abstract

The invention discloses a double-negative-type acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance, which comprises an ultrasonic couplant used as a matrix and a scatterer dispersed in the matrix and used for generating the Mie resonance, wherein the scatterer is a porous polyethylene glycol diacrylate hydrogel microsphere; the volume fraction of the porous polyethylene glycol diacrylate hydrogel microspheres in the matrix is 15-25%. The double-negative acoustic metamaterial provided by the invention can effectively eliminate the dissipation and distortion effects of the skull on sound waves, so that transcranial ultrasonic imaging is hopefully realized without depending on the naturally existing or artificially manufactured sound window of the skull.

Description

Mie resonance-based double-negative-type acoustic metamaterial for transcranial ultrasonic imaging
Technical Field
The invention belongs to the field of acoustic metamaterials, and particularly relates to a double-negative type acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance.
Background
In the medical field, Magnetic Resonance Imaging (MRI), Computed Tomography (CT) and craniocerebral ultrasound are the main imaging diagnostic methods for craniocerebral diseases. While MRI is generally considered to be the most suitable method for craniocerebral examination, CT also has its excellent diagnostic value, in some cases, craniocerebral ultrasound has an irreplaceable role. First, cranial ultrasound can provide hemodynamic information that cannot be obtained by MRI and CT; secondly, the craniocerebral ultrasonic equipment is portable, is suitable for bedside detection and long-term dynamic monitoring of rescue departments such as ambulances, emergency rooms, intensive care units and the like, and can carry out bedside examination on critically ill patients which cannot be carried; in addition, the ultrasonic detection has no radiation damage of CT and no discomfort caused by the strong magnetic field of MRI. Therefore, the craniocerebral ultrasonic imaging technology has important clinical application value. However, due to the huge acoustic impedance mismatch between the skull and the intracranial soft tissue, the ultrasonic wave can be seriously reflected at the internal and external interfaces of the skull, and in addition, the skull strongly absorbs the acoustic wave, and only about 1% of energy is left when the ultrasonic signal carrying the information of the intracranial tissue and the blood flow reaches the receiving probe. Current craniocerebral ultrasound imaging techniques rely heavily on naturally occurring or artificially created acoustic windows of the skull, such as the "temporal acoustic window" and the "orbital acoustic window", where ultrasound cannot be directed through the mostly thicker skull for tissue and blood flow imaging. And researches show that the temporal bone is gradually thickened along with the increase of the age, and the failure rate of transcranial Doppler ultrasound of the old women can reach more than 10%. In summary, the skull has a very strong attenuation and distortion effect on ultrasound, which conventionally has difficulty in effectively penetrating the skull to achieve intracranial tissue and blood flow imaging.
In recent years, the rapid development of acoustic metamaterials has provided a new idea for solving the above-mentioned problems. The acoustic metamaterial is one of hot spots of current international academic and engineering research, and is an artificial periodic material which is composed of sub-wavelength structural units and has extraordinary physical properties. By skillfully designing the structural units of the metamaterial, the transmission direction of sound waves can be accurately controlled, so that unique functions which cannot be achieved by conventional materials, such as negative refraction, negative reflection, sound invisibility and the like, are realized, and the metamaterial has wide application value in the fields of military invisibility, vibration reduction, noise reduction, medical imaging and the like.
Disclosure of Invention
The invention aims to provide a double-negative-type acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance, which can effectively eliminate the dissipation and distortion effects of a skull on sound waves.
The invention provides the following technical scheme:
the acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance comprises an ultrasonic couplant serving as a matrix and scatterers dispersed in the matrix and used for generating the Mie resonance, wherein the scatterers are porous polyethylene glycol diacrylate hydrogel microspheres.
Preferably, the volume fraction of the porous polyethylene glycol diacrylate hydrogel microspheres in the matrix is 15-25%.
Preferably, the density of the ultrasonic coupling agent is 900-1100 kg/m3The sound velocity is 1400-1600 m/s.
Preferably, the mass density of the porous polyethylene glycol diacrylate hydrogel microspheres is 500-700 kg/m3The sound velocity is 120-180 m/s.
Preferably, the radius of the porous polyethylene glycol diacrylate hydrogel microsphere is 50-70 μm.
The acoustic metamaterial can simultaneously realize negative equivalent mass density and negative equivalent elastic modulus in the frequency range of 0.63-0.73 MHz.
Aiming at the problem that ultrasonic waves are difficult to penetrate through a skull, the invention provides a double-negative acoustic metamaterial based on Mie resonance to accurately control a sound wave transmission path so as to improve the penetration rate of the sound wave transmission path. The acoustic metamaterial provided by the invention is a composite material, and the matrix of the acoustic metamaterial is an ultrasonic couplant (the density is 900-1100 kg/m)3The sound velocity is 1400-1600 m/s), and the scatterer generating the Mie resonance is porous polyethylene glycol diacrylate (PEGDA) hydrogel microspheres. Due to the existence of a large number of air cavities, the porous hydrogel microspheres show low sound velocity (120-180 m/s) and moderate mass density (500-700 kg/m)3) Can beCausing a large unipolar mie resonance, resulting in a negative equivalent elastic modulus. At the same time, a large number of viscous particles exhibit strong dipole-mie resonances, resulting in a negative equivalent mass density. By changing the density, the sound velocity, the radius and the volume fraction in the matrix of the porous hydrogel microspheres, the frequency range (0.63-0.73 MHz) generated by the negative equivalent parameters can be regulated and controlled.
The double-negative acoustic metamaterial provided by the invention can effectively eliminate the dissipation and distortion effects of the skull on sound waves. The double-negative acoustic metamaterial provided by the invention is expected to realize transcranial ultrasonic imaging independent of an acoustic window, and has great application value in the field of clinical imaging diagnosis.
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Fig. 1 is a finite element simulation of a focused ultrasound beam sound field: (a) only water is present; (b) water and skull bone; (c) water, skull, and bi-negative acoustic metamaterials.
Fig. 2 is a schematic diagram of preparing porous hydrogel microspheres by a microfluidic technology.
FIG. 3 is a graph of (a) a real equivalent density part, (b) an imaginary equivalent density part, (c) a real equivalent elastic modulus part, and (d) an imaginary equivalent elastic modulus part of the porous hydrogel microspheres of example 1 dispersed in an ultrasound couplant, which are calculated by a multiple scattering model; wherein the density of the porous hydrogel microspheres is 500kg/m3The sound velocity is 120m/s, the radius is 50 mu m, and the volume fraction is 15 percent; ultrasonic coupling agent density is 900kg/m3The speed of sound is 1400 m/s.
FIG. 4 is a graph of (a) a real equivalent density part, (b) an imaginary equivalent density part, (c) a real equivalent elastic modulus part, and (d) an imaginary equivalent elastic modulus part of the porous hydrogel microspheres of example 2 dispersed in an ultrasound couplant, which are calculated by a multiple scattering model; wherein the density of the porous hydrogel microspheres is 600kg/m3The sound velocity is 150m/s, the radius is 60 mu m, and the volume fraction is 20 percent; the density of the ultrasonic coupling agent is 1000kg/m3The speed of sound is 1500 m/s.
FIG. 5 is a graph of (a) a real equivalent density part, (b) an imaginary equivalent density part, (c) a real equivalent elastic modulus part, and (d) an imaginary equivalent elastic modulus part of the porous hydrogel microspheres of example 3 dispersed in an ultrasound couplant, which are calculated by a multiple scattering model; wherein the porous hydrogel microspheres are denseDegree of 700kg/m3Sound velocity of 180m/s, radius of 70 μm, volume fraction of 25%; ultrasonic coupling agent density is 1100kg/m3The speed of sound is 1600 m/s.
FIG. 6 is (a) a real part of equivalent density, (b) an imaginary part of equivalent density, (c) a real part of equivalent elastic modulus, and (d) an imaginary part of equivalent elastic modulus calculated by a multiple scattering model and obtained by dispersing the steel ball microspheres in the ultrasonic couplant in comparative example 1; wherein the density of the steel ball microspheres is 7900kg/m3Sound velocity of 5955m/s, radius of 60 μm, volume fraction of 20%; the density of the ultrasonic coupling agent is 1000kg/m3The speed of sound is 1500 m/s.
FIG. 7 shows (a) a real equivalent density part, (b) an imaginary equivalent density part, (c) a real equivalent elastic modulus part, and (d) an imaginary equivalent elastic modulus part of the hollow hydrogel microspheres in comparative example 2 dispersed in an ultrasound couplant, calculated by a multiple scattering model; wherein the density of the hollow hydrogel microspheres is 200kg/m3Sound velocity 500m/s, radius 60 μm, volume fraction 20%; the density of the ultrasonic coupling agent is 1000kg/m3The speed of sound is 1500 m/s.
Detailed Description
The present invention will be described in further detail with reference to the following examples and the accompanying drawings. The embodiments and descriptions of the present invention are provided to explain the present invention and not to limit the present invention.
According to the double-negative-type acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance, a scatterer porous polyethylene glycol diacrylate hydrogel microsphere (porous hydrogel microsphere) can be prepared by adopting a microfluidic technology (as shown in figure 2).
The specific preparation method of the porous polyethylene glycol diacrylate hydrogel microspheres comprises the following steps: 1) preparing a dispersion phase solution. Adding polyethylene glycol diacrylate (PEGDA), 2-hydroxy-2-methyl-1-phenyl-1-acetone (I-1173, photoinitiator), glacial acetic acid, magnetically stirring for 10 min, adding deionized water, weighing sodium bicarbonate (pore-forming agent), adding the above solution, and stirring to obtain dispersed phase solution. 2) Preparing a continuous phase solution. Adding dimethyl silicone oil and a surfactant SPAN80 into a beaker, and stirring until the dimethyl silicone oil and the surfactant SPAN80 are completely dissolved to obtain a continuous phase solution. 3) And (5) assembling the microfluidic platform. Respectively sucking the dispersion phase and the continuous phase solution into a 2mL syringe, respectively fixing the syringe on an injection pump, and adjusting parameters of the injection pump (the flow rate of the continuous phase is 0.5mL/h, and the flow rate of the dispersion phase is 0.05 mL/h); the microfluidic chip is arranged on a clamp, the inlet of the chip is connected with a needle through a hose, the outlet hose is led into a collecting bottle, and an ultraviolet lamp (7W-365nm) is arranged above the collecting bottle. 4) The injection pump and the ultraviolet lamp are started. And waiting for 2-3 hours, and collecting the solution of the dispersed porous hydrogel microspheres. 5) Separating out the porous hydrogel microspheres. And (4) centrifuging, washing and repeating for 3 times to obtain the porous hydrogel microspheres.
Based on the multiple scattering model, the change curve of the equivalent mass density and the equivalent elastic modulus of the acoustic metamaterial along with the frequency can be obtained through calculation, the specific calculation formula is shown as follows,
Figure BDA0002368832240000061
Figure BDA0002368832240000062
where ρ is the dynamic equivalent mass density, ρ0Mass density in static state, η volume fraction of porous hydrogel microspheres of scatterer, k0In wavenumber, f (0) is the forward scattering function of a single scatterer, f (π) is the backward scattering function of a single scatterer, M is the dynamic equivalent elastic modulus, M is0Is the modulus of elasticity at rest. The scattering function f (θ) is calculated as follows:
Figure BDA0002368832240000063
wherein S isnIs the scattering coefficient, P, of a single scatterern(cos θ) is a Legendre polynomial.
The invention adopts finite element simulation to simulate the sound field distribution condition of a focused ultrasonic beam under three conditions, and the result is shown in figure 1, wherein in figure 1, (a) only water exists, (b) water and a skull, (c) the water, the skull and a double negative type acoustic metamaterial exist. When the ultrasonic waves pass through an aqueous medium only existing in the skull, the energy is greatly reduced (as shown in (b) in fig. 1)), and the focused ultrasonic beam is greatly different from the focused ultrasonic beam only existing in the medium water alone after penetrating the skull, which indicates that the skull has serious distortion and attenuation effects on the ultrasonic beam, and the impedance mismatch between the skull and the water causes the sound waves to be greatly reflected on the surface of the skull, and the skull dissipates the energy of the sound waves. When a layer of the double-negative acoustic metamaterial (in embodiment 1 or embodiment 2 or embodiment 3) provided by the invention is added in front of the skull (as shown in (c) in fig. 1), the energy of the focused ultrasonic beam after penetrating the skull is greatly improved compared with that when the skull exists alone, and the focused position is extremely close to that when only water exists alone. The simulation result theoretically proves that the double-negative acoustic metamaterial provided by the invention can effectively eliminate the dissipation and distortion effects of the skull on sound waves.
Example 1
The density of the porous hydrogel microspheres is 500kg/m3The sound velocity is 120m/s, and the radius is 50 mu m; the density of the ultrasonic coupling agent is 900kg/m3The sound velocity is 1400 m/s; uniformly dispersing the porous hydrogel microspheres in an ultrasonic couplant matrix to obtain the required double-negative acoustic metamaterial, wherein the volume fraction of the porous hydrogel microspheres is 15%. The change curve of the equivalent mass density and the equivalent elastic modulus along with the frequency, which is calculated based on the multiple scattering model, is shown in fig. 3, and the acoustic metamaterial shows the negative equivalent mass density and the negative equivalent elastic modulus at the frequency of 0.63-0.67 MHz.
Example 2
The density of the porous hydrogel microspheres is 600kg/m3The sound velocity is 150m/s, and the radius is 60 mu m; the density of the ultrasonic coupling agent is 1000kg/m3The sound velocity is 1500 m/s; uniformly dispersing the porous hydrogel microspheres in an ultrasonic couplant matrix to obtain the required double-negative acoustic metamaterial, wherein the volume fraction of the porous hydrogel microspheres is 20%. The change curve of the equivalent mass density and the equivalent elastic modulus along with the frequency, which is calculated based on the multiple scattering model, is shown in fig. 4, and the acoustic metamaterial shows the negative equivalent mass density and the negative equivalent elastic modulus at the frequency of 0.67-0.70 MHz.
Example 3
The density of the porous hydrogel microspheres is 700kg/m3The sound velocity is 180m/s, and the radius is 70 mu m; the density of the ultrasonic coupling agent is 1100kg/m3The sound velocity is 1600 m/s; uniformly dispersing the porous hydrogel microspheres in an ultrasonic couplant matrix to obtain the required double-negative acoustic metamaterial, wherein the volume fraction of the porous hydrogel microspheres is 25%. The change curve of the equivalent mass density and the equivalent elastic modulus along with the frequency, which is calculated based on the multiple scattering model, is shown in fig. 5, and the acoustic metamaterial shows the negative equivalent mass density and the negative equivalent elastic modulus at the frequency of 0.68-0.73 MHz.
Comparative example 1
The density of the steel ball microspheres is 7900kg/m3The sound velocity is 5955m/s, and the radius is 60 mu m; the density of the ultrasonic coupling agent is 1000kg/m3The sound velocity is 1500 m/s; and uniformly dispersing the steel ball microspheres in the ultrasonic couplant matrix to obtain the acoustic composite material, wherein the volume fraction of the steel ball microspheres is 20%. The change curves of the equivalent mass density and the equivalent elastic modulus along with the frequency, which are calculated based on the multiple scattering model, are shown in fig. 6, and the acoustic composite material shows the positive equivalent mass density and the positive equivalent elastic modulus within 0-1 MHz.
Comparative example 2
The density of the hollow hydrogel microspheres (hollow polyethylene glycol diacrylate hydrogel microspheres) is 200kg/m3The sound velocity is 500m/s, and the radius is 60 mu m; the density of the ultrasonic coupling agent is 1000kg/m3The sound velocity is 1500 m/s; and uniformly dispersing the hollow hydrogel microspheres in an ultrasonic couplant matrix to obtain the acoustic composite material, wherein the volume fraction of the hollow hydrogel microspheres is 20%. The change curve of equivalent mass density and equivalent elastic modulus along with frequency calculated based on a multiple scattering model is shown in fig. 7, and the acoustic composite material only shows a single negative equivalent elastic modulus within 0.82-1 MHz.
The above-mentioned embodiments are intended to illustrate the technical solutions and advantages of the present invention, and it should be understood that the above-mentioned embodiments are only the most preferred embodiments of the present invention, and are not intended to limit the present invention, and any modifications, additions, equivalents, etc. made within the scope of the principles of the present invention should be included in the scope of the present invention.

Claims (6)

1. The double-negative-type acoustic metamaterial for transcranial ultrasonic imaging based on Mie resonance is characterized by comprising an ultrasonic couplant serving as a matrix and a scatterer dispersed in the matrix and used for generating the Mie resonance, wherein the scatterer is a porous polyethylene glycol diacrylate hydrogel microsphere.
2. The bipnegative-tone acoustic metamaterial for transcranial ultrasound imaging based on mie resonance according to claim 1, wherein the volume fraction of the porous polyethylene glycol diacrylate hydrogel microspheres in the matrix is 15-25%.
3. The dual-negative-tone acoustic metamaterial for trans-cranial ultrasound imaging based on Mie's resonance in claim 1 or 2, wherein the density of the ultrasonic couplant is 900-1100 kg/m3The sound velocity is 1400-1600 m/s.
4. The double-negative-tone acoustic metamaterial for transcranial ultrasonic imaging based on Mie's resonance in claim 1 or 2, wherein the mass density of the porous polyethylene glycol diacrylate hydrogel microspheres is 500-700 kg/m3The sound velocity is 120-180 m/s.
5. The double-negative-tone acoustic metamaterial for transcranial ultrasonic imaging based on Mie's resonance in claim 1 or 2, wherein the radius of the porous polyethylene glycol diacrylate hydrogel microsphere is 50-70 μm.
6. The biprimary negative acoustic metamaterial for transcranial ultrasound imaging based on mie resonance according to claim 1 or 2, wherein the acoustic metamaterial achieves both negative equivalent mass density and negative equivalent elastic modulus at a frequency range of 0.63-0.73 MHz.
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CN112244894A (en) * 2020-10-19 2021-01-22 浙江大学 Ultrasonic noninvasive transcranial imaging method and system based on broadband acoustic metamaterial
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